JPS5817613B2 - X-ray tomography device - Google Patents
X-ray tomography deviceInfo
- Publication number
- JPS5817613B2 JPS5817613B2 JP52050493A JP5049377A JPS5817613B2 JP S5817613 B2 JPS5817613 B2 JP S5817613B2 JP 52050493 A JP52050493 A JP 52050493A JP 5049377 A JP5049377 A JP 5049377A JP S5817613 B2 JPS5817613 B2 JP S5817613B2
- Authority
- JP
- Japan
- Prior art keywords
- ray
- rays
- filter
- filters
- subject
- 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.)
- Expired
Links
- 238000003325 tomography Methods 0.000 title claims description 7
- 238000010521 absorption reaction Methods 0.000 claims description 20
- 238000001514 detection method Methods 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- 230000004907 flux Effects 0.000 description 4
- 238000003745 diagnosis Methods 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 2
- 229910052782 aluminium Inorganic materials 0.000 description 2
- 239000010405 anode material Substances 0.000 description 2
- 238000001228 spectrum Methods 0.000 description 2
- 238000002083 X-ray spectrum Methods 0.000 description 1
- 238000004458 analytical method Methods 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 238000002591 computed tomography Methods 0.000 description 1
- 238000007405 data analysis Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 239000013558 reference substance Substances 0.000 description 1
- 210000004872 soft tissue Anatomy 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- 238000000411 transmission spectrum Methods 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
Landscapes
- Analysing Materials By The Use Of Radiation (AREA)
- X-Ray Techniques (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Description
【発明の詳細な説明】
本発明はコンピュータを利用して画像を再構成するＸ線
断層装置に関するものである。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to an X-ray tomography apparatus that reconstructs images using a computer.
Ｘ線断層装置の一つにコンピュータ・トモグラフィ（Ｃ
ｏｍｐｕｔｅｒｉｚｅｄ Ｔｏｍｏｇｒａｐｈｙ
：以下ＣＴスキャナと略称する）と呼ばれる装置がある
。One of the X-ray tomography devices is computer tomography (C
computerized tomography
There is a device called a CT scanner (hereinafter abbreviated as CT scanner).
このＣＴスキャナは、例えばＸ線管とＸ線検出装置を対
峙させながら例えばペンシルビーム状のＸ線を曝射し、
このペンシルビームＸ線を振らせて被検体の断層面に照
射して、これをＸ線検出装置で捕え、これを−回行なう
毎に断層面に対してＸ線管とＸ線検出装置とを微小角回
転させ再びこれを行ない、以後順次角度を変えながら被
検体の断層面の種々の方向から見たＸ線吸収データを収
集する。This CT scanner emits, for example, pencil beam-shaped X-rays while an X-ray tube and an X-ray detection device are facing each other,
This pencil beam X-ray is swung and irradiated onto the tomographic plane of the subject, and is captured by the X-ray detection device.Every time this is repeated, the X-ray tube and the X-ray detection device are moved to the tomographic plane. This is repeated by rotating it by a small angle, and thereafter X-ray absorption data from various directions of the tomographic plane of the subject are collected while changing the angle sequentially.
そして、通常３６０°の角度範囲のデータを収集した後
、このデータをコンピュータで解析し、断層面の個々の
位置のＸ線吸収率を算出して、その吸収率に応じた階調
度で断層面を再構成するようにしたもので、断層面各部
分の組成をＸ線吸収率に関して２０００段階にも及ぶ階
調度で分析することができるので、軟質組織から硬質組
織に至るまで明確な断層像が得られる。After collecting data in an angular range of 360°, this data is analyzed by a computer, the X-ray absorption rate at each position on the tomographic plane is calculated, and the tomographic plane is graded according to the absorption rate. The composition of each part of the tomographic plane can be analyzed in terms of X-ray absorption in as many as 2,000 gradations, so a clear tomographic image can be obtained from soft tissue to hard tissue. can get.
、 ところで、従来この種の装置ではＸ線管に印加する
高電圧が半固定であり、通常の診断用Ｘ線装置の如く診
断部位に応じて管電圧を変えるようなことはしない。By the way, conventionally, in this type of apparatus, the high voltage applied to the X-ray tube is semi-fixed, and the tube voltage is not changed depending on the diagnosis site as in ordinary diagnostic X-ray apparatuses.
その理由は各部位のＸ線吸収係数を所定のＸ線エネルギ
ーに対する平均値で算出し、νこれを水等の基準とする
物質のＸ線吸収係数の平均値と比較対比しているためで
、Ｘ線管の管電圧を変えると平均のとり方が変わる（Ｘ
線エネルギー分布が変わる）ため、診断部位に対応した
管電圧とすることができないからである。The reason for this is that the X-ray absorption coefficient of each part is calculated as an average value for a predetermined X-ray energy, and this is compared and contrasted with the average value of the X-ray absorption coefficient of a reference substance such as water. Changing the tube voltage of the X-ray tube changes the way the average is taken (X
This is because the tube voltage cannot be adjusted to correspond to the diagnosis site because the linear energy distribution changes).
デ 従って、体厚が薄く、シかもＸ線吸収の小さい部位
等では必要以上の被曝を受けることとなり、またＸ線エ
ネルギー分布が適切でないため良質のデータが得にくく
なり、データ解析に支障を来たして最適な画像の再構成
ができない心配がある。Therefore, parts of the body that are thin and have low X-ray absorption will be exposed to more radiation than necessary, and the X-ray energy distribution will not be appropriate, making it difficult to obtain high-quality data, which will hinder data analysis. There is a concern that optimal image reconstruction may not be possible.
本発明は上記事情に鑑みて成されたもので、Ｘ線吸収率
のそれぞれ異なる複数種のＸ線フィルタを用い、部位に
応じてこれらＸ線フィルタを選択して使用することによ
り、管電圧を変えずに適宜なるエネルギー分布のＸ線を
放射させることができるようにして良質の再構成画像が
得られるようにすると共にＸ線フィルタを除くことによ
り標準Ｘ線強度の再構成像も得られ、他の部位の再構成
像との比較も可能としたＸ線断層装置を提供することを
目的とする。The present invention has been made in view of the above circumstances, and uses multiple types of X-ray filters with different X-ray absorption rates, and by selecting and using these X-ray filters according to the site, the tube voltage can be reduced. By making it possible to emit X-rays with an appropriate energy distribution without changing the energy distribution, a high-quality reconstructed image can be obtained, and by removing the X-ray filter, a reconstructed image with standard X-ray intensity can also be obtained, It is an object of the present invention to provide an X-ray tomography apparatus that allows comparison with reconstructed images of other parts.
以下、本発明の一実施例について図面を参照し聾 なから説明する。Hereinafter, one embodiment of the present invention will be explained with reference to the drawings. Let me explain from the start.
第１図は本発明装置の櫃略的な構成を示すブロック図で
あり、図中１はＸ線管２に与える高電圧を発生するＸ線
高電圧装置、３ａ。FIG. 1 is a block diagram showing a schematic configuration of the apparatus of the present invention, in which reference numeral 1 denotes an X-ray high voltage device 3a that generates a high voltage to be applied to the X-ray tube 2.
３ｂはそれぞれ異なる厚みとしそれぞれ所定のＸ線吸収
率を持たせたＸ線フィルタ、４はこのＸ線フィルタ３ａ
、３ｂのうち所望のフィルタをＸ線管２の放射するＸ
線束中に移動させるフィルタ駆。Reference numeral 3b indicates an X-ray filter having a different thickness and a predetermined X-ray absorption rate, and 4 indicates this X-ray filter 3a.
, 3b, the desired filter is selected from the X-rays emitted by the X-ray tube 2.
A filter driver that moves into the beam bundle.
動装置、５は被検体、６はこの被検体５を介して前記Ｘ
線管２に対峙して設けられ被検体５を透過した前記Ｘ線
管２からのＸ線を検出するＸ線検出器、７はこのＸ線検
出器６の検出出力を増幅する増幅器、８はこの増幅器７
にて増幅された検出用。5 is a subject; 6 is a moving device through which the subject 5 is
An X-ray detector is provided facing the ray tube 2 and detects the X-rays from the X-ray tube 2 that have passed through the subject 5; 7 is an amplifier that amplifies the detection output of the X-ray detector 6; 8 is an amplifier; This amplifier 7
For amplified detection.
力を演算処理し画像の再構成を行なう画像再構成装置、
９はこの画像再構成装置８の出力を表示する表示器であ
る。An image reconstruction device that reconstructs images by calculating forces;
A display 9 displays the output of the image reconstruction device 8.
次に上記構成の本装置の動作について説明する。Next, the operation of this apparatus having the above configuration will be explained.
まず、Ｘ線高電圧装置１より標準Ｘ線強度のＸ線。First, X-rays of standard X-ray intensity are emitted from the X-ray high-voltage device 1.
を放射する電圧値の高電圧を発生させ、Ｘ線管２に与え
る。A high voltage with a voltage value that radiates is generated and applied to the X-ray tube 2.
するとＸ線管２は標準Ｘ線強度のＸ線が放射され、被検
体５に照射される。Then, the X-ray tube 2 emits X-rays of standard X-ray intensity, and the subject 5 is irradiated with the X-rays.
被検体５を透過したＸ線はＸ線検出器６に入射し、ここ
でそのＸ線強度に応じた信号に変換された後、増幅器７
に送られ増幅される。The X-rays that have passed through the object 5 enter the X-ray detector 6, where they are converted into a signal according to the X-ray intensity, and then sent to the amplifier 7.
is sent to and amplified.
そして、この増幅器７にて増幅された後、画像再構成装
置８に送られる。After being amplified by the amplifier 7, the signal is sent to the image reconstruction device 8.
Ｘ線は前述した如く被検体５の断層面を移動して同一方
向から見た断層面透過データを得ると次に断層面に対し
て所定角度移動させ再びこれを行ない、以後、順次角度
基えながらあらゆる方向からの断層面透過Ｘ線データを
収集し、これを画像再構成装置８にて演算解析して断層
面各位置に対応するＸ線吸収率を算出し、画像の再構成
が行われる。As mentioned above, the X-ray moves across the tomographic plane of the subject 5 to obtain tomographic transmission data seen from the same direction, and then moves at a predetermined angle with respect to the tomographic plane and repeats this process again. The X-ray data transmitted through the tomographic plane from all directions is collected, and the image reconstruction device 8 performs arithmetic analysis to calculate the X-ray absorption rate corresponding to each position on the tomographic plane, and reconstructs the image. .
この再構成された画像は表示器９に送られ、ここで像と
して表示される。This reconstructed image is sent to the display 9, where it is displayed as an image.
以上は標準Ｘ線強度のＸ線を用いた場合であるが、この
標準Ｘ線強度のＸ線ではエネルギー分布が適切でない場
合には、その断層面に最適なＸ線エネルギー分布を得る
ためのＸ線フィル 、例えば３ａを選択し、フィルタ駆
動装置４に選択指令を与える。The above is a case where X-rays with standard X-ray intensity are used, but if the energy distribution is not appropriate with X-rays with this standard X-ray intensity, the A line filter, for example 3a, is selected and a selection command is given to the filter driving device 4.
するとこのフィルタ、駆動装置４は作動してＸ線管の放
射するＸ線束中にＸ線フィルタ３ａを移動させる。The filter drive device 4 then operates to move the X-ray filter 3a into the X-ray flux emitted by the X-ray tube.
するとＸ線管２から放射されたＸ線束はこのＸ線フィル
タ３ａを通って、エネルギー分布が変化し断層面に最適
なエネルギー分布となって被検体５に照射されるから、
微妙な差違の認識が行ない得る良質の透過Ｘ線データ（
Ｘ線吸収データ）が検出できる。Then, the X-ray flux emitted from the X-ray tube 2 passes through the X-ray filter 3a, changes its energy distribution, becomes optimal for the tomographic plane, and is irradiated onto the subject 5.
High-quality transmitted X-ray data that allows recognition of subtle differences (
X-ray absorption data) can be detected.
従って、診断対象とする部位に応じて最適なＸ線エネル
ギー分布となるようなＸ線フィルタを選択してこれを通
したＸ線束を用い断層面の種々の方向に対するＸ線吸収
データを得ることにより、明確な断層面再構成画像を得
ることができる。Therefore, by selecting an X-ray filter that provides the optimal X-ray energy distribution according to the region to be diagnosed, and using the X-ray flux that passes through the filter, we can obtain X-ray absorption data for various directions on the tomographic plane. , a clear tomographic reconstruction image can be obtained.
本装置はＸ線フィルタをＸ線束から外せば標準Ｘ線強度
のＸ線による再構成画像を得ることができるから、異な
る部位の断層面を比較したい場合にはこの標準Ｘ線強度
のＸ線を用いれは対比を容易に行なうことができる。This device can obtain reconstructed images using X-rays with standard X-ray intensity by removing the X-ray filter from the X-ray flux, so when you want to compare tomographic planes of different parts, use X-rays with this standard X-ray intensity. The usage allows for easy comparison.
第２図は厚みの異なる２種類のアルミニウムフィルタを
用いたときのＸ線エネルギーと出力Ｘ線強度の関係を示
す特性図であり、Ｘ線管から放射されるＸ線をＡ１厚み
の薄いＸ線フィルタを用いた場合のＸ線をＢ１厚みのや
や厚いＸ線フィルタを用いた場合のＸ線をＣで示す。Figure 2 is a characteristic diagram showing the relationship between X-ray energy and output X-ray intensity when two types of aluminum filters with different thicknesses are used. X-rays when a filter is used are shown as B. X-rays when a slightly thicker X-ray filter with a thickness of 1 is used are shown as C.
フィルタとしてはアルミニウムの他にＸ線管２の陽極材
料と同材料もしくは、その材料の原子番号近傍の材料に
よるフィルタを用いても良い。As the filter, in addition to aluminum, a filter made of the same material as the anode material of the X-ray tube 2 or a material having an atomic number close to that material may be used.
この場合は第２図にＤで示す如き分布となり、陽極材料
に対する特性Ｘ線を主とするスペクトルが得られる。In this case, the distribution becomes as shown by D in FIG. 2, and a spectrum consisting mainly of characteristic X-rays for the anode material is obtained.
また、他の例としてバランスフィルタと呼ばれる原子番
号の近いＥ、Ｆ２組のフィルタを組み合わせて用い、第
３図に示す如くその２組のバランスフィルタＥ、 Ｆの
Ｘ線吸収端のずれを利用して両者の差の部分のＧなる透
過Ｘ線を利用することにより、所望とする強さのＸ線を
得ることができる。Another example is to use a combination of two sets of filters called balance filters, E and F, which have similar atomic numbers, and utilize the shift in the X-ray absorption edges of the two sets of balance filters E and F, as shown in Figure 3. By using the transmitted X-ray of the difference between the two, X-rays of desired intensity can be obtained.
ここでバランスフィルタについて説明しておく。Here, I will explain the balance filter.
バランスフィルタは、原子番号の近いＥ、Ｆ２組のフィ
ルタを用いて構成したものでフィルタＥ１Ｆの各々の厚
みを選んで、Ｘ線吸収端部以外のＸ線吸収係数が一致す
るようにしておく、Ｅ１Ｆフィルタを透過したＸ線スペ
クトルの相違は、各々のフィルタの吸収端附近にのみお
こる。The balance filter is constructed using two sets of filters E and F with similar atomic numbers, and the thickness of each filter E1F is selected so that the X-ray absorption coefficients other than the X-ray absorption edge are the same. Differences in the X-ray spectra transmitted through the E1F filters occur only near the absorption edges of each filter.
すなわち第３図において、フィルタＥ透過後のスペクト
ルハ、エネルギー範囲Ｇにおいてのみ、Ｆの透過スペク
トルより太きい。That is, in FIG. 3, the spectrum C after passing through filter E is thicker than the transmission spectrum of F only in the energy range G.
これが第３図の一点鎖線で示されている。This is shown by the dash-dotted line in FIG.
フィルタＥ、Ｆ透過後の各々の透過信号の差をとるとエ
ネルギー範囲Ｇのみの被検体の情報が得られる。By taking the difference between the transmitted signals after passing through the filters E and F, information on the object only in the energy range G can be obtained.
これは、はぼ単一エネルギーのＸ線に相当するため、Ｘ
線のビームハードニング等の効果がキャンセルされ、良
好な画像が得られる。This corresponds to X-rays with almost single energy, so
Effects such as line beam hardening are canceled and a good image can be obtained.
このようにＣＴ装置において、Ｘ線吸収率のそれぞれ異
なる複数種のＸ線フィルタを用い診断部位に応じてこれ
らＸ線フィルタを任意に選択使用することにより標準的
なエネルギー分布のＸ線を放射するＸ線管からのＸ線を
所望とするエネルギー分布のＸ線に変換することができ
るようにしたので、Ｘ線管の管電圧を変えることなく所
望とするＸ線エネルギー分布のＸ線が得られるから、体
厚の薄い又は吸収の異なる部位であっても適正な強さの
Ｘ線とすることができるので良質の再構成画像を得るこ
とができ、また、Ｘ線管は常に一定の強さのＸ線を放射
するので、フィルタを除いて標準のＸ線にて撮影を行な
えば異なる部位の比較もできる等、優れた特徴を有する
Ｘ線断層装置を提供することができる。In this way, CT equipment uses multiple types of X-ray filters with different X-ray absorption rates, and by arbitrarily selecting and using these X-ray filters depending on the diagnosis area, X-rays with a standard energy distribution are emitted. Since the X-rays from the X-ray tube can be converted into X-rays with the desired energy distribution, X-rays with the desired X-ray energy distribution can be obtained without changing the tube voltage of the X-ray tube. Because of this, it is possible to obtain high-quality reconstructed images because X-rays of appropriate intensity can be applied even to areas with thin body thickness or different absorption levels. Therefore, it is possible to provide an X-ray tomography apparatus with excellent features such as being able to compare different parts by removing the filter and performing imaging with standard X-rays.
第１図は本発明の一実施例を示す概略的なブロック図、
第２図、第３図は各種フィルタを透過させた場合におけ
るＸ線強度を示す特性図である。
２・・・・・・Ｘ線管、３ａ、３ｂ・・・・・・Ｘ線フ
ィルタ、５・・・・・・被検体、６・・・・・・Ｘ線検
出器。FIG. 1 is a schematic block diagram showing an embodiment of the present invention;
FIGS. 2 and 3 are characteristic diagrams showing the intensity of X-rays transmitted through various filters. 2...X-ray tube, 3a, 3b...X-ray filter, 5...subject, 6...X-ray detector.
Claims (1)
被検体の断層面に沿って前記Ｘ線源及びＸ線検出器とを
移動させ前記被検体断層面の各方向からのＸ線吸収デー
タを収集し解析して前記断層面像の再構成を行なうもの
において、複数種のＸ線バランスフィルタを備え、これ
らＸ線バランスフィルタを任意に１対選択して使用する
ことにより、Ｘ線フィルタ間のＸ線吸収差により、Ｘ線
源からのＸ線を被検体厚や部位に応じたエネルギー分布
とすることができるようにしたことを特徴とするＸ線断
層装置。1. An X-ray source and an X-ray detector are placed facing each other, and the X-ray source and X-ray detector are moved along the tomographic plane of the subject to receive X-rays from each direction of the tomographic plane of the subject. In an apparatus that collects and analyzes absorption data to reconstruct the tomographic image, it is equipped with multiple types of X-ray balance filters, and by arbitrarily selecting and using one pair of these X-ray balance filters, An X-ray tomography apparatus characterized in that the energy distribution of X-rays from an X-ray source can be adjusted according to the thickness and region of a subject due to X-ray absorption differences between filters.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP52050493A JPS5817613B2 (en) | 1977-04-30 | 1977-04-30 | X-ray tomography device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP52050493A JPS5817613B2 (en) | 1977-04-30 | 1977-04-30 | X-ray tomography device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS53135590A JPS53135590A (en) | 1978-11-27 |
| JPS5817613B2 true JPS5817613B2 (en) | 1983-04-08 |
Family
ID=12860445
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP52050493A Expired JPS5817613B2 (en) | 1977-04-30 | 1977-04-30 | X-ray tomography device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5817613B2 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0447887B2 (en) * | 1984-06-25 | 1992-08-05 | Canon Denshi Kk |
Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4361901A (en) * | 1980-11-18 | 1982-11-30 | General Electric Company | Multiple voltage x-ray switching system |
| US4528685A (en) * | 1983-05-16 | 1985-07-09 | General Electric Company | X-ray beam filter device |
| JPS6426132A (en) * | 1988-05-07 | 1989-01-27 | Raido Kk X | X-ray body inspecting device |
| GB201308851D0 (en) * | 2013-05-16 | 2013-07-03 | Ibex Innovations Ltd | Multi-spectral x-ray detection apparatus |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5028894A (en) * | 1973-06-01 | 1975-03-24 | ||
| JPS5060191A (en) * | 1973-09-19 | 1975-05-23 |
-
1977
- 1977-04-30 JP JP52050493A patent/JPS5817613B2/en not_active Expired
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5028894A (en) * | 1973-06-01 | 1975-03-24 | ||
| JPS5060191A (en) * | 1973-09-19 | 1975-05-23 |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0447887B2 (en) * | 1984-06-25 | 1992-08-05 | Canon Denshi Kk |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS53135590A (en) | 1978-11-27 |
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