JP2003024320A - Linear motion type x-ray tomography apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To easily extract the tomographic face image of a desired site by using a plurality of radiographing images of different radiographing enlargement ratios in a linear motion type X-ray tomography apparatus. SOLUTION: The X-ray tomography apparatus is provided with an X-ray photographic constitution body provided with an X-ray source for generating X-rays to a subject and an X-ray image pickup means for detecting X-rays transmitted by the subject, a linear movement dividing means for linearly moving the X-ray photographic constitution body in the state of making the X-ray source and the X-ray image pickup means oppose each other at a fixed distance across the subject, a movement measuring means for measuring the linear moving direction of the X-ray photographic constitution body, a photographic image part for drawing a photographic image at the X-ray image pickup means, a photographic image control means for controlling the photographic image at this photographic image part, an enlargement ratio correcting means for correcting the enlargement ratio of the photographic image at the photographic image part and a photographic image synthesizing means for superposing and synthesizing the photographic image corrected by this enlargement ratio correction means.

Description

【発明の詳細な説明】Detailed Description of the Invention

【０００１】[0001]

【発明の属する技術分野】この発明は、直線運動型Ｘ線
断層撮影装置に係り、特に撮影拡大率の異なる複数の撮
影像を用いて所望部位の断層面画像を容易に抽出するこ
とのできる直線運動型Ｘ線断層撮影装置に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a linear motion type X-ray tomography apparatus, and more particularly to a straight line which makes it possible to easily extract a tomographic plane image of a desired portion using a plurality of photographed images having different photographing magnifications. The present invention relates to a moving X-ray tomography apparatus.

【０００２】[0002]

【従来の技術】Ｘ線断層撮影装置としての歯科用断層撮
影装置においては、リニア断層撮影法（線形断層撮影
法）が、一般的な断層撮影法として利用されている。こ
のリニア断層撮影法は、Ｘ線源（管球）とＸ線撮影手段
（フィルムカセット）とが相対して患者の回りを回転す
るが、Ｘ線源（管球）とＸ線撮影手段（フィルムカセッ
ト）とはＸ線の照射方向に動くことなく、Ｘ線源とＸ線
撮像手段との移動は、Ｘ線の照射方向とは直角方向に移
動し、断層域外を撮影と同時にボケさせる方法を採って
いる。2. Description of the Related Art A linear tomography method (linear tomography method) is used as a general tomography method in a dental tomography apparatus as an X-ray tomography apparatus. In this linear tomography, the X-ray source (tube) and the X-ray imaging means (film cassette) rotate around the patient while the X-ray source (tube) and the X-ray imaging means (film cassette) rotate. A cassette) does not move in the X-ray irradiation direction, but the X-ray source and the X-ray imaging means move in a direction perpendicular to the X-ray irradiation direction, and the outside of the tomographic region is blurred simultaneously with imaging. I am collecting.

【０００３】また、このようなＸ線撮影装置としては、
例えば、特開平７−２３９３９号公報に開示されてい
る。この公報に記載のものは、被写体にＸ線を発生する
Ｘ線源と、被写体を通過したＸ線を検出するＸ線撮像手
段とを、被写体を間にして相互に対向し、直線移動させ
ながらＸ線照射を行い、被写体の撮影像をＸ線撮像手段
で取り込みながらＸ線撮影を行うものである。Further, as such an X-ray imaging apparatus,
For example, it is disclosed in Japanese Patent Laid-Open No. 7-23939. In the device described in this publication, an X-ray source for generating X-rays on an object and an X-ray imaging means for detecting X-rays passing through the object are opposed to each other with the object in between and are linearly moved. The X-ray irradiation is performed, and the X-ray imaging is performed while the captured image of the subject is captured by the X-ray imaging means.

【０００４】[0004]

【発明が解決しようとする課題】ところが、従来、Ｘ線
断層撮影装置においては、断層域が数ｍｍ程度と狭く、
フィルム上で、断層域を外れたＸ線源（管球）側又はＸ
線撮影手段（フィルムカセット）側のいずれかの解剖学
的構造がボケるため、目的部位を断層域に入れるために
は、患者の位置付けを正確に行わなければならない。However, in the conventional X-ray tomography apparatus, the tomographic region is as narrow as several mm,
On the film, X-ray source (tube) side or X outside the tomographic region
Since any anatomical structure on the side of the radiographic means (film cassette) is blurred, the patient must be accurately positioned in order to put the target site in the tomographic region.

【０００５】また、１回の位置付けで幾通りかの断層領
域を少しづつずらした断層領域を得た場合であっても、
臼歯部の歯牙４本程度の断層領域しか得られず、口腔内
領域全体の断層撮影を一度に行うことは困難であった。Further, even when a slice area obtained by slightly shifting some slice areas by one positioning is obtained,
Only a tomographic region of about 4 teeth in the molar region was obtained, and it was difficult to perform tomography of the entire oral region at one time.

【０００６】更に、特開平７−２３９３９号公報のＸ線
撮影装置においては、Ｘ線源又はＸ線撮像手段のどちら
か一方を固定させた状態で、Ｘ線撮像手段の検出面に対
して垂直方向に移動させることによって、従来と同様
に、任意断面の断面像が再構成する。つまり、Ｘ線源又
はＸ線撮像手段のどちらか一方を移動して得られる各画
像は、Ｘ線源又はＸ線撮像手段のいずれかの位置に応じ
て決定される単純な比例関数に基づいて、拡大あるいは
縮小されて得られるものである。しかしながら、Ｘ線源
又はＸ線撮像手段のいずれか一方を固定して他方を移動
させることにより、発生する拡大率の変化（増加率又は
増加量）が任意断面の断面像再構成に与える影響につい
ては、述べられていない。Further, in the X-ray imaging apparatus disclosed in Japanese Patent Laid-Open No. 7-23939, with either one of the X-ray source and the X-ray imaging means fixed, the vertical direction with respect to the detection surface of the X-ray imaging means. By moving in the direction, the cross-sectional image of an arbitrary cross section is reconstructed as in the conventional case. That is, each image obtained by moving either the X-ray source or the X-ray imaging means is based on a simple proportional function determined according to the position of either the X-ray source or the X-ray imaging means. , Is obtained by being enlarged or reduced. However, by fixing one of the X-ray source and the X-ray imaging means and moving the other, the influence of the change in the enlargement ratio (increase ratio or increase amount) that occurs on the cross-sectional image reconstruction of an arbitrary cross-section. Is not mentioned.

【０００７】また、断層撮影方法においては、所望部位
の位置決めは、容易ではなく、また、装置自体も複雑な
動きをしなければならず、更に、撮影時間も長く、再現
性を得るのも困難であり、このため、インプラント等を
埋設するのに、誤った情報を提供するおそれがあった。Further, in the tomographic imaging method, it is not easy to position a desired portion, and the apparatus itself has to make complicated movements. Further, the imaging time is long and reproducibility is difficult to obtain. Therefore, there is a possibility that incorrect information may be provided when implanting an implant or the like.

【０００８】[0008]

【課題を解決するための手段】そこで、この発明は、上
述の不都合を除去するために、被写体にＸ線を発生する
Ｘ線源と前記被写体を通過したＸ線を検出するＸ線撮像
手段とが備えられたＸ線撮影構成体を設け、前記被写体
を間にして前記Ｘ線源と前記Ｘ線撮像手段とを一定距離
に相互に対向して前記Ｘ線撮影構成体を直線移動させる
直線移動駆動手段を設け、前記Ｘ線撮影構成体の直線移
動距離を計測する移動計測手段を設け、前記Ｘ線撮像手
段には撮影像を画く撮影画像部を設け、この撮影画像部
での撮影像を制御する撮影像制御手段を設け、前記撮影
画像部での撮影像の拡大率補正を行う拡大率補正手段を
設け、この拡大率補正手段で補正された撮影像を重ね合
わせて合成する撮影像合成手段を設けたことを特徴とす
る。In order to eliminate the above-mentioned inconvenience, the present invention comprises an X-ray source for generating X-rays on a subject and an X-ray imaging means for detecting X-rays passing through the subject. A linear movement for linearly moving the X-ray imaging structure with the object in between and the X-ray source and the X-ray imaging means facing each other at a constant distance. Driving means is provided, movement measuring means for measuring the linear movement distance of the X-ray imaging structure is provided, and the X-ray imaging means is provided with a photographed image section for drawing a photographed image. A photographic image control means for controlling is provided, a magnifying power correction means for correcting the magnifying power of the photographic image in the photographic image part is provided, and the photographic images corrected by the magnifying power correction means are superposed and combined. Means are provided.

【０００９】[0009]

【発明の実施の形態】この発明は、被写体にＸ線を発生
するＸ線源と被写体を通過したＸ線を検出するＸ線撮像
手段とを、被写体を間にして相互に対向し、且つ、Ｘ線
源とＸ線撮像手段との距離を一定に設定し、Ｘ線撮影構
成体を直線移動させながらＸ線照射を行い、任意の時間
毎に被写体の撮影像をＸ線源撮像手段で取り込みながら
Ｘ線撮影を行い、このとき、被写体は予め固定されてい
るため、ある基準点を予め設定すれば、その基準点に合
わせて撮影像の拡大率は、各々の位置により決定され、
取り込まれた複数枚の撮影像を拡大又は縮小し、その撮
影像を重ね合わせて合成することにより、所望部位の断
層面画像を容易に生成することができる。BEST MODE FOR CARRYING OUT THE INVENTION According to the present invention, an X-ray source for generating X-rays on an object and an X-ray imaging means for detecting X-rays passing through the object are opposed to each other with the object in between, and The distance between the X-ray source and the X-ray imaging means is set constant, X-ray irradiation is performed while linearly moving the X-ray imaging structure, and a captured image of the subject is captured by the X-ray source imaging means at arbitrary time intervals. While performing X-ray photography, at this time, since the subject is fixed in advance, if a certain reference point is set in advance, the magnifying power of the captured image is determined according to each reference point,
It is possible to easily generate a tomographic plane image of a desired portion by enlarging or reducing the captured multiple captured images and superimposing the captured images and combining them.

【００１０】[0010]

【実施例】以下図面に基づいてこの発明の実施例を詳細
且つ具体的に説明する。図１〜１８は、この発明の実施
例を示すものである。図１８において、２は例えば歯列
等の被写体Ｍの断層撮影を行う直線運動型Ｘ線断層撮影
装置である。この直線運動型Ｘ線断層撮影装置２におい
ては、被写体ＭにＸ線を発生するＸ線源４と被写体Ｍを
通過したＸ線を検出するＸ線撮像手段６とが備えられた
Ｘ線撮影構成体８を設け、被写体Ｍを間にしてＸ線源４
とＸ線撮像手段６とを一定距離に相互に対向してＸ線撮
影構成体８を直線移動させる直線移動駆動手段１０を設
け、Ｘ線撮影構成体８の直線移動距離を計測する移動計
測手段１２を設け、Ｘ線撮像手段６には撮影像を画く撮
影画像部６Ａを設け、この撮影画像部６Ａでの撮影像を
制御する撮影像制御手段１４を設け、撮影画像部６Ａで
の撮影像の拡大率補正を行う拡大率補正手段１６を設
け、この拡大率補正手段１６で補正された撮影像を重ね
合わせて合成する撮影像合成手段１８を設け、これら撮
影像制御手段１４と拡大率補正手段１６と撮影像合成手
段１８とを一体にした制御装置２０を設けている。Ｘ線
撮影構成体８は、Ｘ線源４を保持する保持部８Ａと、こ
の保持部８ＡとＸ線撮像手段６とを連結した連結部８Ｂ
とからなる。また、制御装置２０には、Ｘ線源４と直線
移動駆動手段１０と移動計測手段１２とが連絡してい
る。Embodiments of the present invention will be described in detail and specifically with reference to the drawings. 1 to 18 show an embodiment of the present invention. In FIG. 18, reference numeral 2 is a linear motion X-ray tomography apparatus for performing tomography of a subject M such as a dentition. The linear motion X-ray tomography apparatus 2 is provided with an X-ray imaging configuration including an X-ray source 4 that generates X-rays on a subject M and an X-ray imaging unit 6 that detects X-rays that have passed through the subject M. The X-ray source 4 is provided with the body 8 and the subject M in between.
And a X-ray imaging means 6 are opposed to each other at a constant distance, and a linear movement driving means 10 for linearly moving the X-ray imaging structure 8 is provided, and a movement measuring means for measuring the linear movement distance of the X-ray imaging structure 8. 12, the X-ray imaging means 6 is provided with a photographed image portion 6A for drawing a photographed image, and the photographed image control means 14 for controlling the photographed image in this photographed image portion 6A is provided, and the photographed image in the photographed image portion 6A is provided. Magnification ratio correcting means 16 for correcting the magnification ratio, and photographed image synthesizing means 18 for superimposing and synthesizing the photographed images corrected by the magnification ratio correcting means 16, and the photographed image control means 14 and the magnification ratio correcting means. A control device 20 in which the means 16 and the captured image synthesizing means 18 are integrated is provided. The X-ray imaging structure 8 has a holding portion 8A that holds the X-ray source 4, and a connecting portion 8B that connects the holding portion 8A and the X-ray imaging means 6.
Consists of. Further, the control device 20 is in communication with the X-ray source 4, the linear movement driving means 10, and the movement measuring means 12.

【００１１】Ｘ線撮像手段６は、受光面２２を有し、二
次元Ｘ線イメージセンサとしての画像センサー（例え
ば、ＴＦＴ（Ｔｈｉｎ Ｆｉｌｍ Ｔｒａｎｓｉｓｔｏ
ｒ）、ＭＯＳ（Ｍｅｔａｌ Ｏｘｉｄｅ Ｓｅｍｉｃｏ
ｎｄｕｃｔｏｒ）、ＣＣＤ（Ｃｈａｒｇｅ Ｃｏｕｐｌ
ｅｄ Ｄｅｖｉｃｅ）、ＸＩＩ（Ｘ線イメージインテン
シファイア）、ＦＰＤ（Ｆｌａｔ Ｐａｎｅｌ Ｄｅｔ
ｅｃｔｏｒ）、ＣｄＴｅセンサ（カドミウムテルルセン
サ）に代表されるいずれか）からなる。The X-ray image pickup means 6 has a light receiving surface 22 and is an image sensor (for example, a TFT (Thin Film Transistor) as a two-dimensional X-ray image sensor.
r), MOS (Metal Oxide Semico)
nductor), CCD (Charge Couple)
ed Device), XII (X-ray image intensifier), FPD (Flat Panel Det)
vector) and a CdTe sensor (one of which is represented by a cadmium tellurium sensor).

【００１２】移動計測手段１２には、被写体Ｍの断層面
位置に目印となる不透過性のアダプタ２４が設けられて
いる。The movement measuring means 12 is provided with an impermeable adapter 24 which serves as a mark at the position of the tomographic plane of the subject M.

【００１３】この移動計測手段１２は、例えば、ＰＳＤ
素子（Ｐｏｓｉｔｉｏｎ Ｓｅｎｓｉｔｉｖｅ Ｄｅｔ
ｅｃｔｏｒ）、エンコーダ、反射型位置計測装置等に代
表されるいずれかからなる。The movement measuring means 12 is, for example, a PSD.
Element (Position Sensitive Det
vector), an encoder, a reflection type position measuring device, or the like.

【００１４】拡大率補正手段１６は、任意の位置での撮
影像の一辺拡大率をＧとし、この位置に重ね合わされる
複数の撮影像の拡大率をＢ１、Ｂ２、Ｂ３…とすると
き、補正係数をＢ１／Ｇ、Ｂ２／Ｇ、Ｂ３／Ｇ…とし、
撮影像合成手段１８は、これらの補正された撮影像を重
ね合わせる機能を有する。The magnifying power correcting means 16 corrects when the magnifying power of one side of a photographed image at an arbitrary position is G and the magnifying powers of a plurality of photographed images superimposed at this position are B1, B2, B3 ... The coefficients are B1 / G, B2 / G, B3 / G ...
The captured image synthesizing means 18 has a function of superposing these corrected captured images.

【００１５】Ｘ線撮像手段６の撮影画像部６Ａは、連続
的に撮影する方式と任意時間毎に撮影する方式とを備え
ている。The photographed image section 6A of the X-ray image pickup means 6 has a method of continuously photographing and a method of photographing every arbitrary time.

【００１６】次に、この実施例の作用を説明する。Next, the operation of this embodiment will be described.

【００１７】直線運動型Ｘ線断層撮影装置２において
は、任意の断層画像を生成するものであり、図１８に示
す如く、Ｘ線源４とＸ線撮像手段６の受光面２２とを対
向配置し、そして、図１７に示す如く、Ｘ線源４とＸ線
撮像手段６との相互間の距離を一定に保ちつつ、被写体
Ｍに対し拡大率の異なる撮影像を複数枚取得し（ステッ
プ１０２）、その後、任意断層面を決定し（ステップ１
０４）、そして、この決定された任意断層面の撮影像の
拡大率に合わせて、各撮影像を拡大又は縮小し、任意断
層面の大きさに合わす拡大率補正の計算を行い（ステッ
プ１０６）、この補正された撮影像を重ね合わせ（ステ
ップ１０８）、断層像を生成する（ステップ１１０）。In the linear motion type X-ray tomography apparatus 2, an arbitrary tomographic image is generated, and as shown in FIG. 18, the X-ray source 4 and the light receiving surface 22 of the X-ray imaging means 6 are arranged so as to face each other. Then, as shown in FIG. 17, while keeping the distance between the X-ray source 4 and the X-ray imaging means 6 constant, a plurality of photographed images with different magnifications are obtained for the subject M (step 102). ), And then determine the arbitrary fault plane (Step 1
04), and enlarges or reduces each captured image in accordance with the determined enlargement ratio of the captured image of the arbitrary tomographic plane, and performs magnification ratio correction calculation to match the size of the arbitrary tomographic plane (step 106). Then, the corrected photographed images are superposed (step 108) to generate a tomographic image (step 110).

【００１８】この実施例においては、図２に示す如く、
Ｘ線源４から受光面２２までの距離を一定とし、且つ、
被写体ＭをＸ線源４とＸ線撮像手段６の受光面２２との
間に置くことによって、拡大率の変化を大きくとること
を可能にする。この図２においては、縦軸に一辺拡大
率、横軸にＸ線源４から被写体Ｍまでの距離を示し、本
願発明と特開平７−２３９３９号公報の発明とを比較し
ている。In this embodiment, as shown in FIG.
The distance from the X-ray source 4 to the light receiving surface 22 is constant, and
By placing the subject M between the X-ray source 4 and the light-receiving surface 22 of the X-ray imaging means 6, it is possible to make a large change in the enlargement ratio. In FIG. 2, the vertical axis represents the one-side magnification ratio and the horizontal axis represents the distance from the X-ray source 4 to the subject M, and the invention of the present application and the invention of JP-A-7-23939 are compared.

【００１９】本願発明においては、図１に示す如く、被
写体Ｍを間にしてＸ線源４とＸ線撮像手段６とを一定距
離に保ちつつ、被写体ＭからＸ線撮像手段６の受光面２
２までの距離Ｂの初期値を２０ｍｍとし、この距離Ｂを
２０ｍｍ〜９８０ｍｍまで移動させ、一辺拡大率を増加
させていく。このとき、全長はＡ＋Ｂ＝１０００ｍｍを
常に保っている。一方、特開平７−２３９３９号公報の
発明のものは、図１９に示す如く、被写体Ｍを間にして
Ｘ線撮像手段２０２及び被写体Ｍを固定したままＸ線源
２０４を移動させて行く。被写体ＭからＸ線撮像手段２
０２までの距離Ｂを一定に保ったまま、Ｘ線源２０４か
ら被写体Ｍまでの距離Ａを被写体Ｍに近づけていく。こ
の動きをグラフ化すると、図２の曲線のようになる。In the present invention, as shown in FIG. 1, the X-ray source 4 and the X-ray image pickup means 6 are kept at a constant distance with the object M in between, and the light-receiving surface 2 of the X-ray image pickup means 6 from the subject M.
The initial value of the distance B up to 2 is set to 20 mm, the distance B is moved from 20 mm to 980 mm, and the one side expansion rate is increased. At this time, the total length is always A + B = 1000 mm. On the other hand, in the invention disclosed in Japanese Patent Laid-Open No. 7-23939, as shown in FIG. 19, the X-ray source 204 is moved with the subject M in between while the X-ray imaging means 202 and the subject M are fixed. X-ray imaging means 2 from subject M
The distance A from the X-ray source 204 to the subject M is brought closer to the subject M while keeping the distance B up to 02 constant. When this movement is graphed, it becomes like the curve in FIG.

【００２０】このとき、この従来の図１９においては、
図１との比較のために、Ｂを２０ｍｍ一定、Ａを９８０
ｍｍ〜２０ｍｍまで変化させている。At this time, in this conventional FIG.
For comparison with FIG. 1, B is constant at 20 mm and A is 980
It is changed from mm to 20 mm.

【００２１】この結果、図２に示す如く、本願発明にお
いては、少ない移動距離で一辺拡大率の大幅な変化が得
られるが、特開平７−２３９３９号公報の発明において
は、一辺拡大率の多少の変化しか得られないことが分か
る。As a result, as shown in FIG. 2, in the present invention, a large change in the one-side enlargement ratio can be obtained with a small moving distance, but in the invention of Japanese Patent Laid-Open No. 7-23939, the one-side enlargement ratio is slightly different. It turns out that only the change of can be obtained.

【００２２】以下に、本願発明の一辺拡大率の変化につ
いて、詳細に説明する。The change in the one side enlargement ratio of the present invention will be described in detail below.

【００２３】つまり、図３に示す如く、Ｘ線を発生する
Ｘ線源４と、被写体Ｍを通過したＸ線を検出するＸ線撮
像手段６の受光面２２とを被写体Ｍを間にして直線状に
配置する。このとき、Ｘ線源４とＸ線撮像手段６の受光
面２２の相互間の距離を一定に保つ。また、被写体Ｍ
は、ある大きさを持ったものである。That is, as shown in FIG. 3, the X-ray source 4 for generating X-rays and the light-receiving surface 22 of the X-ray imaging means 6 for detecting the X-rays passing through the subject M are straight lines with the subject M in between. Arranged in a shape. At this time, the distance between the X-ray source 4 and the light-receiving surface 22 of the X-ray imaging means 6 is kept constant. Also, the subject M
Is a certain size.

【００２４】次に、Ｘ線源４から被写体Ｍまでの距離を
Ａ、被写体ＭからＸ線撮像手段６の受光面２２までの距
離をＢとする。このとき、被写体Ｍでの一辺拡大率Ｇ_２
は、 Ｇ_２＝（Ａ＋Ｂ）／Ａ……（１） となる。Next, the distance from the X-ray source 4 to the subject M is A, and the distance from the subject M to the light receiving surface 22 of the X-ray imaging means 6 is B. At this time, the one side enlargement ratio G ₂ of the subject M
Becomes G ₂ = (A + B) / A (1)

【００２５】そして、被写体Ｍでの面積拡大率ＧＳ
_２は、 ＧＳ_２＝（Ｇ_２）^２＝｛（Ａ＋Ｂ）／Ａ｝^２ ……（２） となる。Then, the area expansion rate GS of the subject M
₂ is GS ₂ = (G ₂ ) ² = {(A + B) / A} ² (2).

【００２６】図４は、複数の被写体Ｍ１、Ｍ２、Ｍ３で
ある歯列の断層撮影を行う本願発明の実施例である。こ
の被写体Ｍ１、Ｍ２、Ｍ３はそれぞれ大きさ、Ｘ線吸収
率は同一とし、Ｘ線源４から被写体Ｍ１、Ｍ２、Ｍ３に
照射されるＸ線強度が均一なものとする。被写体Ｍ１、
Ｍ２、Ｍ３の透過後にＸ線撮像手段６の受光面２２に投
影される信号強度は、面積成分と黒化度成分とに分割さ
れる。面積拡大率が大きいもの程、投影面積は大きくな
り、黒化度成分は小さくなる。FIG. 4 shows an embodiment of the present invention in which tomography of a plurality of objects M1, M2 and M3 is performed. The subjects M1, M2, and M3 have the same size and the same X-ray absorption rate, and the X-ray intensity emitted from the X-ray source 4 to the subjects M1, M2, and M3 is uniform. Subject M1,
The signal intensity projected on the light receiving surface 22 of the X-ray imaging means 6 after passing through M2 and M3 is divided into an area component and a blackening component. The larger the area expansion rate, the larger the projected area and the smaller the blackening component.

【００２７】次に、被写体Ｍ２に関して、信号強度を求
める。被写体Ｍ２に照射される信号強度をＩ_Ｅとし、被
写体Ｍ２の面積をＳ_０（Ｓ_０≠０）とし、Ｘ線撮像手段
６の受光面２２での被写体Ｍ２の面積をＳ_２としたと
き、Ｘ線撮像手段６の受光面２２での被写体Ｍ２の面積
Ｓ_２は、 Ｓ_２＝Ｓ_０＊ＧＳ_２ で示される。Next, the signal strength of the subject M2 is calculated.
Meru. I is the signal intensity applied to the subject M2_EAnd the cover
The area of image M2 is S₀(S₀≠ 0), and X-ray imaging means
The area of the subject M2 on the light receiving surface 22 of 6 is S_TwoAnd
Area of the subject M2 on the light receiving surface 22 of the X-ray imaging means 6
S_TwoIs S_Two= S₀* GS_Two Indicated by.

【００２８】そして、面積拡大率ＧＳ_２によってＸ線撮
像手段６の受光面２２が受ける信号強度Ｉ_Ｄ２は、次式
となる。 Ｉ_Ｄ２＝Ｉ_Ｅ／Ｓ_２ ＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_２） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_２）^２｝ ＝Ｉ_Ｅ／［Ｓ_０＊｛（Ａ＋Ｂ）／Ａ｝^２ ］……（３）The area expansion rate GS_TwoBy x-ray
Signal intensity I received by the light receiving surface 22 of the image means 6_D2Is the expression
Becomes     I_D2= I_E/ S_Two           = I_E/ (S₀* GS_Two)           = I_E/ {S₀* (G_Two)^Two}             = I_E/ [S₀* {(A + B) / A}^Two  ] …… (3)

【００２９】同様に、被写体Ｍ１に関して、信号強度を
求める。ここでも、被写体Ｍ１、Ｍ２、Ｍ３の各被写体
の面積は、全て同一のＳ_０（Ｓ_０≠０）とし、また、被
写体Ｍ１、Ｍ２、Ｍ３に照射される信号強度も、全て同
一のＩ_Ｅとする。被写体Ｍ２を中心にして、Ｘ線撮像手
段６の受光面２２と平行に引いた線をＹ軸、この受光面
２２と垂直に引いた線をＸ軸とする。被写体Ｍ１は、被
写体Ｍ２から距離Ｌだけ、Ｘ線源４側に配置されてい
る。Similarly, the signal strength of the subject M1 is obtained. Here again, the areas of the subjects M1, M2, and M3 are all the same S ₀ (S ₀ ≠ 0), and the signal intensities irradiated to the subjects M1, M2, and M3 are all the same I _E And A line drawn in parallel with the light receiving surface 22 of the X-ray imaging means 6 around the subject M2 is taken as a Y axis, and a line drawn perpendicularly to the light receiving surface 22 is taken as an X axis. The subject M1 is arranged on the X-ray source 4 side a distance L from the subject M2.

【００３０】よって、Ｘ線源４から被写体Ｍ１までの距
離はＡ−Ｌ、被写体Ｍ１からＸ線撮像手段６の受光面２
２までの距離はＢ＋Ｌで表される。このとき、被写体Ｍ
１の一辺拡大率Ｇ_１は、 となる。Therefore, the distance from the X-ray source 4 to the subject M1 is A-L, and the light-receiving surface 2 of the X-ray imaging means 6 from the subject M1.
The distance to 2 is represented by B + L. At this time, the subject M
One side expansion ratio G ₁ of ₁ is Becomes

【００３１】そして、被写体Ｍ１での面積拡大率ＧＳ_１
は、 ＧＳ_１＝（Ｇ_１）^２＝｛（Ａ＋Ｂ）／（Ａ−Ｌ）｝^２ ……（５） となる。Then, the area expansion rate GS ₁ of the subject M1
Becomes GS ₁ = (G ₁ ) ² = {(A + B) / (AL)} ² (5).

【００３２】次に、被写体Ｍ１に関して信号強度を求め
ると、Ｘ線撮像手段６の受光面２２での被写体Ｍ１の面
積をＳ_１とするとき、Ｘ線撮像手段６の受光面２２での
被写体Ｍ１の面積Ｓ_１は、 Ｓ_１＝Ｓ_０＊ＧＳ_１ で示される。Next, the signal strength of the subject M1 is calculated.
Then, the surface of the subject M1 on the light receiving surface 22 of the X-ray imaging means 6
Product S₁, The light receiving surface 22 of the X-ray imaging means 6
Area S of subject M1₁Is S₁= S₀* GS₁ Indicated by.

【００３３】そして、面積拡大率ＧＳ_１によってＸ線撮
像手段６の受光面２２が受ける信号強度Ｉ_D１は、次式
となる。 Ｉ_D１＝Ｉ_Ｅ／Ｓ_１ ＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_１） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_１）^２｝ ＝Ｉ_Ｅ／〔Ｓ_０＊｛（Ａ＋Ｂ）／（Ａ−Ｌ）｝^２〕……（６）The signal intensity I _D1 received by the light receiving surface 22 of the X-ray imaging means 6 by the area enlargement ratio GS _{1 is given} by the following equation. I _D1 = I _E / S ₁ = I _E / (S ₀ * GS ₁ ) = I _E / {S ₀ * (G ₁ ) ² } = I _E / [S ₀ * {(A + B) / (A−L) )} ² ] …… (6)

【００３４】同様に、被写体Ｍ３に関して、信号強度を
求める。ここでも、被写体面積Ｓ_０及び被写体Ｍ３に照
射される信号強度Ｉ_Ｅは、同一であるから、被写体Ｍ３
は、被写体Ｍ２から距離ＬだけＸ線撮像手段６の受光面
２２側に配置されている。Similarly, the signal strength of the subject M3 is obtained. Again, since the subject area S ₀ and the signal intensity I _E applied to the subject M3 are the same, the subject M3
Are arranged on the light receiving surface 22 side of the X-ray imaging means 6 by a distance L from the subject M2.

【００３５】よって、Ｘ線源４から被写体Ｍ３までの距
離はＡ＋Ｌ、被写体Ｍ３からＸ線撮像手段６の受光面２
２までの距離はＢ−Ｌで表される。このとき、被写体Ｍ
３の一辺拡大率Ｇ_３は、 となる。Therefore, the distance from the X-ray source 4 to the subject M3 is A + L, and the light receiving surface 2 of the X-ray imaging means 6 from the subject M3.
The distance to 2 is represented by BL. At this time, the subject M
One side expansion rate G ₃ of ₃ is Becomes

【００３６】そして、被写体Ｍ３での面積拡大率ＧＳ_３
は、 ＧＳ_３＝（Ｇ_３）^２＝｛（Ａ＋Ｂ）／（Ａ＋Ｌ）｝^２ ……（８） となる。Then, the area expansion rate GS ₃ of the subject M3
Becomes GS ₃ = (G ₃ ) ² = {(A + B) / (A + L)} ² (8).

【００３７】次に、被写体Ｍ３に関して信号強度を求め
ると、Ｘ線撮像手段６の受光面２２での被写体Ｍ３の面
積をＳ_３とするとき、Ｘ線撮像手段６の受光面２２での
被写体Ｍ３の面積Ｓ_３は、 Ｓ_３＝Ｓ_０＊ＧＳ_３ で示される。Next, the signal strength of the subject M3 is calculated.
Then, the surface of the subject M3 on the light receiving surface 22 of the X-ray imaging means 6
Product S_Three, The light receiving surface 22 of the X-ray imaging means 6
Area S of subject M3_ThreeIs S_Three= S₀* GS_Three Indicated by.

【００３８】そして、面積拡大率ＧＳ_３によってＸ線撮
像手段６の受光面２２が受ける信号強度Ｉ_Ｄ３は、次式
となる。 Ｉ_Ｄ３＝Ｉ_Ｅ／Ｓ_３ ＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_３） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_３）^２｝ ＝Ｉ_Ｅ／［Ｓ_０＊｛（Ａ＋Ｂ）／（Ａ＋Ｌ）｝^２］……（９）Area expansion rate GS_ThreeBy x-ray
Signal intensity I received by the light receiving surface 22 of the image means 6_D3Is the expression
Becomes       I_D3= I_E/ S_Three             = I_E/ (S₀* GS_Three)             = I_E/ {S₀* (G_Three)^Two}             = I_E/ [S₀* {(A + B) / (A + L)}^Two] …… (9)

【００３９】ここで、実状に則したＡ，Ｂ，Ｌの各距離
値を設定し、Ｘ線源４とＸ線撮像手段６の受光面２２と
の距離を一定に保ったまま、被写体Ｍ１、Ｍ２、Ｍ３の
位置をＸ線源４に接近した位置（Ａ＜Ｂ）、Ｘ線源４及
びＸ線撮像手段６の受光面２２からの距離が同じ位置
（Ａ＝Ｂ）、Ｘ線撮像手段６の受光面２２に接近した位
置（Ａ＞Ｂ）について、一辺拡大率、面積拡大率および
Ｘ線撮像手段６の受光面２２が受ける信号強度の例を、
以下に示す（図５参照）。Here, the respective distance values of A, B, L according to the actual condition are set, and the distance between the X-ray source 4 and the light-receiving surface 22 of the X-ray imaging means 6 is kept constant, and the subject M1, The positions of M2 and M3 are close to the X-ray source 4 (A <B), the positions of the X-ray source 4 and the light-receiving surface 22 of the X-ray imaging unit 6 are the same (A = B), and the X-ray imaging unit. 6 at the position close to the light receiving surface 22 (A> B), an example of the one side magnification, the area enlargement ratio, and the signal intensity received by the light receiving surface 22 of the X-ray imaging means 6,
It is shown below (see FIG. 5).

【００４０】＜条件１＞被写体Ｍ１、Ｍ２、Ｍ３の面積
をＳ_０（Ｓ_０≠０）とし、Ａ＝２５０ｍｍ、Ｂ＝７５０
ｍｍ、Ｌ＝１０ｍｍ、被写体Ｍ１、Ｍ２、Ｍ３に照射さ
れる信号強度をＩ_Ｅとする。<Condition 1> When the areas of the subjects M1, M2 and M3 are S ₀ (S ₀ ≠ 0), A = 250 mm, B = 750
mm, L = 10 mm, and the signal intensity applied to the subjects M1, M2, and M3 is I _E.

【００４１】被写体Ｍ１、Ｍ２、Ｍ３の各々の一辺拡大
率については、被写体Ｍ１の一辺拡大率Ｇ_１１は、
（４）式より、 Ｇ_１１＝（２５０＋７５０）／（２５０−１０）＝４．
１６６７ 被写体Ｍ２の一辺拡大率Ｇ_１２は、（１）式より、 Ｇ_１２＝（２５０＋７５０）／２５０＝４．００００ 被写体Ｍ３の一辺拡大率Ｇ_１３は、は、（７）式より、 Ｇ_１３＝（２５０＋７５０）／（２５０＋１０）＝３．
８４６２ となる。Regarding the one side enlargement ratio of each of the subjects M1, M2 and M3, the one side enlargement ratio G ₁₁ of the subject M1 is
From the equation (4), G ₁₁ = (250 + 750) / (250-10) = 4.
1667 The one-sided enlargement ratio G ₁₂ of the subject M2 is G ₁₂ = (250 + 750) /250=4.0000 from the formula (1) The one-sided enlargement ratio G ₁₃ of the subject M3 is G ₁₃ = from the formula (7) (250 + 750) / (250 + 10) = 3.
It becomes 8462.

【００４２】被写体Ｍ１、Ｍ２、Ｍ３の各々の面積拡大
率については、被写体Ｍ１の面積拡大率ＧＳ_１１は、
（５）式より、 ＧＳ_１１＝（Ｇ_１１）^２＝１７．３６１１ 被写体Ｍ２の面積拡大率ＧＳ_１２は、（２）式より、 ＧＳ_１２＝（Ｇ_１２）^２＝１６．００００ 被写体Ｍ３の面積拡大率ＧＳ_１３は、（８）式より、 ＧＳ_１３＝（Ｇ_１３）^２＝１４．７９２９ となる。Regarding the area expansion rate of each of the objects M1, M2 and M3, the area expansion rate GS ₁₁ of the object M1 is
From the formula (5), GS ₁₁ = (G ₁₁ ) ² = 17.3611 The area expansion ratio GS ₁₂ of the subject M2 is calculated from the formula (2) as follows: GS ₁₂ = (G ₁₂ ) ² = 16.0000 The area of the subject M3 The expansion rate GS ₁₃ is GS ₁₃ = (G ₁₃ ) ² = 14.7929 from the equation (8).

【００４３】次に、夫々の面積拡大率によってＸ線撮像
手段６の受光面２２が受ける信号強度Ｉ_Ｄを求める。Next, the signal intensity I _D received by the light-receiving surface 22 of the X-ray imaging means 6 is obtained by the area enlargement ratio.

【００４４】被写体Ｍ１について、面積拡大率１７．３
６１１によってＸ線撮像手段６の受光面２２が受ける信
号強度をＩ_Ｄ１１とすると、（６）式より、 Ｉ_Ｄ１１＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_１１） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_１１）^２｝ ＝Ｉ_Ｅ／（１７．３６１１＊Ｓ_０） ＝０．０５７６（Ｉ_Ｅ／Ｓ_０） となる。For the subject M1, the area expansion rate 17.3
If the signal strength of the light-receiving surface 22 receives the X-ray imaging means 6 and _{I D11} by 611, from equation _{(6), I D11 = I E / (} S 0 * GS 11) = I E / {S 0 * (G ^{_{11) 2} = I E /(17.3611*S}} 0) = 0.0576 a _(I E _{/ S} 0).

【００４５】被写体Ｍ２について、面積拡大率１６．０
０００によってＸ線撮像手段６の受光面２２が受ける信
号強度をＩ_Ｄ１２とすると、（３）式より、 Ｉ_Ｄ１２ ＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_１２） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_１２）^２｝ ＝Ｉ_Ｅ／（１６．００００＊Ｓ_０） ＝０．０６２５（Ｉ_Ｅ／Ｓ_０） となる。For the subject M2, the area expansion rate is 16.0.
000, the signal intensity received by the light-receiving surface 22 of the X-ray imaging means 6 is I _{D12. From} equation (3), I _D12 = I _E / (S ₀ * GS ₁₂ ) = I _E / {S ₀ * (G ^{_{12) 2} = I E /(16.0000*S}} 0) = 0.0625 a _(I E _{/ S} 0).

【００４６】被写体Ｍ３について、面積拡大率４．７９
２９によってＸ線撮像手段６の受光面２２が受ける信号
強度をＩ_Ｄ１３とすると、（９）式より、 Ｉ_Ｄ１３＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_１３） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_１３）^２｝ ＝Ｉ_Ｅ／（１４．７９２９＊Ｓ_０） ＝０．０６７６（Ｉ_Ｅ／Ｓ_０） となる。For the subject M3, the area expansion rate is 4.79.
_Assuming that the signal intensity received by the light receiving surface 22 of the X-ray imaging unit 6 by 29 is I _D13 , I _D13 = I _E / (S ₀ * GS ₁₃ ) = I _E / {S ₀ * (G ₁₃ ) ² } = I _E /(14.7929*S ₀ ) = 0.0676 (I _E / S ₀ ).

【００４７】＜条件２＞被写体Ｍ１、Ｍ２、Ｍ３の面積
をＳ_０（Ｓ_０≠０）とし、Ａ＝５００ｍｍとし、Ｂ＝５
００ｍｍとし、Ｌ＝１０ｍｍとし、被写体Ｍ１、Ｍ２、
Ｍ３に照射される信号強度をＩ_Ｅとする。<Condition 2> The areas of the subjects M1, M2 and M3 are S ₀ (S ₀ ≠ 0), A = 500 mm, and B = 5.
00 mm, L = 10 mm, subjects M1, M2,
The signal intensity applied to M3 is I _E.

【００４８】被写体Ｍ１、Ｍ２、Ｍ３の各々の一辺拡大
率については、被写体Ｍ１の一辺拡大率Ｇ_２１は、
（４）式より、 Ｇ_２１＝（５００＋５００）／（５００−１０）＝２．
０４０８ 被写体Ｍ２の一辺拡大率Ｇ_２２は、（１）式より、 Ｇ_２２＝（５００＋５００）／５００＝２．００００ 被写体Ｍ３の一辺拡大率Ｇ_２３は、（７）式より Ｇ_２３＝（５００＋５００）／（５００＋１０）＝１．
９６０８ となる。[0048] For the object M1, M2, M3 respectively side magnification of a side enlargement factor _{G 21} of the object M1 is
From the equation (4), G ₂₁ = (500 + 500) / (500-10) = 2.
Side enlargement factor _{G 22} of 0408 subjects M2 is (1) from the equation, one side enlargement factor _{G 23} of the _{G 22 = (500 + 500)} /500=2.0000 object M3 _{is, (7) G 23 = (} 500 + 500) from the equation / (500 + 10) = 1.
It becomes 9608.

【００４９】被写体Ｍ１、Ｍ２、Ｍ３の各々の面積拡大
率については、被写体Ｍ１の面積拡大率ＧＳ_２１は、
（５）式より、 ＧＳ_２１＝（Ｇ_２１）^２＝４．１６４９ 被写体Ｍ２の面積拡大率ＧＳ_２２は、（２）式より、 ＧＳ_２２＝（Ｇ_２２）^２＝４．００００ 被写体Ｍ３の面積拡大率ＧＳ_２３は、（８）式より、 ＧＳ_２３＝（Ｇ_２３）^２＝３．８４４７ となる。Regarding the area expansion rate of each of the objects M1, M2, M3, the area expansion rate GS ₂₁ of the object M1 is
From the formula (5), GS ₂₁ = (G ₂₁ ) ² = 4.1649 The area expansion ratio GS ₂₂ of the subject M2 is calculated from the formula (2) as follows: GS ₂₂ = (G ₂₂ ) ² = 4.0000 Area of the subject M3 The enlargement ratio GS ₂₃ is GS ₂₃ = (G ₂₃ ) ² = 3.8447 from the equation (8).

【００５０】次に、夫々の面積拡大率によってＸ線撮像
手段６の受光面２２が受ける信号強度Ｉ_Ｄを求める。Next, the signal intensity I _D received by the light receiving surface 22 of the X-ray image pickup means 6 is obtained by the area enlargement ratio.

【００５１】被写体Ｍ１について、面積拡大率４．１６
４９によってＸ線撮像手段６の受光面２２が受ける信号
強度をＩ_Ｄ２１とすると、（６）式より、 Ｉ_Ｄ２１＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_２１） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_２１）^２｝ ＝Ｉ_Ｅ／（４．１６４９＊Ｓ_０） ＝０．２４０１（Ｉ_Ｅ／Ｓ_０） となる。For the subject M1, the area expansion rate 4.16.
_Assuming that the signal intensity received by the light receiving surface 22 of the X-ray imaging means 6 by 49 is I _D21 , from the equation (6), I _D21 = I _E / (S ₀ * GS ₂₁ ) = I _E / {S ₀ * (G ^{_{21) 2} = I E /(4.1649*S}} 0) = 0.2401 a _(I E _{/ S} 0).

【００５２】被写体Ｍ２について、面積拡大率４．００
００によってＸ線撮像手段６の受光面２２が受ける信号
強度をＩ_Ｄ２２とすると、（３）式より、 Ｉ_Ｄ２２＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_２２) ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_２２）^２｝ ＝Ｉ_Ｅ／（４．００００＊Ｓ_０） ＝０．２５００（Ｉ_Ｅ／Ｓ_０） となる。For the subject M2, the area expansion rate 4.00
If the signal strength of the light-receiving surface 22 receives the X-ray imaging means 6 by 00 and _{I D22,} (3) from the _{equation, I D22 = I E / (} S 0 * GS 22) = I E / {S 0 * (G ^{_{22) 2} = I E /(4.0000*S}} 0) = 0.2500 a _(I E _{/ S} 0).

【００５３】被写体Ｍ３について、面積拡大率３．８４
４７によってＸ線撮像手段６の受光面２２が受ける信号
強度をＩ_Ｄ２３とすると、（９）式より、 Ｉ_Ｄ２３＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_２３） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_２３）^２｝ ＝Ｉ_Ｅ／（３．８４４７＊Ｓ_０） ＝０．２６０１（Ｉ_Ｅ／Ｓ_０） となる。For the subject M3, the area expansion rate is 3.84.
_Assuming that the signal intensity received by the light-receiving surface 22 of the X-ray imaging means 6 by 47 is I _D23 , I _D23 = I _E / (S ₀ * GS ₂₃ ) = I _E / {S ₀ * (G ^{_{23) 2} = I E /(3.8447*S}} 0) = 0.2601 a _(I E _{/ S} 0).

【００５４】＜条件３＞被写体Ｍ１、Ｍ２、Ｍ３の面積
をＳ_０（Ｓ_０≠０）とし、Ａ＝７５０ｍｍとし、Ｂ＝２
５０ｍｍとし、Ｌ＝１０ｍｍとし、被写体Ｍ１、Ｍ２、
Ｍ３に照射される信号強度をＩ_Ｅとする。<Condition 3> The areas of the subjects M1, M2, and M3 are S ₀ (S ₀ ≠ 0), A = 750 mm, and B = 2.
50 mm, L = 10 mm, and subjects M1, M2,
The signal intensity applied to M3 is I _E.

【００５５】被写体Ｍ１、Ｍ２、Ｍ３の各々の一辺拡大
率については、被写体Ｍ１の一辺拡大率Ｇ_３１は、
（４）式より、 Ｇ_３１＝（７５０＋２５０）／（７５０−１０）＝１．
３５１４ 被写体Ｍ２の一辺拡大率Ｇ_３２は、（１）式より、 Ｇ_３２＝（７５０＋２５０）／７５０＝１．３３３３ 被写体Ｍ３の一辺拡大率Ｇ_３３は、（７）式より、 Ｇ_３３＝（７５０＋２５０）／（７５０＋１０）＝１．
３１５８ となる。Regarding the one side enlargement ratio of each of the subjects M1, M2 and M3, the one side enlargement ratio G ₃₁ of the subject M1 is
From the equation (4), G ₃₁ = (750 + 250) / (750-10) = 1.
3514 The one-sided enlargement ratio G ₃₂ of the subject M2 is G ₃₂ = (750 + 250) /750=1.3333 from the formula (1). The one-sided enlargement ratio G ₃₃ of the subject M3 is G ₃₃ = (750 + 250) from the formula (7). ) / (750 + 10) = 1.
It becomes 3158.

【００５６】被写体Ｍ１、Ｍ２、Ｍ３の各々の面積拡大
率については、被写体Ｍ１の面積拡大率ＧＳ_３１は、
（５）式より、 ＧＳ_３１＝（Ｇ_３１）^２＝１．８２６２ 被写体Ｍ２の面積拡大率ＧＳ_３２は、（２）式より、 ＧＳ_３２＝（Ｇ_３２）^２＝１．７７７８ 被写体Ｍ３の面積拡大率ＧＳ_３３は、（８）式より、 ＧＳ_３３＝（Ｇ_３３）^２＝１．７３１３ となる。Regarding the area expansion rate of each of the objects M1, M2 and M3, the area expansion rate GS ₃₁ of the object M1 is
From the formula (5), GS ₃₁ = (G ₃₁ ) ² = 1.8262 The area expansion ratio GS ₃₂ of the subject M2 is calculated from the formula (2) as follows: GS ₃₂ = (G ₃₂ ) ² = 1.77778 The area of the subject M3 The expansion rate GS ₃₃ is GS ₃₃ = (G ₃₃ ) ² = 1.7313 from the equation (8).

【００５７】次に、夫々の面積拡大率によってＸ線撮像
手段６の受光面２２が受ける信号強度Ｉ_Ｄを求める。Next, the signal intensity I _D received by the light-receiving surface 22 of the X-ray imaging means 6 is obtained by the area enlargement ratio.

【００５８】被写体Ｍ１について、面積拡大率１．８２
６２によってＸ線撮像手段６の受光面２２が受ける信号
強度をＩ_Ｄ３１とすると、（６）式より、 Ｉ_Ｄ３１＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_３１） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_３１）^２｝ ＝Ｉ_Ｅ／（１．８２６２＊Ｓ_０） ＝０．５４７６（Ｉ_Ｅ／Ｓ_０） となる。For the subject M1, the area expansion rate 1.82
_Assuming that the signal intensity received by the light receiving surface 22 of the X-ray imaging means 6 by 62 is I _D31 , from the equation (6), I _D31 = I _E / (S ₀ * GS ₃₁ ) = I _E / {S ₀ * (G ^{_{31) 2} = I E /(1.8262*S}} 0) = 0.5476 a _(I E _{/ S} 0).

【００５９】被写体Ｍ２について、面積拡大率１．７７
７８によってＸ線撮像手段６の受光面２２が受ける信号
強度をＩ_Ｄ３２とすると、（３）式より、 Ｉ_Ｄ３２＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_３２) ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_３２）^２｝ ＝Ｉ_Ｅ／（１．７７７８＊Ｓ_０） ＝０．５６２５（Ｉ_Ｅ／Ｓ_０） となる。With respect to the subject M2, the area expansion rate is 1.77.
_Assuming that the signal intensity received by the light receiving surface 22 of the X-ray imaging means 6 by 78 is I _D32 , I _D32 = I _E / (S ₀ * GS ₃₂ ) = I _E / {S ₀ * (G ^{_{32) 2} = I E /(1.7778*S}} 0) = 0.5625 a _(I E _{/ S} 0).

【００６０】被写体Ｍ３について、面積拡大率１．７３
１３によってＸ線撮像手段６の受光面２２が受ける信号
強度をＩ_Ｄ３３とすると、（９）式より、 Ｉ_Ｄ３３＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_３３） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_３３）^２｝ ＝Ｉ_Ｅ／（１．７３１３＊Ｓ_０） ＝０．５７７６（Ｉ_Ｅ／Ｓ_０） となる。For the subject M3, the area expansion rate 1.73
_Supposing that the signal intensity received by the light receiving surface 22 of the X-ray imaging means 6 by 13 is I _D33 , from the formula (9), I _D33 = I _E / (S ₀ * GS ₃₃ ) = I _E / {S ₀ * (G ^{_{33) 2} = I E /(1.7313*S}} 0) = 0.5776 a _(I E _{/ S} 0).

【００６１】以上の結果をまとめると、図６の様にな
る。The above results are summarized as shown in FIG.

【００６２】この図６においては、被写体Ｍ１の面積拡
大率は１７．３６１１から１．８２６２（一辺拡大率は
４．１６６７から１．３５１４）へ、被写体Ｍ２の面積
拡大率は１６．００００から１．７７７８（一辺拡大率
は４．００００から１．３３３３）へ、被写体Ｍ３の面
積拡大率は１４．７９２９から１．７３１３（一辺拡大
率は３．８４６２から１．３１５８）へと大きく変化
し、このときのＸ線撮像手段６の受光面２２での信号強
度は各々、０．０５７６（Ｉ_Ｅ／Ｓ_０）から０．５４７
６（Ｉ_Ｅ／Ｓ_０）へ、０．０６２５（Ｉ_Ｅ／Ｓ_０）から
０．５６２５（Ｉ _Ｅ／Ｓ_０）へ、０．０６７６（Ｉ_Ｅ／
Ｓ_０）から０．５７７６（Ｉ_Ｅ／Ｓ_０）へと、変化して
いる。In FIG. 6, the area of the subject M1 is expanded.
The large rate is from 17.3611 to 1.8262 (one side expansion rate is
Area of subject M2 from 4.1667 to 1.3514)
The expansion rate is from 16.0000 to 1.7778 (One side expansion rate
From 4.0000 to 1.3333), the surface of subject M3
Product expansion rate is from 14.7929 to 1.7313 (One side expansion
The rate greatly changed from 3.8462 to 1.3158)
However, at this time, the signal intensity on the light receiving surface 22 of the X-ray imaging means 6 is increased.
Each degree is 0.0576 (I_E/ S₀) To 0.547
6 (I_E/ S₀) To 0.0625 (I_E/ S₀) From
0.5625 (I _E/ S₀) To 0.0676 (I_E/
S₀) To 0.5776 (I_E/ S₀)
There is.

【００６３】次に、条件２の被写体Ｍ２を、求める断層
面とした時の画像再構築の例を示す。Next, an example of image reconstruction when the subject M2 under condition 2 is the tomographic plane to be obtained will be described.

【００６４】＜条件１＞の画像について、まず、条件２
での被写体Ｍ２の一辺拡大率Ｇ_２２に対する条件１での
被写体Ｍ２の一辺拡大率Ｇ_１２の補正係数をｋ_１２とす
ると、補正係数ｋ_１２と一辺拡大率との関係は、次式で
示される。 （Ｇ_１２＊ｋ_１２）／Ｇ_２２＝１Regarding the image of <condition 1>, first, the condition 2
Assuming that the correction coefficient of the one-side expansion rate G ₁₂ of the subject M2 under the condition 1 with respect to the one-side expansion rate G ₂₂ of the subject M2 is k ₁₂ , the relationship between the correction coefficient k ₁₂ and the one-side expansion rate is expressed by the following equation. . (G ₁₂ * k ₁₂ ) / G ₂₂ = 1

【００６５】よって、条件２での被写体Ｍ２の一辺拡大
率に対する条件１での被写体Ｍ２の一辺拡大率の補正係
数ｋ_１２は、 ｋ_１２＝Ｇ_２２／Ｇ_１２ ＝２．００００／４．００００＝０．５０００ となる。Therefore, one side of the subject M2 under condition 2 is enlarged.
Correction factor for the one-side expansion ratio of the subject M2 under the condition 1 for the ratio
A few k₁₂Is k₁₂= G₂₂/ G₁₂ = 2.0000 / 4.0000 = 0.5000 Becomes

【００６６】従って、条件１の被写体Ｍ１、Ｍ２、Ｍ３
の各々の一辺拡大率を、０．５０００倍する。Therefore, the subjects M1, M2, M3 of condition 1
Each side expansion factor is multiplied by 0.5000.

【００６７】被写体Ｍ１の補正後の一辺拡大率Ｇ_１１’
は、 Ｇ_１１’＝４．１６６７＊ ０．５０００＝２．０８３
４ となる。One side enlargement ratio G _{11 '} after correction of the subject M1
Is G _{11 ′} = 4.1667 * 0.5000 = 2.083
4.

【００６８】Ｘ線撮像手段６の受光面２２が受ける信号
強度Ｉ_D１１、被写体Ｍ１の面積拡大率ＧＳ_１１は、補
正後信号強度Ｉ_D１１’、被写体Ｍ１の補正後面積拡大
率ＧＳ_１１’に夫々置き換えられる。よって、（６）式
より、 Ｉ_D１１’＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_１１’） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_１１’）^２｝ ＝Ｉ_Ｅ／（Ｓ_０＊４．３４０６） ＝０．２３０４（Ｉ_Ｅ／Ｓ_０） となる。The signal intensity I _D11 received by the light-receiving surface 22 of the X-ray imaging means 6 and the area enlargement ratio GS ₁₁ of the subject M1 are respectively the corrected signal intensity I _{D11 '} and the corrected area enlargement ratio GS _11' of the subject M1. Will be replaced. Therefore, from the equation (6), I _{D11 ′} = I _E / (S ₀ * GS _{11 ′} ) = I _E / {S ₀ * (G _{11 ′} ) ² } = I _E / (S ₀ * 4.3406) = 0.2304 a _(I E _{/ S} 0).

【００６９】被写体Ｍ２の補正後の一辺拡大率Ｇ_１２’
は、 Ｇ_１２’＝４．００００＊ ０．５０００＝２．０００
０ となる。One-side magnification G _{12 '} after correction of subject M2
Is G _{12 ′} = 4.0000 * 0.5000 = 0.200.
It becomes 0.

【００７０】Ｘ線撮像手段６の受光面２２が受ける信号
強度Ｉ_D１２、被写体Ｍ２の面積拡大率ＧＳ_１２は、補
正後信号強度Ｉ_D１２’、被写体Ｍ２の補正後面積拡大
率ＧＳ_１２’に夫々置き換えられる。よって、（３）式
より、 Ｉ_D１２’＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_１２’） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_１２’）^２｝ ＝Ｉ_Ｅ／（Ｓ_０＊４．００００） ＝０．２５００（Ｉ_Ｅ／Ｓ_０） となる。The signal intensity I _D12 received by the light receiving surface 22 of the X-ray imaging means 6 and the area enlargement ratio GS ₁₂ of the subject M2 are respectively the corrected signal intensity I _{D12 '} and the corrected area enlargement ratio GS _12' of the subject M2. Will be replaced. Therefore, from the equation (3), I _{D12 ′} = I _E / (S ₀ * GS _{12 ′} ) = I _E / {S ₀ * (G _{12 ′} ) ² } = I _E / (S ₀ * 4.0000) = 0.2500 a _(I E _{/ S} 0).

【００７１】被写体Ｍ３の補正後の一辺拡大率Ｇ_１３’
は、 Ｇ_１３’＝３．８４６２＊ ０．５０００＝１．９２３
１ となる。One-side magnification G _{13 '} after correction of subject M3
Is G _{13 ′} = 3.8462 * 0.5000 = 1.923
It becomes 1.

【００７２】Ｘ線撮像手段６の受光面２２が受ける信号
強度Ｉ_D１３、被写体Ｍ３の面積拡大率ＧＳ_１３は、補
正後信号強度Ｉ_D１３’、被写体Ｍ３の補正後面積拡大
率ＧＳ_１３’に夫々置き換えられる。よって、（９）式
より、 Ｉ_D１３’＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_１３’） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_１３’）^２｝ ＝Ｉ_Ｅ／（Ｓ_０＊３．６９８３） ＝０．２７０４（Ｉ_Ｅ／Ｓ_０） となる。The signal intensity I _D13 received by the light-receiving surface 22 of the X-ray imaging means 6 and the area enlargement ratio GS ₁₃ of the subject M3 are respectively the corrected signal intensity I _{D13 '} and the corrected area enlargement ratio GS _13' of the subject M3. Will be replaced. Therefore, from the equation (9), I _{D13 ′} = I _E / (S ₀ * GS _{13 ′} ) = I _E / {S ₀ * (G _{13 ′} ) ² } = I _E / (S ₀ * 3.6983) = 0.2704 (I _E / S ₀ ).

【００７３】＜条件２＞の画像について、被写体Ｍ２の
一辺拡大率は基準であるため、被写体Ｍ１、Ｍ３もその
ままの一辺拡大率であり、信号強度Ｉ_Dもそのままの値
となる。被写体Ｍ１の一辺拡大率Ｇ_２１は、Ｇ_２１＝
２．０４０８となる。被写体Ｍ１の信号強度Ｉ
_D２１は、Ｉ_D２１＝０．２４０１（Ｉ_Ｅ／Ｓ_０）とな
る。被写体Ｍ２の一辺拡大率Ｇ_２２は、Ｇ_２２＝２．０
０００となる。被写体Ｍ２の信号強度Ｉ_D１２は、Ｉ
_D１２＝０．２５００（Ｉ_Ｅ／Ｓ_０）となる。被写体Ｍ
３の一辺拡大率Ｇ_２３は、Ｇ_２３＝１．９６０８とな
る。被写体Ｍ３の信号強度Ｉ_D１３は、Ｉ_D１３＝０．２
６０１（Ｉ_Ｅ／Ｓ_０）となる。In the image of <Condition 2>, since the one-side enlargement ratio of the subject M2 is a reference, the subject M1 and M3 are also the one-side enlargement ratio, and the signal intensity I _D is also the same value. The one side enlargement ratio G ₂₁ of the subject M1 is G ₂₁ =
It becomes 2.0408. Signal strength I of subject M1
_D21 is I _D21 = 0.2401 (I _E / S ₀ ). Side enlargement factor _{G 22} of the object M2 _is, G 22 = 2.0
000. The signal strength I _D12 of the subject M2 is I
_D12 = 0.2500 becomes _(I E / _{S 0).} Subject M
The one-sided enlargement ratio G ₂₃ of 3 is G ₂₃ = 1.9608. The signal intensity I _D13 of the subject M3 is I _D13 = 0.2.
601 a _(I E / _{S 0).}

【００７４】＜条件３＞の画像について、まず、条件２
での被写体Ｍ２の一辺拡大率Ｇ_２２に対する条件３での
被写体Ｍ２の一辺拡大率Ｇ_３２の補正係数をｋ_３２とす
ると、補正係数ｋ_３２と一辺拡大率との関係は、次式で
示される。 （Ｇ_３２＊ｋ_３２）／Ｇ_２２＝１Regarding the image of <condition 3>, first, the condition 2
Assuming that the correction coefficient of the one side enlargement ratio G ₃₂ of the subject M2 under the condition 3 with respect to the one side enlargement ratio G ₂₂ of the subject M2 is k ₃₂ , the relationship between the correction coefficient k ₃₂ and the one side enlargement ratio is expressed by the following equation. . (G ₃₂ * k ₃₂ ) / G ₂₂ = 1

【００７５】よって、条件２での被写体Ｍ２の一辺拡大
率に対する条件３での被写体Ｍ２の一辺拡大率の補正係
数ｋ_３２は、 ｋ_３２＝Ｇ_２２／Ｇ_３２＝２．００００／１．３３３３
＝１．５０００ となる。Therefore, the correction coefficient k ₃₂ of the one side enlargement ratio of the subject M2 under the condition 3 with respect to the one side enlargement ratio of the subject M2 under the condition 2 is k ₃₂ = G ₂₂ / G ₃₂ = 2.0000 / 1.3333
= 1.5000.

【００７６】従って、条件３の被写体Ｍ１、Ｍ２、Ｍ３
の各々の一辺拡大率を、１．５０００倍する。Therefore, the subjects M1, M2, M3 of condition 3
Each side expansion factor is multiplied by 1.5000.

【００７７】被写体Ｍ１の補正後の一辺拡大率Ｇ_３１’
は、 Ｇ_３１’＝１．３５１４＊ １．５０００＝２．０２７
１ となる。One-side magnification G _{31 '} after correction of the subject M1
Is G _{31 '} = 1.3514 * 1.5000 = 2.027
It becomes 1.

【００７８】Ｘ線撮像手段６の受光面２２が受ける信号
強度Ｉ_D３１、被写体Ｍ１の面積拡大率ＧＳ_３１は、補
正後信号強度Ｉ_D３１’、被写体Ｍ１の補正後面積拡大
率ＧＳ_D３１’に夫々置き換えられる。よって、（６）
式より、 Ｉ_D３１’＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_３１’） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_３１’）^２｝ ＝Ｉ_Ｅ／（Ｓ_０＊４．１０９１） ＝０．２４３４（Ｉ_Ｅ／Ｓ_０） となる。The signal intensity I _D31 received by the light-receiving surface 22 of the X-ray imaging means 6 and the area enlargement ratio GS ₃₁ of the subject M1 are respectively the corrected signal intensity I _{D31 '} and the corrected area enlargement ratio GS _D31' of the subject M1. Will be replaced. Therefore, (6)
From the formula, I _{D31 ′} = I _E / (S ₀ * GS _{31 ′} ) = I _E / {S ₀ * (G _{31 ′} ) ² } = I _E / (S ₀ * 4.1091) = 0.2434 ( I _E / S ₀ ).

【００７９】被写体Ｍ２の補正後の一辺拡大率Ｇ_３２’
は、 Ｇ_３２’＝１．３３３３＊ １．５０００＝２．０００
０ となる。One-side magnification G _{32 '} after correction of subject M2
Is G _{32 '} = 1.3333 * 1.5000 = 2.000
It becomes 0.

【００８０】Ｘ線撮像手段６の受光面２２が受ける信号
強度Ｉ_D３２、被写体Ｍ２の面積拡大率ＧＳ_３２は、被
写体Ｍ２の補正後面積拡大率ＧＳ_３２’に置き換えられ
る。よって、（３）式より、 Ｉ_D３２’＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_３２’） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_３２’）^２｝ ＝Ｉ_Ｅ／（Ｓ_０＊４．００００） ＝０．２５００（Ｉ_Ｅ／Ｓ_０） となる。The signal intensity I _D32 received by the light receiving surface 22 of the X-ray imaging means 6 and the area expansion rate GS ₃₂ of the subject M2 are replaced with the corrected area expansion rate GS _{32 '} of the subject M2. Therefore, according to the equation (3), I _{D32 '} = I _E / (S ₀ * GS _32' ) = I _E / {S ₀ * (G _{32 '} ) ² } = I _E / (S ₀ * 4.00) = 0.2500 a _(I E _{/ S} 0).

【００８１】被写体Ｍ３の補正後の一辺拡大率Ｇ_３３’
は、 Ｇ_３３’＝１．３１５８＊ １．５０００＝１．９７３
７ となる。One-side enlargement ratio G _{33 '} after correction of the subject M3
Is G _{33 ′} = 1.3158 * 1.5000 = 1.973
7

【００８２】Ｘ線撮像手段６の受光面２２が受ける信号
強度Ｉ_D３３、被写体Ｍ３の面積拡大率ＧＳ_３３は、補
正後信号強度Ｉ_D３３’、被写体Ｍ３の補正後面積拡大
率ＧＳ_３３’に夫々置き換えられる。よって、（９）式
より、 Ｉ_D３３’＝Ｉ_Ｅ／（Ｓ_０＊ＧＳ_３３’） ＝Ｉ_Ｅ／｛Ｓ_０＊（Ｇ_３３’）^２｝ ＝Ｉ_Ｅ／（Ｓ_０＊３．８９５５） ＝０．２５６７（Ｉ_Ｅ／Ｓ_０） となる。The signal intensity I _D33 received by the light receiving surface 22 of the X-ray imaging means 6 and the area enlargement ratio GS ₃₃ of the subject M3 are respectively the corrected signal intensity I _{D33 '} and the corrected area enlargement ratio GS _33' of the subject M3. Will be replaced. Therefore, from the formula (9), I _{D33 ′} = I _E / (S ₀ * GS _{33 ′} ) = I _E / {S ₀ * (G _{33 ′} ) ² } = I _E / (S ₀ * 3.8955) = 0.2567 (I _E / S ₀ ).

【００８３】以上の結果をまとめると、図７の様にな
る。The above results are summarized as shown in FIG.

【００８４】次いで、図８〜１２に基づいて説明する。Next, description will be made with reference to FIGS.

【００８５】条件２の被写体Ｍ２を基準として条件２の
画像に、補正された条件１の画像および補正された条件
３の画像を重ね合わせると、図８、図９、図１０、図１
１に示す如く、被写体Ｍ１はＩ_{D１１’、}Ｉ_{D２１’、}Ｉ
_D３１’の異なる信号強度が、異なる大きさをもって、
ズレて現れる。When the corrected image of condition 1 and the corrected image of condition 3 are superimposed on the image of condition 2 with the subject M2 of condition 2 as a reference, FIG. 8, FIG. 9, FIG.
As shown in FIG. 1, the subject M1 is I _{D11 ',} I _D21', I
Different signal strengths of _{D31 '} have different magnitudes,
Appears to shift.

【００８６】同様に、被写体Ｍ３もＩ_{D１３’、}Ｉ
_{D２３’、}Ｉ_D３３’の異なる信号強度が、異なる大きさ
をもって、ズレて現れる。被写体Ｍ２については、Ｉ
_{D１２’、}Ｉ_{D２２’、}Ｉ_D３２’が同じ大きさの信号強
度をもって重なって現れる。Similarly, the subject M3 also has _{ID 13 ',} I
The different signal intensities of _{D23 'and} I _D33' appear to be different in magnitude. For subject M2, I
_{D12 ',} I _{D22', and} I _{D32 '} appear in an overlapping manner with the same signal strength.

【００８７】これは、求める被写体画像上の任意の部分
はズレることなく黒化度成分が大きくなり、一方、それ
以外の部分は重なりがズレて黒化度成分が小さくなるこ
とを示している。This shows that the blackening degree component is large without any shift in the desired image on the subject image, while the blackening degree component is small in the other portions, and the blackening degree component is small.

【００８８】ここでは、三枚の撮像画をもとに補正を掛
け、重ね合わせた例を示したが、元となる撮像画の枚数
を多くし同様の作業をすることによって、ズレずに重な
る像はさらに黒化度を増し、求める被写体とそれ以外の
被写体との境界（求める被写体の輪郭）はコントラスト
が強く明確になって来る。さらに、マッハ効果によりコ
ントラストが強くなった輪郭は視覚に強く訴えることに
なり、断層像の認識を容易にする。（図１２参照）Here, an example is shown in which correction is performed based on three picked-up images and the images are superimposed, but by increasing the number of original picked-up images and performing the same work, they are not overlapped. The image further increases the degree of blackening, and the boundary between the desired subject and the other subjects (outline of the desired subject) has a strong contrast and becomes clear. Further, the contour having the increased contrast due to the Mach effect is strongly appealing to the eyes and facilitates the recognition of the tomographic image. (See Figure 12)

【００８９】また、上述した本願発明における補正後一
辺拡大率と、特開平７−２３９３９号公報の発明での補
正後一辺拡大率を比較することにより、本願発明の優位
性をより明確にする。Further, by comparing the corrected one-side enlargement ratio in the invention of the present application with the corrected one-side enlargement ratio of the invention of Japanese Patent Laid-Open No. 7-23939, the superiority of the present invention is clarified.

【００９０】特開平７−２３９３９号公報の発明に関し
ては、図２０に示す如く、本願発明と同様に、実状に則
したＡ，Ｂ，Ｌの各距離値を設定し、被写体ＭからＸ線
撮像手段２０２の受光面２０６までの距離を一定に保っ
たまま、Ｘ線源２０４から被写体Ｍ１、Ｍ２、Ｍ３まで
の距離を変化させ、一辺拡大率、面積拡大率及びＸ線撮
像手段２０２の受光面２０６が受ける信号強度の値を求
める。With respect to the invention of Japanese Patent Laid-Open No. 7-23939, as shown in FIG. 20, as in the present invention, the distance values of A, B, and L are set according to the actual condition, and X-ray imaging is performed from the subject M. While keeping the distance to the light receiving surface 206 of the means 202 constant, the distance from the X-ray source 204 to the subjects M1, M2, and M3 is changed, and the one side enlargement ratio, the area enlargement ratio, and the light receiving surface of the X-ray imaging means 202 are changed. The value of the signal strength received by 206 is determined.

【００９１】まず、被写体Ｍ１、Ｍ２、Ｍ３の面積をＳ
_０（Ｓ_０≠０）、Ｂ＝２０ｍｍ（一定）とし、Ｌ＝１０
ｍｍとし、被写体Ｍ１、Ｍ２、Ｍ３に照射される信号強
度をＩ_Ｅとし、条件１をＡ＝２５０ｍｍ、条件２をＡ＝
５００ｍｍ、条件３をＡ＝７５０ｍｍとして、一辺拡大
率、面積拡大率及び受光面が受ける信号強度を、本願発
明と同様に計算し、条件２の被写体Ｍ２を求める断層面
としたときの画像再構築の計算も同様に行った。First, the areas of the subjects M1, M2 and M3 are S
₀ (S ₀ ≠ 0), B = 20 mm (constant), L = 10
mm, the intensity of the signal emitted to the subjects M1, M2, and M3 is I _E , condition 1 is A = 250 mm, condition 2 is A =
Image reconstruction when a one-side expansion rate, an area expansion rate, and a signal intensity received by the light receiving surface are calculated in the same manner as in the present invention, assuming that the subject M2 is 500 mm and the condition 3 is A = 750 mm, and the subject M2 of the condition 2 is obtained. Was calculated in the same manner.

【００９２】以上の特開平７−２３９３９号公報の発明
の結果をまとめると、図２１、２２の様になる。The results of the invention of Japanese Patent Laid-Open No. 7-23939 described above can be summarized as shown in FIGS.

【００９３】以上の補正後一辺拡大率の結果から、本願
発明の図７及び特開平７−２３９３９号公報の発明の図
２２の補正後一辺拡大率比較を、図１３に示す。FIG. 13 shows a comparison of the corrected one side enlargement ratios of FIG. 7 of the present invention and FIG. 22 of the invention of Japanese Patent Application Laid-Open No. 7-23939 from the above results of the corrected one side enlargement ratios.

【００９４】この図１３においては、縦軸に補正後一辺
拡大率、横軸にＸ線源から被写体Ｍまでの距離を示す。In FIG. 13, the vertical axis shows the corrected one-side enlargement ratio, and the horizontal axis shows the distance from the X-ray source to the subject M.

【００９５】被写体Ｍ１の本願発明の補正後一辺拡大率
は、条件１では２．０８３４、条件２では２．０４０
８、条件３では２．０２７１であり、条件１と条件２と
の差は０．０４２６、条件２と条件３との差は０．０１
３７となる。同様に、被写体Ｍ１の特開平７−２３９３
９号公報の発明の補正後一辺拡大率は、条件１では１．
０８３４、条件２では１．０６１２、条件３では１．０
５４０であり、条件１と条件２との差は０．０２２２、
条件２と条件３との差は０．００７２となる。被写体Ｍ
３も同様に、被写体Ｍ３の本願発明の補正後一辺拡大率
は、条件１では１．９２３１、条件２では１．９６０
８、条件３では１．９７３７であり、条件１と条件２と
の差は０．０３７７、条件２と条件３との差は０．０１
２９となる。被写体Ｍ３の特開平７−２３９３９号公報
の発明の補正後一辺拡大率は条件１では１．０００１、
条件２では１．０１９６、条件３では１．０２６４であ
り、条件１と条件２との差は０．０１９５、条件２と条
件３との差は０．００６８となる。The corrected one-side enlargement ratio of the subject M1 according to the present invention is 2.0834 for condition 1 and 2.040 for condition 2.
8, condition 3 is 2.0271, the difference between condition 1 and condition 2 is 0.0426, and the difference between condition 2 and condition 3 is 0.01
37. Similarly, the subject M1 of Japanese Patent Laid-Open No. 7-2393
The corrected one-side enlargement ratio of the invention of Japanese Patent No. 9 is 1.
0834, 1.0612 in condition 2, 1.0 in condition 3
540, the difference between condition 1 and condition 2 is 0.0222,
The difference between Condition 2 and Condition 3 is 0.0072. Subject M
Similarly, the corrected one-side enlargement ratio of the subject M3 according to the present invention is 1.9231 in condition 1 and 1.960 in condition 2.
8, condition 3 is 1.9737, the difference between condition 1 and condition 2 is 0.0377, and the difference between condition 2 and condition 3 is 0.01
29. The corrected one-side enlargement ratio of the subject M3 according to the invention of Japanese Patent Application Laid-Open No. 7-23939 is 1.0001 under condition 1.
The condition 2 is 1.0196, the condition 3 is 1.0264, the difference between the condition 1 and the condition 2 is 0.0195, and the difference between the condition 2 and the condition 3 is 0.0068.

【００９６】ここで、本願発明での補正後一辺拡大率の
ズレの差は、特開平７−２３９３９号公報の発明の補正
後一辺拡大率のズレの差よりも大きく、この一辺拡大率
のズレの差が大きいほど求める断層面以外の断層像のズ
レが大きく現れ、黒化度成分が小さくなる。被写体Ｍ２
に関しては、条件２の被写体２に対して補正してあるた
め、条件１、条件２、条件３の各々の被写体Ｍ２補正後
一辺拡大率はズレることがない。このため、求める被写
体Ｍ２の断層面はズレることなく黒化度成分が大きくな
り、求める被写体の断層面とそれ以外の被写体の断層面
との境界はコントラストが強く明確になってくる。Here, the difference between the corrected one-side enlargement ratios in the present invention is larger than the difference between the corrected one-side enlargement ratios in the invention of Japanese Patent Laid-Open No. 7-23939, and the difference between the one-side enlargement ratios. The larger the difference between, the larger the deviation of the tomographic image other than the desired tomographic plane appears, and the smaller the blackening component. Subject M2
With respect to the above, since the subject 2 of condition 2 is corrected, the one-side enlargement ratio after the subject M2 correction of each of condition 1, condition 2, and condition 3 does not deviate. For this reason, the tomographic plane of the subject M2 to be obtained has a large blackening component without deviation, and the boundary between the tomographic plane of the subject to be obtained and the tomographic planes of the other subjects becomes strong and clear.

【００９７】即ち、本願発明は、特開平７−２３９３９
号公報の発明よりも、補正後一辺拡大率及び面積拡大率
の差が大きくなるため、よりマッハ効果が強調され、求
める被写体Ｍの断層面とそれ以外の被写体の断層面との
境界はコントラストが強く明確に現れる。なお、図２
１、２２には、参考のために信号強度も明記した。That is, the present invention is disclosed in JP-A-7-23939.
Since the difference between the corrected one-side enlargement ratio and the area enlargement ratio becomes larger than that in the invention of the publication, the Mach effect is further emphasized, and the boundary between the tomographic plane of the subject M to be obtained and the tomographic plane of the other subjects has a higher contrast. Appear strongly and clearly. Note that FIG.
For reference, signal strengths are also specified in Nos. 1 and 22.

【００９８】次に、被写体Ｍのズレの方向および大きさ
について説明する。Next, the direction and size of the displacement of the subject M will be described.

【００９９】図１４は被写体ＭとＸ線源４との距離がＡ
からＡ＋ｘに移動したときの、求める被写体Ｍの画像に
対し、それ以外の画像がズレて重なる位置関係の計算例
を示す。このとき、ｘは移動距離を示している。In FIG. 14, the distance between the subject M and the X-ray source 4 is A.
An example of the calculation of the positional relationship in which the image of the subject M to be obtained when moving from A to A + x is shifted and overlapped with other images will be shown. At this time, x indicates the moving distance.

【０１００】図１５は被写体Ｍ１、Ｍ２、Ｍ３の位置関
係を示す座標図である。まず、被写体Ｍ２を０とする
と、被写体Ｍ１は被写体Ｍ２からＸ軸方向に−Ｌ、Ｙ軸
方向にＰの位置に位置する。次に、被写体Ｍ３は被写体
Ｍ２からＸ軸方向にＬ、Ｙ軸方向に−Ｐの位置に位置す
る。この被写体Ｍ１、Ｍ２、Ｍ３の座標関係は変化しな
いものとする。FIG. 15 is a coordinate diagram showing the positional relationship among the subjects M1, M2, M3. First, assuming that the subject M2 is 0, the subject M1 is located at a position -L in the X-axis direction and P in the Y-axis direction from the subject M2. Next, the subject M3 is located at a position L from the subject M2 in the X-axis direction and -P in the Y-axis direction. It is assumed that the coordinate relationship between the subjects M1, M2, M3 does not change.

【０１０１】被写体Ｍ１ａ、Ｍ２ａ、Ｍ３ａを基準面と
し、被写体Ｍ１ａ、Ｍ２ａ、Ｍ３ａが距離ｘだけＸ線撮
像手段６の受光面２２側に移動した被写体を被写体Ｍ１
ｂ、Ｍ２ｂ、Ｍ３ｂとし、基準面の被写体Ｍ２ａを求め
る被写体とする。The subject M1a, M2a, M3a is used as a reference plane, and the subject M1a, M2a, M3a moved to the light receiving surface 22 side of the X-ray imaging means 6 by the distance x is the subject M1.
b, M2b, and M3b, and the subject M2a on the reference plane is the subject to be obtained.

【０１０２】次に、Ｘ線源４から受光面２２に垂直方向
に引いた軸をＸ軸とし、Ｘ軸を基準に被写体Ｍ１ａのＸ
線撮像手段６の受光面２２での断層像の距離をＱ１ａで
示し、被写体Ｍ１ｂのＸ線撮像手段６の受光面２２での
断層像の距離をＱ１ｂで示す。また、同様に、被写体Ｍ
３ａのＸ線撮像手段６の受光面２２での断層像の距離を
−Ｑ３ａで示し、被写体Ｍ３ｂの受光面２２での断層像
の距離を−Ｑ３ｂで示す。Next, the axis drawn from the X-ray source 4 in the direction perpendicular to the light-receiving surface 22 is taken as the X-axis, and the X-axis is used as a reference for the X-axis of the subject M1a.
The distance of the tomographic image on the light receiving surface 22 of the X-ray imaging unit 6 is indicated by Q1a, and the distance of the tomographic image of the subject M1b on the light receiving surface 22 of the X-ray imaging unit 6 is indicated by Q1b. Similarly, the subject M
The distance of the tomographic image on the light receiving surface 22 of the X-ray imaging unit 6 of 3a is indicated by -Q3a, and the distance of the tomographic image on the light receiving surface 22 of the subject M3b is indicated by -Q3b.

【０１０３】まず、被写体Ｍ１ａのＸ線撮像手段６の受
光面２２でのＱ１ａの長さは、次のように示される。 Ｑ１ａ＝{ｐ＊（Ａ＋Ｂ）}／（Ａ−Ｌ）……（１１）First, the length of Q1a on the light-receiving surface 22 of the X-ray imaging means 6 of the subject M1a is shown as follows. Q1a = {p * (A + B)} / (AL) …… (11)

【０１０４】被写体Ｍ１ｂのＸ線撮像手段６の受光面２
２でのＱ１ｂの長さは、次のように示される。 Ｑ１ｂ＝{ｐ＊（Ａ＋Ｂ）}／（Ａ＋ｘ−Ｌ）……（１２）Light receiving surface 2 of the X-ray imaging means 6 of the subject M1b
The length of Q1b at 2 is shown as: Q1b = {p * (A + B)} / (A + x−L) (12)

【０１０５】被写体Ｍ１ａの断層像の一辺拡大率に対す
る被写体Ｍ１ｂの断層像の一辺拡大率の補正係数をｋ
_Q１とおくと、（Ｑ１ｂ＊ｋ_Q１）／Ｑ１ａ＝１より、 ｋ_Q１＝Ｑ１ａ／Ｑ１ｂ……（１３） となる。The correction coefficient of the one side magnification of the tomographic image of the subject M1b with respect to the one side magnification of the tomographic image of the subject M1a is k.
When put to the _Q1, the from _{(Q1b * k Q1) / Q1a} = 1, k Q1 = Q1a / Q1b ...... (13).

【０１０６】この（１３）式に（１１）、（１２）の式
を代入すると、 ｋ_Q１＝[{ｐ＊（Ａ＋Ｂ）}／（Ａ−Ｌ）]／[{ｐ＊（Ａ＋Ｂ）}／（Ａ＋ｘ −Ｌ）]＝（Ａ＋ｘ−Ｌ）／（Ａ−Ｌ） ＝｛（Ａ−Ｌ）／（Ａ−Ｌ）｝＋｛ｘ／（Ａ−Ｌ）｝ ＝１＋｛ｘ／（Ａ−Ｌ）｝ となる。Substituting the expressions (11) and (12) into the expression (13), k _Q1 = [{p * (A + B)} / (AL)] / [{p * (A + B)} / (A + x−L)] = (A + x−L) / (A−L) = {(A−L) / (A−L)} + {x / (A−L)} = 1+ {x / (A−) L)}.

【０１０７】ここで、（１３）式はＱ１ａ＝Ｑ１ｂ＊ｋ
_Q１となり、ｋ_Q１＝１＋｛ｘ／（Ａ−Ｌ）｝を代入する
と、 Ｑ１ａ＝Ｑ１ｂ＊ [１＋｛ｘ／（Ａ−Ｌ）｝] Ｑ１ａ＝Ｑ１ｂ＋｛ｘ／（Ａ−Ｌ）｝＊Ｑ１ｂ Ｑ１ａ−Ｑ１ｂ＝｛ｘ／（Ａ−Ｌ）｝＊Ｑ１ｂ となる。Here, the equation (13) is Q1a = Q1b * k
_It becomes _Q1 , and when k _Q1 = 1 + {x / (AL)} is substituted, Q1a = Q1b * [1+ {x / (AL)}] Q1a = Q1b + {x / (AL)} * Q1b Q1a-Q1b = {x / (AL)} * Q1b.

【０１０８】即ち、ｘ＝０の時、被写体Ｍ１ａと被写体
Ｍ１ｂの撮影像は重なり合う。ｘが大きくなると、Ｑ１
ｂが小さくなり、被写体Ｍ１ｂの撮影像は被写体Ｍ２ａ
の撮影像の方向へと移動していく。That is, when x = 0, the photographed images of the subject M1a and the subject M1b overlap. When x becomes large, Q1
b becomes smaller, and the captured image of the subject M1b becomes the subject M2a.
It moves in the direction of the captured image of.

【０１０９】同様にして、被写体Ｍ３ａの受光面２２で
の−Ｑ３ａの長さは、次のように示される。 −Ｑ３ａ＝{−ｐ＊（Ａ＋Ｂ）}／（Ａ＋Ｌ）……（１４）Similarly, the length of -Q3a on the light receiving surface 22 of the subject M3a is shown as follows. -Q3a = {-p * (A + B)} / (A + L) (14)

【０１１０】被写体Ｍ３ｂの受光面２２での−Ｑ３ｂの
長さは、次のように示される。 −Ｑ３ｂ＝{−ｐ＊（Ａ＋Ｂ）}／（Ａ＋ｘ＋Ｌ）……（１５）The length of -Q3b on the light receiving surface 22 of the subject M3b is shown as follows. -Q3b = {-p * (A + B)} / (A + x + L) (15)

【０１１１】被写体Ｍ３ａの撮影像の一辺拡大率に対す
る被写体Ｍ３ｂの撮影像の一辺拡大率の補正係数をｋ
_Q３とおくと、（−Ｑ３ｂ＊ｋ_Q３）／−Ｑ３ａ＝１より ｋ_Q３＝−Ｑ３ａ／−Ｑ３ｂ……（１６） となる。The correction coefficient of the one side enlargement ratio of the taken image of the subject M3b to the one side enlargement ratio of the taken image of the subject M3a is k.
When put to the _Q3, the Q3a = 1 than _{k Q3 = -Q3a / -Q3b ...... (} 16) - (- Q3b * k Q3) /.

【０１１２】この（１６）式に（１４）、（１５）の式
を代入すると、 ｋ_Q３＝[{−ｐ＊（Ａ＋Ｂ）}／（Ａ＋Ｌ）]／[{−ｐ＊（Ａ＋Ｂ）}／（Ａ＋ ｘ＋Ｌ）]＝（Ａ＋ｘ＋Ｌ）／（Ａ＋Ｌ） ＝｛（Ａ＋Ｌ）／（Ａ＋Ｌ）｝＋｛ｘ／（Ａ＋Ｌ）｝ ＝１＋｛ｘ／（Ａ＋Ｌ）｝ となる。Substituting the equations (14) and (15) into the equation (16), k _Q3 = [{-p * (A + B)} / (A + L)] / [{-p * (A + B)} / (A + x + L)] = (A + x + L) / (A + L) = {(A + L) / (A + L)} + {x / (A + L)} = 1+ {x / (A + L)}.

【０１１３】ここで、（１６）式は−Ｑ３ａ＝−Ｑ３ｂ
＊ｋ_Q３となり、ｋ_Q１＝１＋｛ｘ／（Ａ＋Ｌ）｝を代入
すると、 −Ｑ３ａ＝−Ｑ３ｂ＊ [１＋｛ｘ／（Ａ＋Ｌ）｝] Ｑ３ａ＝Ｑ３ｂ＋｛ｘ／（Ａ＋Ｌ）｝＊Ｑ３ｂ Ｑ３ａ−Ｑ３ｂ＝｛ｘ／（Ａ＋Ｌ）｝＊Ｑ３ｂ となる。Here, the equation (16) is -Q3a = -Q3b
* K _Q3 , and substituting k _Q1 = 1 + {x / (A + L)}, -Q3a = -Q3b * [1+ {x / (A + L)}] Q3a = Q3b + {x / (A + L)} * Q3b Q3a- Q3b = {x / (A + L)} * Q3b.

【０１１４】即ち、ｘ＝０の時、被写体Ｍ１ａと被写体
Ｍ１ｂの撮影像は重なり合う。ｘが大きくなると、Ｑ３
ｂが小さくなり、被写体Ｍ３ｂの撮影像は被写体Ｍ２ａ
の撮影像の方向へと移動していく。That is, when x = 0, the photographed images of the subject M1a and the subject M1b overlap. When x becomes large, Q3
b becomes smaller, and the captured image of the subject M3b becomes the subject M2a.
It moves in the direction of the captured image of.

【０１１５】被写体Ｍ１ａ、Ｍ２ａ、Ｍ３ａの基準面の
撮影像に対し、Ｘ線源４と被写体Ｍの距離をｘだけ移動
した被写体Ｍの撮影像を重ね合わせていくと、求める被
写体Ｍ２ａ以外の撮影像は同じ位置に重なるのではな
く、被写体Ｍ２ａ方向にズレて重なることになり、より
ボケ像となる（図１６参照）。When the captured images of the subject M1a, M2a, M3a are superposed on the captured images of the reference plane of the subject M1a, M2a, M3a by moving the distance between the X-ray source 4 and the subject M by x, the captured images other than the desired subject M2a The images do not overlap at the same position but shift in the direction of the subject M2a and overlap, resulting in a more blurred image (see FIG. 16).

【０１１６】以上のことから、求める被写体撮影像に、
それ以外の被写体撮影像を重ね合わせることにより、各
撮影像のズレは求める被写体Ｍ２ａの撮影像に近付いて
いく。また、ズレの大きさは、被写体Ｍ３よりも被写体
Ｍ１の方が大きくなる。これは、被写体Ｍ１の方が被写
体３よりも一辺拡大率が大きいためである。From the above, in the subject photographed image,
By superimposing the other photographic images of the subject, the deviation of each photographic image approaches the photographic image of the desired subject M2a. Further, the magnitude of the deviation is larger in the subject M1 than in the subject M3. This is because the subject M1 has a larger side expansion ratio than the subject 3.

【０１１７】この結果、この実施例においては、拡大率
を利用して所望部位を撮影する装置を提供し、管球焦点
と検出部とを直線運動させ、その運動と共にＸ線照射を
し、被写体をある時間毎にフレーム画像に取り込みなが
ら撮影し、被写体が固定されているので、ある基準点を
予め決めておけば、それに合わせて拡大率を決定し、そ
の拡大率に合わせて画像を生成することにより、所望部
位のみ抽出することができる。また、縦、横、斜め方向
に直線運動させれば、所望部位の様々な角度を撮影する
ことができる。As a result, in this embodiment, an apparatus for photographing a desired portion by utilizing the magnification is provided, and the tube focus and the detector are linearly moved, and X-ray irradiation is performed together with the movement, and the object is photographed. Since the subject is fixed by capturing while capturing in the frame image every certain time, if a certain reference point is determined in advance, the enlargement ratio is determined accordingly, and the image is generated according to the enlargement ratio. As a result, only the desired part can be extracted. In addition, by performing linear movements in the vertical, horizontal, and diagonal directions, it is possible to capture various angles of a desired portion.

【０１１８】これにより、各フレーム毎の画像を得られ
ることで、一回の撮影にて、多くのスライス画像を提供
することができ、より正確な臨床情報を得ることがで
き、被爆線量・撮影時間を減少させ、また、直線運動な
ので、装置を簡単にすることができる。As a result, since images for each frame can be obtained, many slice images can be provided in one shot, more accurate clinical information can be obtained, and radiation dose and radiographing can be performed. The time is reduced and the linear motion allows the device to be simplified.

【０１１９】つまり、本願発明によれば、一辺拡大率及
び面積拡大率の変化を大きく得ることが可能となり、任
意の被写体画像以外の画像に補正係数の逆数を掛け、こ
れを被写体Ｍの画像に重ね合わせることにより、これま
で困難であった、口腔内領域の撮影を一度の位置付けで
行うことが可能となり、また、必要に応じて任意の断層
像を再構築することが可能となり、さらに、Ｘ線断層撮
影装置２の小型化が可能となるので、廉価に製作可能な
り、口腔内領域のみならずや頭部の断層撮影でのニーズ
に応えることが可能となる。That is, according to the present invention, it is possible to obtain a large change in the one-sided enlargement ratio and the area enlargement ratio, and an image other than an arbitrary subject image is multiplied by the reciprocal of the correction coefficient to obtain an image of the subject M. By superimposing them, it is possible to perform imaging of the intraoral region with a single positioning, which has been difficult until now, and it is possible to reconstruct an arbitrary tomographic image as necessary. Since the line tomography apparatus 2 can be miniaturized, it can be manufactured at low cost, and it is possible to meet the needs not only in the oral region but also in the tomography of the head.

【０１２０】[0120]

【発明の効果】以上詳細な説明から明らかなようにこの
発明によれば、被写体にＸ線を発生するＸ線源と被写体
を通過したＸ線を検出するＸ線撮像手段とを、被写体を
間にして相互に対向し、且つ、Ｘ線源とＸ線撮像手段と
の距離を一定に設定し、Ｘ線撮影構成体を直線移動させ
ながらＸ線照射を行い、任意の時間毎に被写体の撮影像
をＸ線源撮像手段で取り込みながらＸ線撮影を行い、こ
のとき、被写体が予め固定されているので、ある基準点
を予め設定すれば、その基準点に合わせて撮影像の拡大
率は、各々の位置により決定され、取り込まれた複数枚
の撮影像を拡大又は縮小し、その撮影像を重ね合わせて
合成することにより、所望部位の断層面画像を容易に生
成し得る。As is apparent from the above detailed description, according to the present invention, an X-ray source for generating X-rays on an object and an X-ray imaging means for detecting X-rays passing through the object are arranged between the objects. And the X-ray source and the X-ray imaging means are set to a constant distance from each other, and X-ray irradiation is performed while linearly moving the X-ray imaging component, and an object is imaged at arbitrary time intervals. X-ray imaging is performed while the image is captured by the X-ray source imaging means. At this time, since the subject is fixed in advance, if a certain reference point is set in advance, the magnifying power of the captured image according to the reference point will be It is possible to easily generate a tomographic image of a desired portion by enlarging or reducing a plurality of captured images that are determined by the respective positions, and superimposing the captured images and combining them.

【図面の簡単な説明】[Brief description of drawings]

【図１】Ｘ線撮影構成体の直線移動状態を示す正面図で
ある。FIG. 1 is a front view showing a linear movement state of an X-ray imaging structure.

【図２】Ｘ線源から被写体までの距離と一辺拡大率との
関係を示す図である。FIG. 2 is a diagram showing a relationship between a distance from an X-ray source to a subject and a side enlargement ratio.

【図３】単一の被写体の撮影を示す正面図である。FIG. 3 is a front view showing shooting of a single subject.

【図４】複数の被写体の撮影を示す正面図である。FIG. 4 is a front view showing shooting of a plurality of subjects.

【図５】複数の被写体の各条件での撮影を示す正面図で
ある。FIG. 5 is a front view showing photographing of a plurality of subjects under each condition.

【図６】複数の被写体の各条件での補正前の拡大率及び
信号強度を示す図である。FIG. 6 is a diagram showing an enlargement ratio and a signal strength before correction under a plurality of conditions for a plurality of subjects.

【図７】複数の被写体の各条件での補正後の拡大率及び
信号強度を示す図である。FIG. 7 is a diagram showing a magnification rate and a signal intensity after correction of a plurality of subjects under respective conditions.

【図８】撮影像を縮小したときの撮影を示す図である。FIG. 8 is a diagram illustrating shooting when a captured image is reduced.

【図９】撮影像を等倍したときの撮影を示す図である。FIG. 9 is a diagram showing photographing when a photographed image is magnified.

【図１０】撮影像を拡大したときの撮影を示す図であ
る。FIG. 10 is a diagram showing photographing when a photographed image is enlarged.

【図１１】撮影像を合成したときを示す図である。FIG. 11 is a diagram showing a case where captured images are combined.

【図１２】信号強度を示す図である。FIG. 12 is a diagram showing signal strength.

【図１３】補正後の一辺拡大率を示す図である。FIG. 13 is a diagram showing a corrected one-side enlargement ratio.

【図１４】被写体とＸ線源との距離が移動したときの図
である。FIG. 14 is a diagram when the distance between the subject and the X-ray source has moved.

【図１５】各被写体の位置関係を示す座標図である。FIG. 15 is a coordinate diagram showing a positional relationship between subjects.

【図１６】被写体のボケ像を示す図である。FIG. 16 is a diagram showing a blurred image of a subject.

【図１７】実施例において撮影像の生成の流れを示す図
である。FIG. 17 is a diagram showing a flow of generation of a captured image in the embodiment.

【図１８】Ｘ線断層撮像装置のシステム構成図である。FIG. 18 is a system configuration diagram of an X-ray tomographic imaging apparatus.

【図１９】従来においてＸ線源を移動させた正面図であ
る。FIG. 19 is a front view showing a conventional X-ray source moved.

【図２０】従来において複数の被写体の各条件での撮影
を示す正面図である。FIG. 20 is a front view showing conventional photography of a plurality of subjects under each condition.

【図２１】従来において複数の被写体の各条件での補正
前の拡大率及び信号強度を示す図である。FIG. 21 is a diagram showing an enlargement ratio and a signal strength before correction in each condition of a plurality of subjects in the related art.

【図２２】従来において複数の被写体の各条件での補正
後の拡大率及び信号強度を示す図である。FIG. 22 is a diagram showing a magnification rate and a signal intensity after correction in the related art under a plurality of conditions under respective conditions.

【符号の説明】 ２ Ｘ線断層撮影装置 ４ Ｘ線源 ６ Ｘ線撮像手段 ６Ａ 撮影画像部 ８ Ｘ線撮影構成体 １０ 直線移動駆動手段 １２ 移動計測手段 １４ 撮影影像制御手段 １６ 拡大率補正手段 １８ 撮影像合成手段 ２０ 制御装置 ２２ 受光面[Explanation of symbols] 2 X-ray tomography equipment 4 X-ray source 6 X-ray imaging means 6A photographed image section 8 X-ray imaging structure 10 Linear movement drive means 12 Movement measuring means 14 Photographing image control means 16 Enlargement factor correction means 18 Photographed image synthesizing means 20 Control device 22 Light receiving surface

Claims (6)

【特許請求の範囲】[Claims] 【請求項１】 被写体にＸ線を発生するＸ線源と前記被
写体を通過したＸ線を検出するＸ線撮像手段とが備えら
れたＸ線撮影構成体を設け、前記被写体を間にして前記
Ｘ線源と前記Ｘ線撮像手段とを一定距離に相互に対向し
て前記Ｘ線撮影構成体を直線移動させる直線移動駆動手
段を設け、前記Ｘ線撮影構成体の直線移動距離を計測す
る移動計測手段を設け、前記Ｘ線撮像手段には撮影像を
画く撮影画像部を設け、この撮影画像部での撮影像を制
御する撮影像制御手段を設け、前記撮影画像部での撮影
像の拡大率補正を行う拡大率補正手段を設け、この拡大
率補正手段で補正された撮影像を重ね合わせて合成する
撮影像合成手段を設けたことを特徴とする直線運動型Ｘ
線断層撮影装置。1. An X-ray imaging structure provided with an X-ray source for generating X-rays to an object and X-ray imaging means for detecting X-rays passing through the object, the object being interposed between the X-ray imaging structure. A linear movement driving unit that linearly moves the X-ray imaging structure is provided so that the X-ray source and the X-ray imaging unit face each other at a constant distance, and movement for measuring the linear movement distance of the X-ray imaging structure. A measuring means is provided, a photographed image portion for drawing a photographed image is provided in the X-ray image pickup means, and a photographed image control means for controlling the photographed image in the photographed image portion is provided to enlarge the photographed image in the photographed image portion. A linear motion type X characterized in that a magnifying power correcting means for correcting the magnifying power is provided, and a photographed image synthesizing means for superimposing and synthesizing the photographed images corrected by the magnifying power correcting means is provided.
Line tomography device. 【請求項２】 前記Ｘ線撮像手段は、二次元Ｘ線イメー
ジセンサとしての画像センサーからなることを特徴とす
る請求項１に記載の直線運動型Ｘ線断層撮影装置。2. The linear motion X-ray tomography apparatus according to claim 1, wherein the X-ray imaging unit is an image sensor as a two-dimensional X-ray image sensor. 【請求項３】 前記移動計測手段には、前記被写体の断
層面位置に目印となる不透過性のアダプタが設けられた
ことを特徴とする請求項１に記載の直線運動型Ｘ線断層
撮影装置。3. The linear motion type X-ray tomography apparatus according to claim 1, wherein the movement measuring means is provided with an impermeable adapter which serves as a mark at a position of a tomographic plane of the subject. . 【請求項４】 前記移動計測手段は、ＰＳＤ素子、エン
コーダ、反射型位置計測装置からなることを特徴とする
請求項１に記載の直線型Ｘ線断層撮影装置。4. The linear X-ray tomography apparatus according to claim 1, wherein the movement measuring unit includes a PSD element, an encoder, and a reflection-type position measuring apparatus. 【請求項５】 前記拡大率補正手段は、任意の位置での
撮影像の一辺拡大率をＧとし、この位置に重ね合わされ
る複数の撮影像の拡大率をＢ１、Ｂ２、Ｂ３…とすると
き、補正係数をＢ１／Ｇ、Ｂ２／Ｇ、Ｂ３／Ｇ…とし、
前記撮影像合成手段は、これらの補正された撮影像を重
ね合わせる機能を有することを特徴とする請求項１に記
載の直線運動型Ｘ線断層撮影装置。5. The magnifying power correction means sets G to be one side magnifying power of a photographed image at an arbitrary position, and B1, B2, B3 ... , Correction coefficients are B1 / G, B2 / G, B3 / G ...
The linear motion X-ray tomography apparatus according to claim 1, wherein the captured image synthesizing unit has a function of superposing these corrected captured images. 【請求項６】 前記Ｘ線撮像手段の前記撮影画像部は、
連続的に撮影する方式と任意時間毎に撮影する方式とを
備えることを特徴とする請求項１に記載の直線運動型Ｘ
線断層撮影装置。6. The captured image portion of the X-ray imaging means is
The linear motion type X according to claim 1, comprising a method of continuously photographing and a method of photographing every arbitrary time.
Line tomography device.