JPS62176433A - Subtraction system for removing scattering x-rays - Google Patents
Subtraction system for removing scattering x-raysInfo
- Publication number
- JPS62176433A JPS62176433A JP61016623A JP1662386A JPS62176433A JP S62176433 A JPS62176433 A JP S62176433A JP 61016623 A JP61016623 A JP 61016623A JP 1662386 A JP1662386 A JP 1662386A JP S62176433 A JPS62176433 A JP S62176433A
- Authority
- JP
- Japan
- Prior art keywords
- rays
- scattered
- ray
- grid
- primary
- 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
- 238000002834 transmittance Methods 0.000 claims description 6
- 230000015654 memory Effects 0.000 claims description 5
- 230000005855 radiation Effects 0.000 description 8
- 238000010586 diagram Methods 0.000 description 4
- 230000000694 effects Effects 0.000 description 3
- 230000006866 deterioration Effects 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 244000025254 Cannabis sativa Species 0.000 description 1
- 235000012766 Cannabis sativa ssp. sativa var. sativa Nutrition 0.000 description 1
- 235000012765 Cannabis sativa ssp. sativa var. spontanea Nutrition 0.000 description 1
- 235000009120 camo Nutrition 0.000 description 1
- 235000005607 chanvre indien Nutrition 0.000 description 1
- 235000021438 curry Nutrition 0.000 description 1
- 230000002542 deteriorative effect Effects 0.000 description 1
- 239000011487 hemp Substances 0.000 description 1
- 238000003780 insertion Methods 0.000 description 1
- 230000037431 insertion Effects 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
- A61B6/5282—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to scatter
Landscapes
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Health & Medical Sciences (AREA)
- Medical Informatics (AREA)
- Pathology (AREA)
- Heart & Thoracic Surgery (AREA)
- High Energy & Nuclear Physics (AREA)
- Physics & Mathematics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Computer Vision & Pattern Recognition (AREA)
- Radiology & Medical Imaging (AREA)
- Biomedical Technology (AREA)
- Biophysics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Analysing Materials By The Use Of Radiation (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
(57)【要約】本公報は電子出願前の出願データであるた
め要約のデータは記録されません。(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.
Description
【発明の詳細な説明】 （イ）産業上の利用分野 本発明は、Ｘ線測定の分野で利用される。[Detailed description of the invention] (b) Industrial application field INDUSTRIAL APPLICATION This invention is utilized in the field of X-ray measurement.
本発明は、Ｘ線撮影におけるχｆｒｊ１．画像の画質を
ピコ １−レ↓ト ２ 子、１人ハせり壬Ｉ Ｖ丘臼ｇ
仝土、ｌ−η” ｋ 二 ｈ４′ノ ２ ’／シ
ステムに関する。The present invention provides χfrj1. Pico the image quality
Regarding the earth, l−η”k2h4′ノ2′/system.
（ロ）従来技術
Ｘ線撮影において、被検体から出る散乱Ｘ線は被写体コ
ントラストを下げる。 このことは第３図右側に示すよ
うに、Ｘ線強度のうち散乱線が占める割合がパックグラ
ウンドとして大きく、−次Ｘ線の占める割合が小さくな
るからである。(b) Prior art In X-ray photography, scattered X-rays emitted from the subject reduce the contrast of the subject. This is because, as shown on the right side of FIG. 3, the proportion of scattered rays in the X-ray intensity is large as back ground, and the proportion of -order X-rays is small.
この散乱線による画質低下を防ぐために、従来より散乱
線を除去する努力がなされている。In order to prevent the image quality from deteriorating due to the scattered radiation, efforts have been made to remove the scattered radiation.
散乱線除去グリッドの介挿は、一般的に知られている。The insertion of anti-scatter grids is generally known.
（ハ）発明が角９決しようとする問題点しかしながら、
そのようなグリッド方式や、スリットレジオロジーと称
されるラインセンサーによる散乱線除去方式は、散乱線
の嵐少の分、Ｘ線の出力を増大させ、＜ｉってｘ線管へ
の負荷増大、また愚者への被は（線量増大につながり、
画質とそれらとの兼合いで限度がある。(c) Problems that the invention attempts to resolve, however,
Such a grid method and a scattered radiation removal method using a line sensor called slit resiology increase the output of X-rays by the amount of scattered radiation, increasing the load on the x-ray tube. , and the exposure to fools (leading to increased dose,
There is a limit depending on the image quality and the balance between them.
本発明の目的は、上記のような事情において散コツＮ？
４６１ｍＬ＋Ｐｉ声；ル〆レ−／ｌ−？１１ｗ−――・
＝１−ｊａ）’、１−−ｈ−９嘲ｌ啼コツＭ４Ｃ＋白し
Ａ市カレーよ ０■」貝力］ＬτＣＸ肯ロＪ月ｆｆ、に
−９つ円叉白し人麻除去サブトラクションシステムを提
供することである。The purpose of the present invention is to solve the above-mentioned circumstances.
461 mL + Pi voice; Lure-/l-? 11w---・
= 1-ja)', 1--h-9 mocking tips M4C + white A city curry 0■'' shell power] LτCX affirmation J month ff, ni-9 yen white human hemp removal subtraction system The goal is to provide the following.
（ニ）問題点を解決するための手段
前記した目的は、被検体の直後にグリッドを挿入した場
合のＸ線ｌＦ２ （Ｆ２ ＝ａＴｔ ＋ｂＳ１、ただ
しＴ１は一次Ｘ線、Ｓｌは散乱Ｘ線、ａは一次Ｘ線透過
率、ｂは散乱Ｘ線透過率）のメモリＭ２と、グリッドを
除去した場合のＸ線量Ｆｉ（Ｆｉ ＝Ｔ１＋Ｓ１ ）の
メモリと、グリッドによって決まる既知の一次線透過率
ａと散乱Ｘ線透過率）／（ｂ−ａ）を算出する演算器と
を具有することにより、達成できる。(d) Means for solving the problem The above purpose is to calculate the X-rays when a grid is inserted immediately after the subject. is the primary X-ray transmittance; This can be achieved by having an arithmetic unit that calculates X-ray transmittance)/(ba).
（ホ）作用
ｔ％来のように、散乱線による画質低下を防ぐのに、散
乱線を直接除去する器具を使うのではな（、散乱線を含
む像が記録される媒体ないしメモリを２つ用意し、両者
間の演算により一次Ｘ線を摘出する。 つ談り、散乱線
そのものを取除くのではなく、散乱線による像を利用し
て散乱線による画質劣化を改善する。(e) Effect t% To prevent image quality deterioration due to scattered rays, do not use a device that directly removes scattered rays (i.e., use two media or memories in which images containing scattered rays are recorded). The primary X-rays are extracted by calculation between the two. Rather than removing the scattered rays themselves, the image of the scattered rays is used to improve the image quality deterioration caused by the scattered rays.
（へ）実施例
本発明の好）商な実権例は、図面の第１図と第２図につ
いて説明される。DESCRIPTION OF THE PREFERRED EMBODIMENTS A practical example of the present invention will be described with reference to FIGS. 1 and 2 of the drawings.
理解の便宜上、従来のグリッドよる散乱線除去例を第４
図により示している。For convenience of understanding, an example of scattering radiation removal using a conventional grid is shown in the fourth example.
Illustrated in the figure.
１４がグリッドであり、入射側の散乱Ｘ線Ｓ１が一次Ｘ
線Ｔ１に比べ進む角度が大きくずれていることを利用し
、−次線の進む方向に並べた鉛などのＸ線じゃΔ〜い物
によるついたて１４により、角度の異なるＸ線（つまり
散乱線）Ｓｌを除去している。14 is a grid, and the scattered X-rays S1 on the incident side are the primary
Taking advantage of the fact that the advancing angle is greatly different from that of the line T1, X-rays at different angles (that is, scattered rays) are Sl is removed.
グリッド１４に入射するＸ線は、−次線Ｔ１と散乱線Ｓ
１の和であり、さらにグリッドを通過した各々をＴ２、
Ｓ２とおくと、’Ｉ’２ ＝ ａＴ１、Ｓ２ ＝ｂＳｘ
でａ、ｂ （１、さらにａ）ｂとなって、散乱線の含有
率が罵って画質が改善される。The X-rays incident on the grid 14 consist of a −th order ray T1 and a scattered ray S.
1, and each passing through the grid is T2,
If we set S2, 'I'2 = aT1, S2 = bSx
Then, a, b (1, and further a) b, the content of scattered radiation is reduced and the image quality is improved.
ａ、ｂはグリッド１４によって決まる係数で、ｂはさら
に散乱線の度合にも依存する。a and b are coefficients determined by the grid 14, and b further depends on the degree of scattered radiation.
そこで、本発明の原理作用例が第２図により示されてい
る。 グリッド１４をはさみ、Ｘ線入射側とその反対側
にそれぞれＸ線記録物（例えばフィルム、増感紙、ＦＣ
，Ｒ）をおき、撮影を行なう。Therefore, an example of the principle operation of the present invention is shown in FIG. Grid 14 is sandwiched between X-ray recording materials (for example, film, intensifying screen, FC
, R) and take pictures.
入射側のフィルムＦ１には、Ｆ１＝Ｔ１＋８１、反対側
にはＦ２ ＝Ｔ２ ＋Ｓ２ ＝ａＴｉ ＋ｂＳｉが記録
される。 もし、ｂ ＩＪ（既知であればＦｌを重み係
数すをかけ、Ｆ２を引算して一次線のみの像Ｔ１を求め
ることができる。F1=T1+81 is recorded on the film F1 on the incident side, and F2=T2+S2=aTi+bSi is recorded on the opposite side. If b IJ (if known), the image T1 of only the primary line can be obtained by multiplying Fl by the weighting coefficient and subtracting F2.
つまり、ｐ１＝’ｐｉ＋５Ｉ
Ｆ２ ＝ａＴ１＋ｂＳ１ （ただし、ａは一次線透過
率、ｂは散乱線透過率としてそれぞれ既知である。）が
成立しているので、
ｂＦｌ −Ｆ２ ＝ （ｂ−ａ） ・Ｔｉが得られ、
Ｔ１＝ （ｂＦｌ−Ｆ２）／ （ｂ−ａ）として、−次
Ｘ線Ｔ１のみの像、つまり散乱線のとれた像を得ること
ができる。In other words, p1='pi+5I F2 =aT1+bS1 (However, a is known as the primary ray transmittance and b is the scattered ray transmittance.), so bFl - F2 = (b-a) ・Ti is obtained,
As T1=(bFl-F2)/(ba-a), an image of only -order X-rays T1, that is, an image without scattered rays can be obtained.
第１図は本発明の１実施例として上記の原理を実行した
処理ブロック図である。 ここで、１０はＸ線管、１２
は被亭＄体、１４はグリッド、１日はイメージ・インテ
ンシファイア、１８はＴＶカメラ、２０はメモリ、２２
は演算器、２４は係数ａ、ｂの設定器、２６は表示器で
ある。FIG. 1 is a processing block diagram in which the above principle is implemented as an embodiment of the present invention. Here, 10 is an X-ray tube, 12
is the object, 14 is the grid, 1st is the image intensifier, 18 is the TV camera, 20 is the memory, 22
24 is a calculator, 24 is a setter for coefficients a and b, and 26 is a display.
メモリ２０の一方は、グリッド１４を挿入して得たＸ線
像を、他方はグリッド１４を除去して得たＸ線像をそれ
ぞれ格納している。 演算器２２は前記した演算を行な
う。One of the memories 20 stores an X-ray image obtained by inserting the grid 14, and the other stores an X-ray image obtained by removing the grid 14. The arithmetic unit 22 performs the above-mentioned arithmetic operations.
（ト）効果
従来例に比べて、散乱線をも有効利用するため退者の被
ば（線思が少な（て足り、従ってＸ線管の負荷も軽厘で
き、両者の寿命を延ばすことができるという効果が奏さ
れる。(G) Effects Compared to the conventional example, since scattered radiation is also used effectively, there is less radiation exposure for the retiree, and the load on the X-ray tube can therefore be reduced, extending the lifespan of both. The effect of being able to do this is achieved.
第１図は本発明の１実施例を示した処理ブロック図、第
２図は本発明による原理作用例示図、第３図は散乱線の
発生態様とその作用例示図、菓４図は従来例の作用説明
図である。
１４はグリッド、２０はメモリ、２２は演算器、２４は
設定器である。
第１図
第２図
第３図
第４図Fig. 1 is a processing block diagram showing one embodiment of the present invention, Fig. 2 is a diagram illustrating the principle operation according to the present invention, Fig. 3 is a diagram illustrating the generation mode of scattered rays and its operation, and Fig. 4 is a conventional example. FIG. 14 is a grid, 20 is a memory, 22 is an arithmetic unit, and 24 is a setting device. Figure 1 Figure 2 Figure 3 Figure 4
Claims (1)
Ｆ２＝ａＴ１＋ｂＳ１、ただしＴ１は一次Ｘ線、Ｓ１は
散乱Ｘ線、ａは一次Ｘ線透過率、ｂは散乱Ｘ線透過率）
のメモリＭ２と、グリッドを除去した場合のＸ線量Ｆ１
（Ｆ１＝Ｔ１＋Ｓ１）のメモリと、グリッドによつて決
まる既知の一次Ｘ線透過率ａと散乱Ｘ線透過率ｂの設定
器と、メモリＭ１、Ｍ２の各読出しデータと設定データ
とにより式Ｔ１＝（ｂＦ１−Ｆ２）／（ｂ−ａ）を算出
する演算器とを具有することを特徴とする散乱Ｘ線除去
サブトラクションシステム。X-ray dose F2 (when the grid is inserted immediately after the subject)
F2=aT1+bS1, where T1 is primary X-ray, S1 is scattered X-ray, a is primary X-ray transmittance, b is scattered X-ray transmittance)
memory M2 and the X-ray dose F1 when the grid is removed
The formula T1= 1. A subtraction system for removing scattered X-rays, comprising: a computing unit that calculates (bF1-F2)/(ba).
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61016623A JPS62176433A (en) | 1986-01-28 | 1986-01-28 | Subtraction system for removing scattering x-rays |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61016623A JPS62176433A (en) | 1986-01-28 | 1986-01-28 | Subtraction system for removing scattering x-rays |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPS62176433A true JPS62176433A (en) | 1987-08-03 |
Family
ID=11921470
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP61016623A Pending JPS62176433A (en) | 1986-01-28 | 1986-01-28 | Subtraction system for removing scattering x-rays |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS62176433A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH02237277A (en) * | 1989-03-09 | 1990-09-19 | Toshiba Corp | X-ray diagnostic device |
| JP2001134748A (en) * | 1999-08-31 | 2001-05-18 | General Electric Co <Ge> | Method and device for correcting digital x-ray imaging |
| JP2017227541A (en) * | 2016-06-23 | 2017-12-28 | 株式会社日立製作所 | Radiation imaging apparatus and radiation imaging method |
-
1986
- 1986-01-28 JP JP61016623A patent/JPS62176433A/en active Pending
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH02237277A (en) * | 1989-03-09 | 1990-09-19 | Toshiba Corp | X-ray diagnostic device |
| JPH0582111B2 (en) * | 1989-03-09 | 1993-11-17 | Tokyo Shibaura Electric Co | |
| JP2001134748A (en) * | 1999-08-31 | 2001-05-18 | General Electric Co <Ge> | Method and device for correcting digital x-ray imaging |
| JP2017227541A (en) * | 2016-06-23 | 2017-12-28 | 株式会社日立製作所 | Radiation imaging apparatus and radiation imaging method |
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