JPH04436B2 - - Google Patents
Info
- Publication number
- JPH04436B2 JPH04436B2 JP56168961A JP16896181A JPH04436B2 JP H04436 B2 JPH04436 B2 JP H04436B2 JP 56168961 A JP56168961 A JP 56168961A JP 16896181 A JP16896181 A JP 16896181A JP H04436 B2 JPH04436 B2 JP H04436B2
- Authority
- JP
- Japan
- Prior art keywords
- ray
- slit
- image
- rays
- scanning
- 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 - Lifetime
Links
- 238000003384 imaging method Methods 0.000 claims description 16
- 230000005540 biological transmission Effects 0.000 claims description 7
- 230000005855 radiation Effects 0.000 claims description 3
- 239000000284 extract Substances 0.000 claims description 2
- 238000000605 extraction Methods 0.000 claims 1
- 210000000988 bone and bone Anatomy 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 3
- 229910052782 aluminium Inorganic materials 0.000 description 3
- 230000002238 attenuated effect Effects 0.000 description 3
- 230000001360 synchronised effect Effects 0.000 description 3
- 239000002023 wood Substances 0.000 description 3
- 230000000694 effects Effects 0.000 description 2
- 230000035945 sensitivity Effects 0.000 description 2
- 101700004678 SLIT3 Proteins 0.000 description 1
- 102100027339 Slit homolog 3 protein Human genes 0.000 description 1
- 230000007812 deficiency Effects 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 210000003205 muscle Anatomy 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
Landscapes
- Apparatus For Radiation Diagnosis (AREA)
Description
【発明の詳細な説明】
この発明は、Ｘ線曝射による被写体よりの散乱
Ｘ線の影響を軽減してコントラストの良いＸ線透
過像を得るＸ線撮影装置に関するものである。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to an X-ray imaging apparatus that reduces the influence of scattered X-rays from a subject due to X-ray exposure and obtains an X-ray transmission image with good contrast.
一般に被写体をＸ線撮影する場合、被写体を通
過してＸ線透過像を形成する被写体により減衰さ
れた一次Ｘ線は、被写体への入射Ｘ線に比べ大巾
に少ない。被写体で減衰されるＸ線の多くは、被
写体を中心に四方への散乱Ｘ線として放射され、
受像面ではＸ線透過像に重なり、そのコントラス
トを大巾に低下させる。従つて従来は、第１図に
示すように被写体１３と受像面１５の間にＸ線グ
リツド１４を配置して、１次Ｘ線１６と同じ方向
のＸ線のみを通すことにより、散乱Ｘ線を除去し
ようとするシステムが広く用いられている。しか
し、このＸ線グリツド１４は、Ｘ線減衰の大きい
鉛板とＸ線減衰の少ないアルミ板又は木材を、１
次Ｘ線の通過方向に平行にサンドウイツチにした
もので、散乱Ｘ線の除去効率は鉛板の間に挟まれ
たＸ線減衰の少ない物質の奥行／巾にほぼ比例す
る。所がアルミや木材は一般に被写体と同等かそ
れ以上にＸ線を吸収し、必要とする１次透過Ｘ線
の一部を吸収するので、あまり奥行を大きくでき
ず、従つてその巾は非常に小さくせざるを得な
い。それ故、鉛板とアルミ板又は木材を多数重ね
る必要があり、１次Ｘ線に対するＸ線グリツドの
開孔率を維持するために、非常に薄いものとしな
ければならない。従つて、鉛板の散乱Ｘ線除去効
果も限定される。このようなことから、Ｘ線グリ
ツドによる被写体よりの散乱Ｘ線の除去効果は、
可成り不満足なものである。尚、第１図中、１１
はＸ線源例えばＸ線管である。 Generally, when X-ray photographing a subject, the primary X-rays that pass through the subject and are attenuated by the subject to form an X-ray transmission image are much smaller than the incident X-rays to the subject. Most of the X-rays that are attenuated by the object are emitted as scattered X-rays in all directions around the object,
On the image-receiving surface, it overlaps with the X-ray transmitted image, greatly reducing its contrast. Therefore, conventionally, as shown in FIG. 1, an X-ray grid 14 is placed between a subject 13 and an image receiving surface 15 to allow only X-rays in the same direction as the primary X-rays 16 to pass through, thereby eliminating scattered X-rays. Systems that attempt to remove these are widely used. However, this X-ray grid 14 consists of a lead plate with high X-ray attenuation and an aluminum plate or wood with low X-ray attenuation.
It is made into a sandwich parallel to the passing direction of the next X-ray, and the removal efficiency of scattered X-rays is approximately proportional to the depth/width of the material sandwiched between the lead plates and having little X-ray attenuation. However, aluminum and wood generally absorb X-rays as much as or more than the subject, and absorb a portion of the necessary primary transmitted X-rays, so the depth cannot be increased very much, and therefore the width is very large. I have no choice but to make it smaller. Therefore, it is necessary to overlap many lead plates and aluminum plates or wood, which must be very thin in order to maintain the aperture ratio of the X-ray grid for the primary X-rays. Therefore, the effect of the lead plate on removing scattered X-rays is also limited. For this reason, the effectiveness of the X-ray grid in removing scattered X-rays from the subject is
This is quite unsatisfactory. In addition, in Figure 1, 11
is an x-ray source, for example an x-ray tube.
そこで第２図に示すような走査スリツトシステ
ムが用いられている。本システムは、被写体２３
の前後にＸ線を通すスリツト２２ａ，２４ａを有
するスリツト走査板２２，２４がお互いに同期し
て被写体２３を上下方向に走査することによりＸ
線源例えばＸ線管２１から発生したＸ線からフア
ンビーム２６を形成し、フアンビーム２６で被写
体２３を走査する。被写体２３の後にあるスリツ
ト走査板２４は、フアンビーム２６の通過する所
だけ開孔するように調節してあるので、被写体２
３を透過した１次Ｘ線のみが受像面２５に達す
る。被写体２３で散乱されたＸ線２７は、１次Ｘ
線と平行にならないのでスリツト走査板２４の開
孔してない所に当り、受像面１５に達しない。従
つてコントラストが非常に良くなる。しかもＸ線
グリツドを使用した場合のように１次透過Ｘ線を
減衰させないので、トータル感度が良く、被写体
２３の被曝が低減されるという利点もある。しか
し、このシステム（第２図）は機構的に非常に難
かしく、又、Ｘ線管２１の負荷が非常に大きくな
るという欠点がある。 Therefore, a scanning slit system as shown in FIG. 2 is used. This system uses the subject 23
The slit scanning plates 22 and 24 having slits 22a and 24a through which X-rays pass before and after scan the subject 23 in the vertical direction in synchronization with each other.
A fan beam 26 is formed from X-rays generated from a radiation source, for example, an X-ray tube 21, and the subject 23 is scanned with the fan beam 26. The slit scanning plate 24 located behind the subject 23 is adjusted to open only where the fan beam 26 passes.
Only the primary X-rays that have passed through the image receiving surface 25 reach the image receiving surface 25. The X-rays 27 scattered by the object 23 are primary X-rays.
Since it is not parallel to the line, it hits a part of the slit scanning plate 24 that does not have holes and does not reach the image receiving surface 15. Therefore, the contrast becomes very good. Moreover, since the primary transmitted X-rays are not attenuated unlike when an X-ray grid is used, there is an advantage that the total sensitivity is good and the exposure of the subject 23 to radiation is reduced. However, this system (FIG. 2) is mechanically very difficult and has the disadvantage that the load on the X-ray tube 21 is very large.
即ち、被写体２３の前と後の２つのスリツト走
査板２２，２４を、完全に同期させ走査させなけ
ればならない。特に被写体２３の後のスリツト走
査板２４は、被写体の撮影部分より大きい部分を
走査しなければならないので、スリツト２４ａが
大きくなり、しかもスリツト開孔以外で完全にＸ
線を遮断するため、厚い鉛板を張る必要があり、
可成り重くなる。又、スリツト２４ａの走査によ
つて被写体２３に危害を加えないようカバー等で
保護しなければならないので、可成り大きなもの
となり、被写体２３の前のスリツト走査板２２と
完全に同期して走査するには、可成り大掛りな機
構を必要とする。又、スリツト走査板で走査して
Ｘ線撮影するため、Ｘ線管２１のＸ線曝射時間は
第１図のようにＸ線グリツド１４を使用する場合
に比べ大巾に長くなり、Ｘ線管２１の負荷が大き
くなる。従つて、焦点の大きいＸ線管を使用しな
ければならない。所がスリツト走査板２４のため
に被写体２３と受像面２５の間に可成の間隙が必
要となり、Ｘ線管２１の焦点が大きいのでＸ線透
過像がボケる。 That is, the two slit scanning plates 22 and 24 in front and behind the subject 23 must be scanned in complete synchronization. In particular, the slit scanning plate 24 after the subject 23 must scan a larger area than the photographed part of the subject, so the slit 24a becomes large and the area other than the slit opening must be completely
It was necessary to put a thick lead plate in order to block the wires.
It becomes quite heavy. In addition, since the subject 23 must be protected with a cover or the like to avoid harm to the subject 23 due to scanning by the slit 24a, it is quite large and scans in complete synchronization with the slit scanning plate 22 in front of the subject 23. requires a fairly large-scale mechanism. Furthermore, since X-ray photography is performed by scanning with a slit scanning plate, the X-ray exposure time of the X-ray tube 21 is much longer than when using the X-ray grid 14 as shown in FIG. The load on the pipe 21 increases. Therefore, an X-ray tube with a large focus must be used. However, the slit scanning plate 24 requires a considerable gap between the subject 23 and the image receiving surface 25, and since the focus of the X-ray tube 21 is large, the X-ray transmitted image becomes blurred.
この発明は、上記従来の欠点を除去したＸ線撮
影装置を提供することを目的とする。 An object of the present invention is to provide an X-ray imaging apparatus that eliminates the above-mentioned conventional drawbacks.
以下、図面を参照してこの発明の一実施例を詳
細に説明する。この発明のＸ線撮影装置は第３図
に示すように構成され、Ｘ線源例えばＸ線管３
１、Ｘ線を通すスリツト３２ａを有するスリツト
走査板３２、被写体３４、イメージ管３５、撮像
管を有するテレビカメラ３７が所定間隔で同軸上
に配設されている。更に前記テレビカメラ３７は
記憶演算処理装置であるデータ処理装置３８に接
続され、このデータ処理装置３８は表示器例えば
受像機３９に接続されると共にスリツトの位置信
号発生器３３に接続され、この位置信号発生器３
３は前記スリツト走査板３２に接続されている。 Hereinafter, one embodiment of the present invention will be described in detail with reference to the drawings. The X-ray imaging apparatus of the present invention is constructed as shown in FIG.
1. A slit scanning plate 32 having a slit 32a through which X-rays pass, a subject 34, an image tube 35, and a television camera 37 having an image pickup tube are arranged coaxially at predetermined intervals. Further, the television camera 37 is connected to a data processing device 38, which is a storage and arithmetic processing device, and this data processing device 38 is connected to a display device, for example, a television receiver 39, and is also connected to a slit position signal generator 33. Signal generator 3
3 is connected to the slit scanning plate 32.
さて動作時には、スリツト走査板３２のスリツ
ト３２ａによりＸ線管３１より発生したＸ線から
Ｘ線フアンビーム３６を形成し、このフアンビー
ム３６は被写体３４を透過して受像面であるイメ
ージ管３５の入力面に到達する。そして被写体３
４と受像面の間に散乱Ｘ線を除去するスリツト走
査板がないので、散乱Ｘ線と一次透過Ｘ線像の両
方がイメージ管３５に入り、イメージ管３５に第
４図ａのような像が得られる。この像のAA′断面
の輝度分布は第４図ｂのようになる。輝度分布の
中心部４１は一次透過Ｘ線によるもので必要とす
る像であり、周辺部４２は散乱Ｘ線によるもので
不必要なもので、これがコントラストを低下させ
る。そこで、この第４図ａの像をテレビカメラ３
７で撮像し、データー処理装置３８に送る。デー
ター処理装置３８では、スリツト走査板３２より
スリツトの位置信号発生器３３でスリツト走査板
３２の走査位置をデーター処理装置３８に送る。
このデーター処理装置３８でスリツト位置に対応
する１次透過Ｘ線の位置を検出し、その位置に相
当するテレビ像のみを取り出すことにより、第４
図ｂの中心部４１に相当する像即ち第４図ｃに相
当するものが取り出され、第４図ａから散乱Ｘ線
を除去した第４図ｄが得られ、被写体３４の後に
対応したスリツト走査板を配置して散乱Ｘ線を除
去したと同じ効果が得られる。更にスリツト走査
板３２の走査位置に対応するテレビ像上の位置
は、本装置で被写体３４をはずした状態でＸ線ビ
ームを走査し、走査位置信号に対する像位置をデ
ータ処理装置３８に記録させ、この記録を読み出
し使用することにより容易にスリツト走査板３２
と同期を取ることができる。又、このようにして
像位置を決めることにより、受像面にイメージ管
３５のように幾学的な歪を有する素子を使つても
走査スリツトと同期を取ることができ、スリツト
の走査機構が大巾に簡略化される。又、Ｘ線ビー
ムスキヤンを機械的走査でなく電子的走査のよう
に必ずしもリニアーな走査でなくても容易に同期
できる。又、被写体３４と受像面であるイメージ
管３５の間に走査スリツトがないので、この間隙
を狭くすることができ、Ｘ線拡大による像のボケ
が減少し鮮鋭な像が得られる。 During operation, the slit 32a of the slit scanning plate 32 forms an X-ray fan beam 36 from the X-rays generated from the X-ray tube 31. Reach the input surface. And subject 3
4 and the image receiving surface, both the scattered X-rays and the primary transmitted X-ray image enter the image tube 35, and an image as shown in FIG. is obtained. The brightness distribution on the AA' section of this image is as shown in Figure 4b. The center part 41 of the brightness distribution is caused by primary transmitted X-rays and is a necessary image, and the peripheral part 42 is caused by scattered X-rays and is unnecessary, and this reduces the contrast. Therefore, the image shown in Figure 4a was captured by the television camera 3.
7 and sends it to the data processing device 38. In the data processing device 38 , a slit position signal generator 33 sends the scanning position of the slit scanning plate 32 to the data processing device 38 .
This data processing device 38 detects the position of the primary transmitted X-ray corresponding to the slit position and extracts only the television image corresponding to that position.
An image corresponding to the central part 41 of FIG. 4b, that is, an image corresponding to FIG. 4c, is taken out, and FIG. The same effect as removing scattered X-rays by arranging a plate can be obtained. Furthermore, the position on the television image corresponding to the scanning position of the slit scanning plate 32 is determined by scanning the X-ray beam with this device with the subject 34 removed, and having the data processing device 38 record the image position corresponding to the scanning position signal. By reading and using this record, the slit scanning plate 32 can be easily
can be synchronized with. Furthermore, by determining the image position in this way, even if an element with geometric distortion, such as the image tube 35, is used on the image receiving surface, it can be synchronized with the scanning slit, and the scanning mechanism of the slit can be greatly improved. It is greatly simplified. Furthermore, the X-ray beam scans can be easily synchronized even if they are not necessarily linear scans, such as electronic scans rather than mechanical scans. Further, since there is no scanning slit between the subject 34 and the image tube 35 which is the image receiving surface, this gap can be narrowed, image blur due to X-ray magnification is reduced, and a sharp image can be obtained.
次に、この発明のＸ線撮影装置におけるＸ線の
曝射のタイミングおよび画像の記録の仕方の例に
ついて述べる。即ち、Ｘ線パルスは垂直方向の帰
線期間に第５図ａのように曝射する。この曝射に
よるＸ線フアンビームによる像がテレビカメラ３
７の撮像面に記録され、これを次のフイールドで
読み出すと、第５図ｂのような信号が得られる。
この信号はフイールド毎にスリツト走査板をフア
ンビームの巾ｓに相当するだけ移動させることに
より、ｂ図のように得られる。これらの信号を各
フイールド毎にデーター処理装置３８で前述のよ
うに散乱Ｘ線の影響を除去すると、ｃのような信
号が得られる。この信号を順次１枚のフイールド
メモリーに記録すると、ｄ図のように連結したイ
メージ像が記録される。この場合、ｃ図の信号を
フイールド間で完全に過不足がないように走査ス
リツトと走査スピード、フイールド間隙を調整す
ることは非常に難かしい。そこで、各フイールド
の像が若干重複するように走査スリツト巾を若干
巾広くして、メモリーに記録するときに、お互い
に重なる像の端の信号については、重複して記録
しないようにするか、両方重ねてその1/2を記録
する等の処理をすることにより、この困難を解消
することができる。又、Ｘ線スリツトを散乱Ｘ線
の影響が無視できる間隙に複数設けることによ
り、走査時間を短縮することができる。 Next, examples of the timing of X-ray exposure and the method of recording images in the X-ray imaging apparatus of the present invention will be described. That is, the X-ray pulse is emitted during the retrace period in the vertical direction as shown in FIG. 5a. The image of the X-ray fan beam resulting from this exposure is shown at the television camera 3.
7, and when this is read out in the next field, a signal as shown in FIG. 5b is obtained.
This signal is obtained as shown in figure b by moving the slit scanning plate for each field by an amount corresponding to the width s of the fan beam. When the influence of scattered X-rays is removed from these signals for each field by the data processing device 38 as described above, a signal like c is obtained. When these signals are sequentially recorded in one field memory, a connected image is recorded as shown in figure d. In this case, it is very difficult to adjust the scanning slit, scanning speed, and field gap so that there is no excess or deficiency of the signal in figure c between the fields. Therefore, the width of the scanning slit should be made slightly wider so that the images of each field overlap slightly, and when recording in memory, the signals at the edges of the images that overlap each other should not be recorded redundantly. This difficulty can be overcome by processing such as overlapping both and recording 1/2 of them. Further, by providing a plurality of X-ray slits in gaps where the influence of scattered X-rays can be ignored, scanning time can be shortened.
次に、この発明の他の実施例について述べる。
一般にＸ線透過像は骨や各種の臓器等の重なつた
像のため、非常に見ずらいものである。従つて、
コントラストを良くすると同時に、例えば胸部の
像から骨を分離した像が見られると非常に都合が
良い。そこで骨と筋肉ではＸ線の線質により若干
減衰率が異なることを利用して、高い線質のＸ線
の透過像と低い線質のＸ線の透過像の間で演算処
理することにより、骨の部分を除去した像の形成
が行なわれる。このようなＸ線像の作成誤差に
は、散乱Ｘ線の影響が非常に大きいので、この本
発明の応用効果の大きい分野である。第６図およ
び第７図にその例を説明する。先ず第６図につき
述べると、第３図の走査スリツト３２を静止させ
て、第６図のａのようにＸ線線質ＹのＸ線パルス
Ｙを曝射し、ｂのようにテレビカメラ３７出力信
号Ｓ（Y1）を得る。これをデーター処理装置３８
で散乱Ｘ線の影響を除去して第６図ｃのようにＩ
（Y1）を得る。次にＸ線線質ＺのＸ線パルスZ1を
曝射して同じくＩ（Z1）を得る。このＩ（Y1）と
Ｉ（Z1）をデーター処理装置３８で演算処理して
例えば骨の部分のデーターを除去し、第６図ｄの
ように信号J1（Y1Z1）を得る。これを第６図ｅの
ようにメモリーの所定の位置に記録する。次にＸ
線スリツト３２の位置を移動させて、同じくＸ線
パルスY2を曝射し同じくＩ（Y2）を得、次にＸ線
パルスZ2を曝射しＩ（Z2）を得、これよりＪ（Y2，
Z2）を得てこれをメモリーに記録する。このよう
にして順次記録することにより像を完成する。 Next, other embodiments of the invention will be described.
In general, X-ray transmission images are extremely difficult to see because they contain overlapping images of bones, various organs, and the like. Therefore,
It would be very convenient if the contrast could be improved and at the same time, for example, an image of the chest separated from the bones could be seen. Therefore, by taking advantage of the fact that bones and muscles have slightly different attenuation rates depending on the quality of the X-rays, we perform calculation processing between the transmission images of high-quality X-rays and the transmission images of low-quality X-rays. An image is formed with the bone portion removed. Since the error in creating such an X-ray image is greatly influenced by scattered X-rays, this is a field where the present invention can be applied to a large extent. An example will be explained in FIGS. 6 and 7. First, referring to FIG. 6, the scanning slit 32 in FIG. 3 is kept stationary, and an X-ray pulse Y of X-ray quality Y is emitted as shown in a of FIG. Obtain the output signal S(Y 1 ). This is transferred to the data processing device 38
By removing the influence of scattered X-rays, I
(Y 1 ) is obtained. Next, an X-ray pulse Z 1 of X-ray quality Z is irradiated to similarly obtain I(Z 1 ). These I(Y 1 ) and I(Z 1 ) are processed by the data processing device 38 to remove, for example, data on bone parts, and a signal J 1 (Y 1 Z 1 ) is obtained as shown in FIG. 6d. . This is recorded at a predetermined location in the memory as shown in FIG. 6e. Then X
By moving the position of the line slit 32, we irradiate the same X-ray pulse Y 2 to obtain the same I(Y 2 ), then we irradiate the X-ray pulse Z 2 to obtain I(Z 2 ), and from this, J( Y2 ,
Z 2 ) and record it in memory. By sequentially recording in this manner, the image is completed.
次に第７図の例について説明する。第６図の例
では、同じスリツト位置でＸ線を２度曝射しなけ
ればならないのでスリツト走査板をその都度停止
しなければならない。従つて制御機構が可成り複
雑となり、あまり短かい間隙では制御できないの
で時間がかかる。そこで第７図は、スリツト走査
板を停止させず撮影する例である。第３図のスリ
ツト走査板３２の走査速度に対してＸ線パルスの
巾は充分小さいものを使用し、第７図ａのように
Ｘ線線質ＹのＸ線パルスY1によりテレビカメラ
３７の出力信号Ｓ（Y1）が得られる。これよりデ
ーター処理装置３８で散乱Ｘ線の影響を除去し
て、第７図ｃのＩ（Y1）が得られる。スリツト走
査板３２の走査速度をテレビカメラの１フイール
ドの期間に、スリツト３２ａのスリツト巾の1/2
移動するように設定しておく。次にＸ線線質Ｚの
Ｘ線パルスZ1により同様にしてＩ（Z1）が得られ
る。そこでＩ（Y1）の後半とＩ（Z1）の前半は被
写体の同じ位置の像であるので、それぞれ演算処
理してＪ（Y1，Z1）を得る。このようにして次に
Ｊ（Y2，Z1）と順次出力を得て、第７図ｅのよう
に順次メモリーに記録することにより像を完成す
る。 Next, the example shown in FIG. 7 will be explained. In the example shown in FIG. 6, since X-rays must be irradiated twice at the same slit position, the slit scanning plate must be stopped each time. Therefore, the control mechanism becomes quite complex, and it takes time because it cannot be controlled with very short gaps. Therefore, FIG. 7 shows an example of photographing without stopping the slit scanning plate. The width of the X-ray pulse is sufficiently small for the scanning speed of the slit scanning plate 32 shown in FIG. 3, and as shown in FIG . An output signal S(Y 1 ) is obtained. From this, the influence of scattered X-rays is removed by the data processing device 38, and I(Y 1 ) shown in FIG. 7c is obtained. The scanning speed of the slit scanning plate 32 is set to 1/2 of the slit width of the slit 32a during one field of the TV camera.
Set it to move. Next, I(Z 1 ) is obtained in the same manner using an X-ray pulse Z 1 of X-ray quality Z. Therefore, since the second half of I(Y 1 ) and the first half of I(Z 1 ) are images at the same position of the subject, arithmetic processing is performed on each to obtain J(Y 1 , Z 1 ). In this way, the outputs J(Y 2 , Z 1 ) are sequentially obtained, and the images are completed by sequentially recording them in the memory as shown in FIG. 7e.
この発明のＸ線撮影装置は上記説明および図示
のように構成されているので、複雑で困難な機構
を用いないので、優れた性能が得られる。即ち、
感度大にして解像度が優れ、而も被曝量が少な
い。 Since the X-ray imaging apparatus of the present invention is configured as described above and shown in the drawings, it does not use any complicated or difficult mechanism, and therefore excellent performance can be obtained. That is,
It has high sensitivity, excellent resolution, and low radiation exposure.
尚、上記イメージ管３５の代りに、スリツト３
２ａと直交する方向に長いセンサを並べて、各々
から出力を取り出すようにしてもよい。 Incidentally, instead of the image tube 35, the slit 3
Long sensors may be arranged in a direction perpendicular to 2a, and outputs may be taken out from each sensor.
以上説明したようにこの発明によれば、工業的
価値大なるＸ線撮影装置を提供することができ
る。 As explained above, according to the present invention, it is possible to provide an X-ray imaging apparatus with great industrial value.
第１図は従来最もよく用いられるＸ線撮影装置
を示す構成図、第２図は一部に用いられている散
乱Ｘ線の除去効果の大きいＸ線スリツトを用いた
従来のＸ線撮影装置を示す構成図、第３図はこの
発明の一実施例に係るＸ線撮影装置を示す構成
図、第４図、第５図はこの発明の装置における動
作の説明図、第６図、第７図はこの発明の他の実
施例の説明図である。
１１，２１，３１……Ｘ線管、２２ａ，３２ａ
……スリツト、２２，３２……スリツト走査板、
１３，２３，３４……被写体、２４ａ……スリツ
ト、２４……スリツト走査板、１４……Ｘ線グリ
ツド、１５，２５……受像面、３５……イメージ
管、３７……テレビカメラ、３８……データ処理
装置、３９……受像機、３３……Ｘ線スリツト位
置信号発生器。
Figure 1 is a configuration diagram showing the most commonly used conventional X-ray imaging device, and Figure 2 shows a conventional X-ray imaging device that uses an X-ray slit, which is highly effective in removing scattered FIG. 3 is a configuration diagram showing an X-ray imaging apparatus according to an embodiment of the present invention, FIGS. 4 and 5 are explanatory diagrams of operations in the apparatus of this invention, and FIGS. 6 and 7. FIG. 2 is an explanatory diagram of another embodiment of the present invention. 11, 21, 31...X-ray tube, 22a, 32a
...Slit, 22, 32...Slit scanning plate,
13, 23, 34... Subject, 24a... Slit, 24... Slit scanning plate, 14... X-ray grid, 15, 25... Image receiving surface, 35... Image tube, 37... Television camera, 38... ...Data processing device, 39...Receiver, 33...X-ray slit position signal generator.
Claims (1)
ト走査板、イメージ管、撮像・記憶・演算装置、
表示器を順次所定間隔で配列し、且つ前記スリツ
ト走査板と前記演算装置との間に位置信号発生器
を接続してなり、前記スリツト走査板と前記イメ
ージ管との間に被写体を配置し、前記スリツト走
査板によりＸ線フアンビームを形成し前記被写体
を透過させて得た散乱Ｘ線と１次透過Ｘ線を前記
イメージ管を介して前記撮像・記憶・演算装置に
送り、更に前記位置信号発生器で前記スリツト走
査板の走査位置を前記演算装置に送り、この演算
装置でスリツト位置に対応する１次透過Ｘ線の位
置を検出し、その位置に相当する像のみを取出す
ことを特徴とするＸ線撮影装置。 ２ 撮像の各フイールド毎にそのフイールド期間
により充分小さい期間、前記スリツトにより形成
されたＸ線フアンビームを曝射し、そのＸ線フア
ンビームの１次線の幅および位置に相当する部分
のみ信号を取り出し記録することを、Ｘ線フアン
ビームの走査に従つて順次繰り返し、連続した２
次元透過像を得る特許請求の範囲第１項記載のＸ
線撮影装置。 ３ 複数のＸ線フアンビームを用いる特許請求の
範囲第１項記載のＸ線撮影装置。 ４ 隣接するフイールドで線質の異なるＸ線フア
ンビームにより得られた被写体の同じ部分のＸ線
透過像のフイールド間の各画素間に演算処理を行
つて各画素を構成する特許請求の範囲第１項記載
のＸ線撮影装置。[Scope of Claims] 1.
display devices are sequentially arranged at predetermined intervals, a position signal generator is connected between the slit scanning plate and the arithmetic unit, and a subject is placed between the slit scanning plate and the image tube; An X-ray fan beam is formed by the slit scanning plate, and the obtained scattered X-rays and primary transmitted X-rays are transmitted through the image tube to the imaging/storage/arithmetic device, and further the position signal is sent to the imaging/storage/arithmetic device. The generator sends the scanning position of the slit scanning plate to the arithmetic unit, the arithmetic unit detects the position of the primary transmitted X-ray corresponding to the slit position, and extracts only the image corresponding to that position. X-ray imaging equipment. 2. For each field of imaging, the X-ray fan beam formed by the slit is irradiated for a sufficiently smaller period than the field period, and a signal is emitted only in a portion corresponding to the width and position of the primary line of the X-ray fan beam. The extraction and recording is repeated sequentially according to the scanning of the X-ray fan beam, and two consecutive
X according to claim 1 for obtaining a dimensional transmission image
Ray imaging device. 3. The X-ray imaging apparatus according to claim 1, which uses a plurality of X-ray fan beams. 4. Claim 1, in which each pixel is constructed by performing arithmetic processing between each pixel between fields of X-ray transmission images of the same part of the subject obtained by X-ray fan beams with different radiation qualities in adjacent fields. The X-ray imaging device described in Section 1.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP56168961A JPS5869532A (en) | 1981-10-22 | 1981-10-22 | X-ray photography apparatus |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP56168961A JPS5869532A (en) | 1981-10-22 | 1981-10-22 | X-ray photography apparatus |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5869532A JPS5869532A (en) | 1983-04-25 |
| JPH04436B2 true JPH04436B2 (en) | 1992-01-07 |
Family
ID=15877762
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP56168961A Granted JPS5869532A (en) | 1981-10-22 | 1981-10-22 | X-ray photography apparatus |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5869532A (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS60111637A (en) * | 1983-11-22 | 1985-06-18 | 株式会社東芝 | X-ray diagnostic apparatus |
| JPS6454506U (en) * | 1987-09-30 | 1989-04-04 |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5618842A (en) * | 1979-07-23 | 1981-02-23 | Tokyo Shibaura Electric Co | Xxray device for diagnosis |
-
1981
- 1981-10-22 JP JP56168961A patent/JPS5869532A/en active Granted
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5618842A (en) * | 1979-07-23 | 1981-02-23 | Tokyo Shibaura Electric Co | Xxray device for diagnosis |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5869532A (en) | 1983-04-25 |
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