JPS61133847A - Promation of image clear of scattered line in x ray image - Google Patents
Promation of image clear of scattered line in x ray imageInfo
- Publication number
- JPS61133847A JPS61133847A JP59257138A JP25713884A JPS61133847A JP S61133847 A JPS61133847 A JP S61133847A JP 59257138 A JP59257138 A JP 59257138A JP 25713884 A JP25713884 A JP 25713884A JP S61133847 A JPS61133847 A JP S61133847A
- Authority
- JP
- Japan
- Prior art keywords
- image
- ray
- scattered
- low frequency
- rays
- 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
- 230000005855 radiation Effects 0.000 claims description 27
- 238000000034 method Methods 0.000 claims description 15
- 238000003384 imaging method Methods 0.000 claims description 8
- 238000002601 radiography Methods 0.000 claims 2
- 238000002583 angiography Methods 0.000 claims 1
- 238000001514 detection method Methods 0.000 claims 1
- 238000001914 filtration Methods 0.000 abstract description 13
- 238000004364 calculation method Methods 0.000 abstract description 2
- 238000010586 diagram Methods 0.000 description 4
- 230000007423 decrease Effects 0.000 description 2
- 238000010183 spectrum analysis Methods 0.000 description 2
- OAICVXFJPJFONN-UHFFFAOYSA-N Phosphorus Chemical compound [P] OAICVXFJPJFONN-UHFFFAOYSA-N 0.000 description 1
- 241000555745 Sciuridae Species 0.000 description 1
- 238000000333 X-ray scattering Methods 0.000 description 1
- 238000003759 clinical diagnosis Methods 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- PSGAAPLEWMOORI-PEINSRQWSA-N medroxyprogesterone acetate Chemical compound C([C@@]12C)CC(=O)C=C1[C@@H](C)C[C@@H]1[C@@H]2CC[C@]2(C)[C@@](OC(C)=O)(C(C)=O)CC[C@H]21 PSGAAPLEWMOORI-PEINSRQWSA-N 0.000 description 1
- 238000005070 sampling Methods 0.000 description 1
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
- G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
- G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. 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
Abstract
Description
【発明の詳細な説明】
〔発明の技術分野〕
この発明は撮影手段によって撮影されたＸ線画像（Ｘ線
フィルム、蓄積性螢光体ノート、イメーノイ／テンノフ
ァイアなどの検出器に形成された画像）を電気的信号に
変換しディジタル画像を作製する電気的Ｘ線画像システ
ムに関するものである。[Detailed Description of the Invention] [Technical Field of the Invention] This invention relates to X-ray images taken by a photographing means (an image formed on a detector such as an ) into electrical signals to produce digital images.
一般に臨床診断用Ｘ線画像を得るには、Ｘ線フィルム上
に直接Ｘ線画像を形成する方法と、Ｘ線をＸ線検出器で
とらえ電気的信号（こ変換しＸ線ディジタル画像として
像を形成する方法がある。In general, to obtain X-ray images for clinical diagnosis, there are two methods: forming an X-ray image directly on X-ray film, and capturing X-rays with an X-ray detector and converting them into electrical signals (which are converted into digital X-ray images). There is a way to form it.
このＸ線画像を形成するさい昏こ、Ｘ線の散乱線を除去
する目的で、被検体とＸ線検出器の開にＸ線グリッド又
はエアギャグ（Ｇｒｏｅｄｅｌ法、被検体とＸ線検出器
の開に１０〜３０Ｃｊｎの空間をあける。）を用い散乱
線を除去している。When forming this X-ray image, in order to remove scattered X-ray rays, an X-ray grid or an air gag (Groedel method) is used between the subject and the X-ray detector. A space of 10 to 30 Cjn is left between the two.) to remove scattered radiation.
Ｘ線管電圧が高くなるにつれ散乱線の割合は多くなし、
画像コノトラストは低下する。また散乱線が多くなると
透過Ｘ線量の定量性も低下する。As the X-ray tube voltage increases, the proportion of scattered radiation does not increase.
Image conotrust decreases. Furthermore, as the amount of scattered radiation increases, the quantitative quality of the amount of transmitted X-rays also decreases.
Ｘ線電圧６０Ｋｅｖ以上ではＸ線の散乱線を除去するこ
とは診断をする上で必要となる。At an X-ray voltage of 60 Kev or more, it is necessary to remove scattered X-rays for diagnosis.
一般に撮影手技（こよって撮影されたＸ線画像では、Ｘ
線の散乱線除去（こＸ線グ’１ ノドを用いる方法が施
行されている。Ｘ線グリッドを被検体とＸ線検出器の間
に入れることによし、Ｘ線グリッドにＸ線が吸収され直
接Ｘ線の損失が生じる。この直接Ｘ線の損失はＸ線管球
の負荷を増し患者の被曝線量も増重。また静止形Ｘ線グ
リッドでは格子縞が出現し高画質を得ることができない
。またＸ線グリッドに平行な散乱線は除去することがで
きない。このために画像コントラストは低下する。In general, X-ray images taken using the imaging technique (X
Scattered radiation removal (this method uses an X-ray grid). By placing an X-ray grid between the subject and the X-ray detector, the X-ray grid absorbs the A loss of direct X-rays occurs. This loss of direct X-rays increases the load on the X-ray tube and increases the patient's exposure dose. Also, with a stationary X-ray grid, checkered fringes appear and high image quality cannot be obtained. Also, scattered rays parallel to the X-ray grid cannot be removed, which reduces image contrast.
一般をこはあまり用いられないがエアギャグ（Ｇｒｏｅ
ｄｅｌ法）を被検体とＸ線検出器の間に入れた場合（こ
は、Ｘ線画像の幾何学的拡大もありＸ線管焦屯（こよる
幾何学的ボケも大きくなる。Although it is not commonly used, air gags (Groe
del method) is placed between the subject and the X-ray detector (in this case, the X-ray image is also geometrically enlarged, and the X-ray tube focus (the resultant geometric blur) also increases.
このように現行のＸ線画像番こおけるＸ線の散乱線除去
は、きわめて多くの問題を含んでいる。As described above, the removal of scattered X-rays in current X-ray image processing involves numerous problems.
この発明は上記事情にもとずいてなされたもので、電気
的Ｘ線画像ノステムにおいてＸ線の散乱線を電気的計算
手法によし、散乱線除去を目的とするものである。This invention has been made based on the above circumstances, and aims to eliminate scattered rays by using an electrical calculation method to calculate scattered rays of X-rays in an electrical X-ray imaging system.
（発明の概要Ｊ
この発明は上記目的を達成するため、Ｘ線の散乱線画像
が低周波画像から成り立つことに着目し、Ｘ線グリッド
やエアギャブを用いず撮影されたＸ線画像よし、散乱線
画像に相当する低周波画像を製作し、撮影されたＸ線画
像から差し引くことで、散乱線除去を達成する。(Summary of the Invention J In order to achieve the above object, this invention focuses on the fact that X-ray scattered ray images consist of low-frequency images. Scattered radiation removal is achieved by creating a low-frequency image corresponding to the image and subtracting it from the captured X-ray image.
以下この発明を図面に示す。一実施例を参照して説明す
る。This invention is illustrated in the drawings below. This will be explained with reference to one embodiment.
第１図は電気的Ｘ線画像システムのブロック図である。FIG. 1 is a block diagram of an electrical x-ray imaging system.
図中１はＸ線を曝射するＸ線管、２は被検体、３はＸ線
管１から曝射されて被検体２を透下したＸ線を検出する
Ｘ線検出器（Ｘ線フィルム、蓄積性螢光体シート、イメ
ージイノテンノファイアなど）、４はＸ線検出器３で検
出された画像を電気的ディンタル信号に変換するＸ線画
像読取装置、５はＸ線画像読取装置４で入力したディノ
タル画像を処理し散乱線画像に相当する低周波画像を作
り低周波画像減算を行なう画像処理装置、６は画像処理
装置５で散乱線番こ相当する低周波画像を減算した散乱
線除去画像を出力するＸ線画像表示装置（ＣＲＴなど）
又はＸ線画像記録装置（フィルム、紙などに視覚的表示
記録するための装置）である。In the figure, 1 is an X-ray tube that emits X-rays, 2 is a subject, and 3 is an X-ray detector (X-ray film) that detects the X-rays emitted from the X-ray tube 1 and transmitted through the subject 2. , stimulable phosphor sheet, image innotenfire, etc.); 4 is an X-ray image reading device that converts the image detected by the X-ray detector 3 into an electrical digital signal; 5 is the X-ray image reading device 4; An image processing device that processes the input dinotal image to create a low frequency image corresponding to a scattered radiation image and performs low frequency image subtraction; 6 is an image processing device 5 for removing scattered radiation by subtracting a low frequency image corresponding to the scattered radiation image; X-ray image display device (CRT, etc.) that outputs images
or an X-ray image recording device (a device for visually displaying and recording on film, paper, etc.).
上記のように構成された電気的Ｘ線画像システムは次の
ように作用する。被検体２とＸ線検出器３の間にはＸ線
グリッド又はエアギャブが用いられていないため、Ｘ線
検出器３に検出されるＸ線画像は散乱線を多量に含む画
像である。これをＸ線画像読取装置４（こより電気的デ
ィジタル画像に変換し、画像処理装置５へ送られる。こ
こで散乱線を多く含む原画像から、散乱線画像の主体を
なす低周波画像を作製する。この低周波画像の波長と割
合を決定する要素として、Ｘ線管電圧、被検体厚、照射
野面積、被検体部位などの要素がある。The electrical X-ray imaging system configured as described above operates as follows. Since no X-ray grid or air gab is used between the subject 2 and the X-ray detector 3, the X-ray image detected by the X-ray detector 3 is an image containing a large amount of scattered rays. This is converted into an electrical digital image by the X-ray image reading device 4 and sent to the image processing device 5. Here, from the original image containing many scattered rays, a low frequency image, which is the main part of the scattered ray image, is created. There are factors such as the X-ray tube voltage, the thickness of the subject, the area of the irradiation field, and the part of the subject that determine the wavelength and proportion of this low-frequency image.
これらの要素データから散乱線画像に相当するより厳密
な低周波画像を作製することができる。A more precise low-frequency image corresponding to a scattered radiation image can be created from these elemental data.
この低周波画像を作製する方法として、空間フィルタリ
ングをこよる画像処理と、フーリエ変換を用いスペクト
ル解析を行なって周波数フィルタリング、）〜リエ逆変
換を行なうことによって低周波画像を再構成する画像処
理の２方法が一般的である。The methods for creating this low-frequency image include image processing that involves spatial filtering, frequency filtering that uses Fourier transform to perform spectral analysis, and image processing that reconstructs the low-frequency image by performing spectral analysis using Fourier transform. Two methods are common.
ここでは近年頻繁（こ行なわれている空間フィルタリ／
グによる画像処理で、低周波画像を作製する方法（こつ
いて説明する。これは２次元的な入力画像のＸ線量情報
を２次元的に処理して新たな画像を得るための処理であ
るが、この空間フィルタリングの中でも特に多く用いら
れるものが該たたみ込みろ波（Ｋｅｒｎｅｌ Ｃｏｎ
ｖｏｌｕｔｉｏｎ Ｆｉｌｔｅｒｉｎｇ ）と呼ばれ
る処理である。Here, we will introduce the spatial filtering that has been carried out frequently in recent years.
A method of creating low-frequency images through image processing using Among these spatial filtering methods, the most commonly used one is convolutional filtering (Kernel Convolution filtering).
This is a process called volume filtering.
第２図はこのたたみ込み沖波を説明するための図であっ
て、入力画像の隣接するｔＸ＆個の要素たとえば第２図
（ＡｌｅこＡｒｒｒ−１＋ ｎ−５Ａｒｒｒｌ＋ ｒｌ
、Ａｒｒｒｌ＋ ｎ＋ｌ・・・・・・・・・・・・・・
・Ａｍ−１＋ ｎ＋１．として示した３×３個の各ま丁
目に入れられているものはＸ線検出器で撮像して得られ
る画像の各画素であるが、この９個の画素のうち中央の
画素Ａｍｅｎは該画像の標本化点のＸ線量情報を与える
ものであし、このＸ線全情報が大きい場合は該画像の輝
度が高くなっているものとする。FIG. 2 is a diagram for explaining this convolutional offshore wave, in which adjacent tX& elements of the input image, for example,
,Arrrl+n+l・・・・・・・・・・・・・・・
・Am-1+ n+1. What is placed in each of the 3 x 3 blocks shown as is each pixel of the image obtained by taking an image with an X-ray detector, but among these nine pixels, the center pixel Amen is the image It gives the X-ray dose information of the sampling point, and if this total X-ray information is large, it is assumed that the brightness of the image is high.
したかって第２図回申のＡｎｒ １． ｎ−ｌ、Ａｍ−
１，ｎ、・・・・ ・・・・Ａｒｒｒ＋−１，ｎ＋１、
は上記中央の画素Ａｍ、 ｎ ｉこ隣接した各画素の輝
度情報である。Therefore, Anr of Figure 2 Circular 1. n-l, Am-
1, n, ... Arrr+-1, n+1,
is the luminance information of the central pixel Am, n i adjacent pixels.
このような構成を有する入力画像の中の画素Ａｍ＋ ｎ
とそのまわりの各画素に対して、水平方向をこ４個、垂
直方向にに個配例された要素たとえば第２図■をこ示し
たオペレータＢｌｌ、ＢＩ２．・・Ｂ３３を作用させた
場合（二対応する第２図（Ｏｉこ示した出力Ｈｍ＋ ｎ
は
Ｈｍｎ＝Ｂ Ｉ ＩＡｎＴ−Ｌ＋ ｎ−ｌ＋Ｂ Ｉ ２
Ａｒｒｒ−Ｌ ｒｒ−１−Ｂ Ｉ ３Ａｍ−１、ｎ＋１
＋Ｂ ２１Ａｍ＋ ｎ −＋＋Ｂ ２２Ａｍ＋ ｎ＋Ｂ
ｚ ３ Ａｍ＋ ｒ＋１＋Ｂ ３ ＋ Ａｍ＋ｌ 、
ｎ−１＋Ｂ３２ Ａｍ＋ｌ＋ ｎ十Ｂ ３３Ａｒｒｒ＋
−１＋ ｎ＋ｌとして与えられる。Pixel Am+n in the input image having such a configuration
For each pixel around it, four elements are arranged horizontally and four elements are arranged vertically, for example, operators Bll, BI2, .・When B33 is applied (2 corresponding figure 2 (Oi) output Hm + n
is Hmn=BI IAnT-L+ n-l+BI 2
Arrr-L rr-1-B I 3Am-1, n+1
+B 21Am+ n -++B 22Am+ n+B
z 3 Am+ r+1+B 3 + Am+l,
n-1+B32 Am+l+ n10B 33Arrr+
It is given as -1+n+l.
このように中央の画素をこ対応する位置にある１つの出
力すなわち変換画素信号Ｈｒｒ＋＋ｎを求める操作を、
第２図（２）の点線で囲んで記号の記入していない他の
部分を含む入力画像全体に対して順次行なっていくには
、第２図■に示したオペ［／−夕を、上下左右に］ます
ずつ順次移動させて、そのたびにＨｒ＋ｔ−＋ 、 ｎ
−＋、Ｉ←）、ｎ＋１−・・・・ＨＪＴ＋＋−１，ｎ−
１を木ｙ）ていくのであるが、このようＱこして求めら
れた出力画像は元の入力画像′ｆなわち第２図（支）と
ゲＪＳなった空間周波数を持つようになる。In this way, the operation of obtaining one output, that is, the converted pixel signal Hrr++n at the position corresponding to the central pixel, is as follows:
To sequentially perform operations on the entire input image, including the other parts surrounded by the dotted line in Figure 2 (2) and without symbols, the operations shown in Figure 2 [left and right] one by one, and each time move Hr+t-+, n
-+, I←), n+1-...HJT++-1, n-
1 to tree y), and the output image obtained through Q-filtering in this way has a spatial frequency equal to that of the original input image 'f, that is, Fig. 2 (support).
たとえば前記のような３×３個からなるオペレータをｉ
′：：」とした場合、このオペレータはＩ １２１
し
低域ろ波機能を有するため（こ、入力画像に対して空間
周波数領域上で低域が強調され、低周波画像を作製する
ことができる。For example, if the operator consisting of 3 x 3 operators as mentioned above is
'::', this operator has an I 121 and low-pass filtering function (this means that the input image is emphasized in the low range in the spatial frequency domain, making it possible to create a low-frequency image. .
Ｘ線散乱画像の低域強調領域と散乱線含有率は、Ｘ線管
電圧、被検体部位、被検体厚、照射野面積の４つからほ
ぼ決定できる。Ｘ線管電圧は高くなると散乱線画像は、
より低域側の低周波画像となし、散乱線含有率も増す。The low-frequency emphasis region and scattered ray content of an X-ray scattering image can be approximately determined from four factors: X-ray tube voltage, subject site, subject thickness, and irradiation field area. As the X-ray tube voltage increases, the scattered radiation image becomes
The result is a low-frequency image on the lower side, and the scattered radiation content increases.
被検体部位の平均密度が高いほど散乱線画像は、より低
域側の低周波画像となし、散乱線含有率も増す。被検体
厚が厚くなると散乱線画像は、より低域側の低周波画像
となし、散乱線含有率も増す。照射野が広いと散乱線含
有率が増す。これらの散乱線画像における低域強調領域
と散乱線含有率の決定要因は、各Ｘ線装置によりＸ線エ
ネルギーとＸ線出力効率が違うため、各Ｘ線装置ごと（
こ実験的ζこ求めなければならない。The higher the average density of the subject part, the lower the frequency of the scattered radiation image becomes, and the higher the scattered radiation content. As the thickness of the object increases, the scattered radiation image becomes a lower-frequency image on the lower side, and the scattered radiation content increases. When the irradiation field is wide, the content of scattered radiation increases. The determining factors for the low-frequency enhancement region and scattered radiation content in these scattered radiation images are determined by each X-ray device (
This must be determined experimentally.
上記の４つの要因から実験的に求めた散乱線画像の低域
強調領域と散乱線含有率を基にして、空間フィルタリン
グの２つの要素であるｔＸｋ個とオペレータを決定する
。Two elements of spatial filtering, tXk, and an operator are determined based on the low-frequency emphasis region of the scattered radiation image and the scattered radiation content rate, which are experimentally determined from the above four factors.
散乱線を含む元の画像（こ上記の空間フィルタリングを
行なうことによし、散乱線画像に相当する低周波画像を
作製し、元の画像から差し引くことによし、散乱線除去
画像が製造できる。An original image containing scattered radiation (by performing the above spatial filtering, a low frequency image corresponding to the scattered radiation image is created, and by subtracting it from the original image, a scattered radiation removed image can be produced).
（発明の動画〕
以上の説明から明らかなように、この発明（こよれば、
散乱線が低周波であること営利用し、Ｘ線グリッドを用
いず撮影しても、散乱線除去画像が得られる。Ｘ線グリ
ッドを用いる方法（二較べＸ線グリッドに吸収される直
接Ｘ線の損失を避けろことができ、そのためＸ線管球負
荷が減り被曝線量が減少でとる。また目ｆ動形ＸＩＭグ
リッドを用いなくともリス縞は出現しない。(Video of invention) As is clear from the above explanation, this invention (according to
Since the scattered radiation is of low frequency, it is commercially available, and even if the image is taken without using an X-ray grid, a scattered radiation removed image can be obtained. Compared to the method using an X-ray grid, the loss of direct X-rays absorbed by the X-ray grid can be avoided, which reduces the X-ray tube load and reduces the exposure dose. Even if it is not used, squirrel stripes will not appear.
エアギャグ（Ｇｒｏｅｄｅｌ法）と較べた場合（こは、
拡大率が少なくなし、ＸＭＡ管焦点焦点る幾何学的ボケ
が小さい画像を得ることが可能となる。When compared with air gag (Groedel method)
It is possible to obtain an image with a small magnification and a small geometric blur caused by the focus of the XMA tube.
またＸ線グリッドを用い撮影した場合をこけ、Ｘ線グリ
ッドと平行な散乱線はＸ線グリッドを通過し除去できな
いが、これらの散乱線画像に対しても散乱線画像相当の
低周波画像を製造し差し引くことにより散乱線除去が可
能となる。In addition, when imaging using an X-ray grid, scattered rays parallel to the X-ray grid pass through the X-ray grid and cannot be removed, but low-frequency images equivalent to scattered ray images can be produced for these scattered ray images. Scattered radiation can be removed by subtracting it.
電気的Ｘ線画像システムＱこおいてＸ線グ’Ｊ ｙド法
に替わる実用的であり有効なＸ線画像の散乱線除法効果
がある。In the electrical X-ray imaging system Q, there is a practical and effective X-ray image scattering ray removal effect that replaces the X-ray grid method.
第１図は電気的Ｘ線画像システムの一例を示すブロック
図である。第２図囚、■、０、はたたみ込みろ波を説明
するための図である。FIG. 1 is a block diagram showing an example of an electrical X-ray imaging system. Figure 2 is a diagram for explaining convolutional filtering.
Claims (1)
、ディジタルフルオログラフィ、コンピュータラジオグ
ラフィ、ディジタルアンギオグラフィなどがあげられる
。これらの電気的Ｘ線画像形成システムにおいて、被検
体とＸ線検出器間に、Ｘ線グリッド又はエアギャブ（Ｇ
ｒｏｅｄｅｌ法）を使用せずとも、散乱線が低周波画像
から成り立つことを利用し、Ｘ線検出装置とＸ線像入力
装置と画像処理装置と画像出力装置を使用し、Ｘ線原画
像から散乱線画像に相当する低周波画像を作製し、原画
像から低周波画像を差し引くことにより、Ｘ線画像の散
乱線除去画像を製造する方法。Examples of X-ray image forming systems include digital radiography, digital fluorography, computer radiography, and digital angiography. In these electrical X-ray imaging systems, an X-ray grid or air gab (G
roedel method), the fact that scattered rays consist of low-frequency images can be used to detect scattered rays from the original X-ray image by using an X-ray detection device, an X-ray image input device, an image processing device, and an image output device. A method of producing a scattered radiation removed image of an X-ray image by creating a low-frequency image corresponding to a line image and subtracting the low-frequency image from the original image.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP59257138A JPS61133847A (en) | 1984-12-04 | 1984-12-04 | Promation of image clear of scattered line in x ray image |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP59257138A JPS61133847A (en) | 1984-12-04 | 1984-12-04 | Promation of image clear of scattered line in x ray image |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPS61133847A true JPS61133847A (en) | 1986-06-21 |
Family
ID=17302242
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP59257138A Pending JPS61133847A (en) | 1984-12-04 | 1984-12-04 | Promation of image clear of scattered line in x ray image |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS61133847A (en) |
Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH04180056A (en) * | 1990-11-15 | 1992-06-26 | Fuji Photo Film Co Ltd | Method for processing radiograph |
| JP4612754B2 (en) * | 2000-02-04 | 2011-01-12 | キヤノン株式会社 | Image acquisition apparatus and image acquisition method |
| JP2015100543A (en) * | 2013-11-26 | 2015-06-04 | 富士フイルム株式会社 | Radiation image processing apparatus, method and program |
| JP2016032623A (en) * | 2014-03-10 | 2016-03-10 | 富士フイルム株式会社 | Radiation image processing apparatus, method and program |
| JP2016198665A (en) * | 2013-03-28 | 2016-12-01 | 富士フイルム株式会社 | Radiation image processing device and method and program |
| JP2017056257A (en) * | 2016-12-27 | 2017-03-23 | 富士フイルム株式会社 | Radiation image processing device, method and program |
| JP2017099967A (en) * | 2017-03-02 | 2017-06-08 | 富士フイルム株式会社 | Radiation image photographing device, radiation image photographing method, and radiation image photographing program |
| JP2017100022A (en) * | 2017-03-08 | 2017-06-08 | 富士フイルム株式会社 | Radiation image processing device, method and program |
| US10762384B2 (en) | 2015-04-15 | 2020-09-01 | Konica Minolta, Inc. | Radiation image capture system and body system estimation method with scatter reduction |
-
1984
- 1984-12-04 JP JP59257138A patent/JPS61133847A/en active Pending
Cited By (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH04180056A (en) * | 1990-11-15 | 1992-06-26 | Fuji Photo Film Co Ltd | Method for processing radiograph |
| JP4612754B2 (en) * | 2000-02-04 | 2011-01-12 | キヤノン株式会社 | Image acquisition apparatus and image acquisition method |
| JP2016198665A (en) * | 2013-03-28 | 2016-12-01 | 富士フイルム株式会社 | Radiation image processing device and method and program |
| JP2015100543A (en) * | 2013-11-26 | 2015-06-04 | 富士フイルム株式会社 | Radiation image processing apparatus, method and program |
| JP2016032623A (en) * | 2014-03-10 | 2016-03-10 | 富士フイルム株式会社 | Radiation image processing apparatus, method and program |
| US10045746B2 (en) | 2014-03-10 | 2018-08-14 | Fujifilm Corporation | Radiation image processing apparatus, method, and medium |
| US10762384B2 (en) | 2015-04-15 | 2020-09-01 | Konica Minolta, Inc. | Radiation image capture system and body system estimation method with scatter reduction |
| JP2017056257A (en) * | 2016-12-27 | 2017-03-23 | 富士フイルム株式会社 | Radiation image processing device, method and program |
| JP2017099967A (en) * | 2017-03-02 | 2017-06-08 | 富士フイルム株式会社 | Radiation image photographing device, radiation image photographing method, and radiation image photographing program |
| JP2017100022A (en) * | 2017-03-08 | 2017-06-08 | 富士フイルム株式会社 | Radiation image processing device, method and program |
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