JPS6343099B2 - - Google Patents
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- Publication number
- JPS6343099B2 JPS6343099B2 JP55147918A JP14791880A JPS6343099B2 JP S6343099 B2 JPS6343099 B2 JP S6343099B2 JP 55147918 A JP55147918 A JP 55147918A JP 14791880 A JP14791880 A JP 14791880A JP S6343099 B2 JPS6343099 B2 JP S6343099B2
- Authority
- JP
- Japan
- Prior art keywords
- radiation
- subject
- diagnostic apparatus
- sampling
- control means
- 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
- 230000005855 radiation Effects 0.000 claims description 46
- 230000005540 biological transmission Effects 0.000 claims description 22
- 238000005070 sampling Methods 0.000 claims description 22
- 238000013480 data collection Methods 0.000 claims description 11
- 238000001514 detection method Methods 0.000 claims description 7
- 230000005251 gamma ray Effects 0.000 claims description 2
- 239000000470 constituent Substances 0.000 claims 1
- 238000010586 diagram Methods 0.000 description 5
- 230000006870 function Effects 0.000 description 4
- 238000003745 diagnosis Methods 0.000 description 3
- 239000003990 capacitor Substances 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 210000000038 chest Anatomy 0.000 description 1
- 238000002591 computed tomography Methods 0.000 description 1
- 239000013078 crystal Substances 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
- 210000004072 lung Anatomy 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000013441 quality evaluation Methods 0.000 description 1
- 230000003252 repetitive effect Effects 0.000 description 1
- 229910052710 silicon Inorganic materials 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- 229910052724 xenon Inorganic materials 0.000 description 1
- FHNFHKCVQCLJFQ-UHFFFAOYSA-N xenon atom Chemical compound [Xe] FHNFHKCVQCLJFQ-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、コントラスト解像力の優れた（すな
わち、その階調度のダイナミツク・レンジの広
い）被検体透過像を得る放射線診断装置に係り、
特に被検体細部の拡大表示を可能とする放射線診
断装置に関するものである。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a radiological diagnostic apparatus that obtains a transmitted image of a subject with excellent contrast resolution (that is, a wide dynamic range of gradations).
In particular, the present invention relates to a radiological diagnostic apparatus that enables enlarged display of details of a subject.
通常のＸ線診断装置によるＸ線フイルム上の被
検体透過像とCTスキヤナ（コンピユータ断層装
置）による断層像とを画質評価という観点で比較
した場合、空間解像力では前者の方が優れている
が、コントラスト解像力（階調識別能力）では後
者が少なくとも15〜20倍優れている。従つて例え
ば肺の内部組織の診断など、高いコントラスト解
像力が要求される診断分野に対しては、前者のみ
では不充分である。このため、Ｘ線ビームを１つ
の平面上に扇形状に放射するＸ線源を用いたCT
スキヤナ（いわゆるフアンビーム型CTスキヤナ）
において、前記平面に垂直方向（これをＸ方向と
定義する。）に、被検体を、Ｘ線源およびＸ線検
出器（検出器セル配列方向を直線とみなしてそれ
をＹ方向と定義する。）に対して相対的に移動さ
せることにより、そのコントラスト解像力がCT
スキヤナの断層像とほぼ等しくしかも被検体の被
曝線量も少ない、デイジタル的なＸ線透過像を作
ることが行なわれている。然るに肺胞の微細組織
等を観察したい場合には、コントラスト解像力と
同様、高い空間解像力も必要となる。この点で既
存のCTスキヤナのＸ線検出器では、検出器セル
数、すなわちチヤネル数が500〜1000個程度であ
り、断層像を得るためにはＸ線検出器（セル列）
のＹ方向の長さが胸部の体幅長をカバーしなけれ
ばならないので、Ｙ方向についての分解能が制限
され前記肺胞微細組織を診断するのに充分な空間
解像力は望めない。またCTスキヤナではＸ線源
−被検体間距離（このＸ線源−被検体の対向方向
をＺ方向と定義する）を大幅に変化させることは
機構的に難しく、該距離を変えて拡大透過像を得
ることは容易ではない。仮に前記距離を変え得て
も、前記Ｘ線透過像を得るためのＸ方向への相対
的な移動速度、あるいは該方向への移動に伴うデ
ータ収集手段のサンプリング・タイミングを適切
に選択制御することはできず、拡大率がＸ、Ｙ両
方向で異なつて（画素の幅が方向により異なつ
て）しまい、正確な拡大Ｘ線透過像は得られなか
つた。このことはCTスキヤナのみならずコント
ラスト解像力の高いデイジタル的なＸ線透過像を
得る目的で構成された専用の装置についても該当
する。 When comparing a transmitted image of a subject on an X-ray film by a normal X-ray diagnostic device and a tomographic image by a CT scanner (computer tomography device) from the perspective of image quality evaluation, the former has superior spatial resolution; The latter is at least 15 to 20 times better in terms of contrast resolution (gradation discrimination ability). Therefore, the former alone is insufficient for diagnostic fields that require high contrast resolution, such as diagnosis of internal tissue of the lungs. For this reason, CT using an X-ray source that emits an X-ray beam in a fan shape on one plane
Scanner (so-called fan beam type CT scanner)
In the above, the subject is placed in a direction perpendicular to the plane (this is defined as the X direction), and an X-ray source and an X-ray detector (the direction in which the detector cells are arranged is regarded as a straight line and is defined as the Y direction). ), its contrast resolution can be improved by moving it relative to CT.
Digital X-ray transmission images, which are almost the same as scanner tomographic images and which expose the subject to less radiation, are being created. However, when it is desired to observe fine structures such as alveoli, high spatial resolution as well as contrast resolution is required. In this regard, existing CT scanner X-ray detectors have a number of detector cells, or channels, of approximately 500 to 1000, and in order to obtain a tomographic image, the number of X-ray detectors (cell rows)
Since the length in the Y direction must cover the body width of the thorax, the resolution in the Y direction is limited and sufficient spatial resolution cannot be expected for diagnosing the alveolar fine tissue. In addition, in CT scanners, it is mechanically difficult to significantly change the distance between the X-ray source and the subject (the facing direction of the X-ray source and the subject is defined as the Z direction), so it is difficult to change the distance between the X-ray source and the subject. is not easy to obtain. Even if the distance can be changed, the relative speed of movement in the X direction for obtaining the X-ray transmission image, or the sampling timing of the data collection means associated with movement in the direction, should be appropriately selected and controlled. However, the magnification ratio was different in both the X and Y directions (the width of the pixel was different depending on the direction), and an accurate enlarged X-ray transmission image could not be obtained. This applies not only to CT scanners but also to specialized equipment configured for the purpose of obtaining digital X-ray transmission images with high contrast resolution.
本発明は、上述した事情に鑑みて成されたもの
で、１つの平面上に扇形を形成する放射線ビーム
を発生する放射線源と、該放射線ビームをそれぞ
れ予定角度間隔で検出するように多数配列された
検出器セルからなる放射線検出器の両者を、被検
体に対し相対的にＸ方向に移動させることにより
被検体透過像を得、さらに放射線源−被検体間距
離を変化し得るようにするとともに該変化に対応
したサンプリング・タイミングで前記放射線検出
器の出力情報を収集するようにすることにより、
簡単な構成で所望の拡大率の被検体透過像を得る
ことを可能とする放射線診断装置を提供すること
を目的としている。 The present invention has been made in view of the above-mentioned circumstances, and includes a radiation source that generates a radiation beam forming a fan shape on one plane, and a large number of radiation sources arranged so as to detect each of the radiation beams at predetermined angular intervals. By moving both of the radiation detectors consisting of detector cells in the X direction relative to the subject, a transmitted image of the subject can be obtained, and the distance between the radiation source and the subject can be changed. By collecting the output information of the radiation detector at a sampling timing corresponding to the change,
It is an object of the present invention to provide a radiological diagnostic apparatus that can obtain a transmission image of a subject at a desired magnification with a simple configuration.
以下図面を参照して本発明の実施例を説明す
る。 Embodiments of the present invention will be described below with reference to the drawings.
第１図は本発明による放射線診断装置の一実施
例の構成を示すものである。 FIG. 1 shows the configuration of an embodiment of a radiation diagnostic apparatus according to the present invention.
図において１はＸ線源、２はＸ線源１から発せ
られるＸ線ビームを１平面上の扇形状に放射させ
るためのコリメータ、３は被検体、４は寝台、５
は500〜1000個のSi（シリコン）単結晶またはXe
（キセノン）ガスセルからなる検出器セルで構成
されＸ線源１からコリメータ２を介して放射され
るＸ線ビームXBをそれぞれ予定角度間隔で検出
するＸ線検出器、６は後述するサンプリング・タ
イミング制御信号Ｓ１によりＸ線検出器５の出力
をサンプリング入力するデータ収集回路、７は寝
台４のＺ方向の位置（すなわちＸ線源−被検体間
の距離に対応する位置）を検出するために両端を
それぞれ＋Ｖの正電源及び接地点に接続し且つ可
動端を寝台４のＺ方向移動に連動させた可変抵
抗、８は可変抵抗７の出力アナログ信号Ｓ２に基
づいて、その繰り返しパルス周期が決定される一
定パルス幅のパルス列のサンプリング・タイミン
グ制御信号Ｓ１を発生するPFM（パルス周波数変
調）回路、９はデータ収集回路６から被検体３ａ
の各点のＸ線透過データを順次蓄積しさらに所望
の画像処理を施す記憶演算制御部、１０は記憶演
算制御部９の出力により被検体３のＸ線透過像を
表示する表示装置である。なお、３Ａ，４Ａは被
検体３、寝台４を図示実線の状態からＺ方向に移
動させた一状態を示している。また前記Ｘ線源１
および前記Ｘ線検出器５を被検体３に対しＸ方向
に相対的に移動させるものとし、且つ、前記扇形
を含む平面と、被検体３の関心領域（診断を所望
する領域）が交わる間のみ、Ｘ線源１からＸ線が
ほぼ連続的に発せられるものとする。 In the figure, 1 is an X-ray source, 2 is a collimator for emitting the X-ray beam emitted from the X-ray source 1 in a fan shape on one plane, 3 is a subject, 4 is a bed, and 5
is 500 to 1000 Si (silicon) single crystals or Xe
The X-ray detector is composed of a detector cell consisting of a (xenon) gas cell and detects the X-ray beam XB emitted from the X-ray source 1 via the collimator 2 at predetermined angular intervals, and 6 is the sampling timing control described later. A data acquisition circuit 7 samples and inputs the output of the X-ray detector 5 using a signal S1, and a data acquisition circuit 7 connects both ends of the bed 4 in order to detect the position in the Z direction (i.e., the position corresponding to the distance between the X-ray source and the subject). A variable resistor 8 is connected to the positive power supply of +V and a ground point, and whose movable end is linked to the movement of the bed 4 in the Z direction.The repetition pulse period is determined based on the output analog signal S2 of the variable resistor 7. A PFM (Pulse Frequency Modulation) circuit that generates a sampling timing control signal S1 of a pulse train with a constant pulse width;
10 is a display device that displays an X-ray transmission image of the subject 3 based on the output of the storage calculation control section 9. Note that 3A and 4A indicate a state in which the subject 3 and bed 4 are moved in the Z direction from the state indicated by the solid line in the figure. In addition, the X-ray source 1
The X-ray detector 5 shall be moved relative to the subject 3 in the X direction, and only during the period where the plane containing the fan shape intersects the region of interest (area where diagnosis is desired) of the subject 3. , it is assumed that X-rays are emitted almost continuously from the X-ray source 1.
第２図は上記PFM回路８の一具体例の詳細図
であり、図示のごとくタイマ用ICであるNE55V
（シグネテイクス社）Ｉ１、抵抗Ｒ１、およびコ
ンデンサＣ１，Ｃ２により構成されている。 FIG. 2 is a detailed diagram of a specific example of the above PFM circuit 8, and as shown in the figure, the timer IC NE55V
(Signetakes) I1, resistor R1, and capacitors C1 and C2.
次に上述の構成における動作の説明する。 Next, the operation in the above configuration will be explained.
今、被検体３、および寝台４をＸ方向に関し
て、以後関心領域を診断すべく関心領域のＸ方向
についての一端部の位置にセツトし、Ｘ線源１か
らコメリータ２を介して被検体３にＸ線ビーム
XBを照射し始めるとともに前記Ｘ線源１および
Ｘ線検出器５を該被検体３に対してＸ方向に相対
的に一定速度で移動させる。このとき前記Ｘ線検
出器５の各検出器セルのＹ方向の間隔に対応する
被検体３上の間隔つまり被検体３上での投影Ｘ線
パスの間隔ｄ１により前記被検体３の透過像のＹ
方向の空間解像力は決定されるが、該透過像上
で、Ｘ方向、Ｙ方向で等しい拡大率を得るために
は、前記相対的なＸ方向の移動に際して、データ
収集回路６はｄ１の距離の移動毎に前記Ｘ線検出
器５の出力信号をサンプリング入力し、記憶演算
制御部９に予定の変換データを転送しなければな
らない。 Now, the subject 3 and the bed 4 are set in the X-direction at one end of the region of interest in order to diagnose the region of interest from now on, and the X-ray source 1 is connected to the subject 3 via the commeritor 2. x-ray beam
At the same time that XB irradiation is started, the X-ray source 1 and X-ray detector 5 are moved at a constant speed relative to the subject 3 in the X direction. At this time, the transmission image of the subject 3 is determined by the interval on the subject 3 corresponding to the interval in the Y direction between each detector cell of the X-ray detector 5, that is, the interval d1 of the projected X-ray path on the subject 3. Y
The spatial resolution in the direction is determined, but in order to obtain the same magnification in the X direction and Y direction on the transmitted image, the data acquisition circuit 6 must adjust the distance of d1 during the relative movement in the X direction. The output signal of the X-ray detector 5 must be sampled and the planned conversion data must be transferred to the storage arithmetic control section 9 for each movement.
これは、前記Ｘ線源−被検体間距離を、その可
動端が寝台４と連動する可変抵抗７で検出し、こ
の検出出力であるアナログ信号Ｓ２をPFM回路
８に入力し、さらに該PFM回路８で、該信号Ｓ
２に対応する繰り返しパルス周期で且つ一定パル
ス幅を有するパルス列のサンプリング・タイミン
グ制御信号Ｓ１を得て該信号Ｓ１で前記データ収
集回路６のサンプリングを制御することで実現さ
れる。従つて前記記憶演算制御部９に順次格納さ
れた前記被検体３の各点のＸ線透過情報によつ
て、表示装置１０上には第３図に示すごとく、各
画素がＸ、Ｙ両方向で等しいｄ１の長さにすなわ
ち同じ拡大率で表示されるため、正確な拡大率の
Ｘ線透過像が得られる。 This detects the distance between the X-ray source and the subject with a variable resistor 7 whose movable end is interlocked with the bed 4, inputs the analog signal S2 which is the detection output to the PFM circuit 8, and further inputs the analog signal S2 to the PFM circuit 8. 8, the signal S
This is realized by obtaining a sampling timing control signal S1 of a pulse train having a repetitive pulse period corresponding to 2 and a constant pulse width, and controlling the sampling of the data acquisition circuit 6 using the signal S1. Therefore, as shown in FIG. 3, each pixel is displayed on the display device 10 in both the X and Y directions based on the X-ray transmission information of each point of the subject 3 sequentially stored in the storage calculation control section 9. Since the images are displayed at the same length d1, that is, at the same magnification, an X-ray transmission image with an accurate magnification can be obtained.
次に寝台４をＺ方向に移動してＸ線源−被検体
間距離が上述の場合の約半分になる様に被検体
３、寝台４をそれぞれ図示３Ａ，４Ａの位置に移
動したとする。このときには上述（つまりもとの
位置）の場合に比べＸ線透過像のＹ方向の空間解
像力は約２倍となる。このときデータ収集回路６
が上述の場合と同様なサンプリング・タイミング
でＸ線検出器５の出力信号をサンプリングしたの
では、表示装置１０上のＸ線透過像が第４図のご
とく、そのＸ方向についての空間解像力がＹ方向
に比べて約半分（つまり画素のＸ方向寸法がＹ方
向寸法の約２倍）となり、両方向で等しい正確な
拡大率の像は得られない。このため寝台４の位置
4A（つまり被検体３の位置3A）を可変抵抗７で
検出し、さらにPFM回路８で、その繰り返しパ
ルス周期が上述の（もとの位置の）場合の約半分
のサンプリング・タイミング制御信号Ｓ１を得
て、データ収集回路６を制御する。従つて、Ｘ線
透過像のＸ方向の空間解像力も約２倍になるの
で、第３図の場合と同様の、正しいＸ線透過像を
表示装置１０上に表示することができる。 Next, it is assumed that the bed 4 is moved in the Z direction and the subject 3 and the bed 4 are moved to positions 3A and 4A in the figure, respectively, so that the distance between the X-ray source and the subject becomes approximately half of that in the above case. At this time, the spatial resolution of the X-ray transmission image in the Y direction is approximately twice that of the case described above (that is, the original position). At this time, the data collection circuit 6
If the output signal of the X-ray detector 5 is sampled at the same sampling timing as in the above case, the X-ray transmitted image on the display device 10 will have a spatial resolution in the X direction as shown in FIG. This is approximately half the size of the pixel in the X direction (that is, the size of the pixel in the X direction is approximately twice the size of the pixel in the Y direction), and an image with the same accurate magnification in both directions cannot be obtained. Therefore, the position of bed 4
4A (that is, the position 3A of the object 3) is detected by the variable resistor 7, and the PFM circuit 8 generates a sampling timing control signal S1 whose repetition pulse period is approximately half that of the above-mentioned (original position) case. and controls the data acquisition circuit 6. Therefore, the spatial resolution of the X-ray transmission image in the X direction is also approximately doubled, so that a correct X-ray transmission image similar to that shown in FIG. 3 can be displayed on the display device 10.
以上のようにすれば、従来のＸ線フイルム上へ
被検体透過像を結ぶ、Ｘ線診断装置に比べ、コン
トラスト解像力が格段に優れたＸ線透過像を得る
ことができ、また被検体の被曝線量の低減も図れ
る他、幅広い拡大率レンジによつて、従来Ｘ線フ
イルムによる撮像装置に比べて劣るとされていた
空間解像力の点でも、決して劣らない体内細部の
拡大Ｘ線透過像を得ることができる。また、体内
細部各点でのＸ線透過情報が、デイジタル的に記
憶されるので、診断に適した画像処理を施すこと
も可能である。しかも、構成も簡単である。 By doing the above, it is possible to obtain an X-ray transmission image with much superior contrast resolution compared to conventional X-ray diagnostic equipment that forms a transmission image of the subject on an X-ray film, and also In addition to reducing radiation doses, the wide magnification range allows for the acquisition of enlarged X-ray transmission images of internal details that are comparable to conventional X-ray film imaging devices in terms of spatial resolution, which was considered to be inferior. I can do it. Furthermore, since X-ray transmission information at each detailed point within the body is stored digitally, it is also possible to perform image processing suitable for diagnosis. Furthermore, the configuration is simple.
なお、本発明は、決して上記実施例にのみ限定
されることなく、その主旨を変更しない範囲で
様々に変形して実施し得るものである。 It should be noted that the present invention is by no means limited to the above embodiments, and can be implemented with various modifications without changing the spirit thereof.
例えば、上記実施例では、放射線源および放射
線検出器として、それぞれＸ線源１（例えばＸ線
管装置）、Ｘ線検出器５を用いたが、ガンマ線検
出器としても良い。 For example, in the above embodiment, the X-ray source 1 (for example, an X-ray tube device) and the X-ray detector 5 are used as the radiation source and the radiation detector, respectively, but a gamma ray detector may also be used.
また、データ収集手段のサンプリング・タイミ
ングを制御する手段として、PFM回路８を用い
たが、第５図のごとき構成を用いても良い。 Further, although the PFM circuit 8 is used as means for controlling the sampling timing of the data collecting means, a configuration as shown in FIG. 5 may also be used.
第５図において１１は可変抵抗７の出力アナロ
グ電圧信号Ｓ２が入力されるＡ／Ｄ（アナログ−
デイジタル）変換器、１２はＡ／Ｄ変換器１１の
出力に基づき、択一的に出力を選択する、すなわ
ち複数出力端のうち入力に応じた１出力に論理
「１」を出力するデコーダ、１３１，１３２，…
１３ｎ、はゲート回路、１４は発振器、１５１，
１５２，…１５ｎは、それぞれ分周率の異なる分
周カウンタ、１６は該分周カウンタ１５１〜１５
ｎのそれぞれのキヤリー出力の論理和をとるゲー
ト回路である。すなわち、寝台４の位置に応じ
た、可変抵抗７の出力アナログ電圧信号Ｓ２を
Ａ／Ｄ変換器１１でデイジタル化し、そのデイジ
タル値に基づきデコーダ１２が、ゲート回路１３
１〜１３ｎのうちの１つを開く。一方、発振器１
４の出力は、ゲート回路１３１，〜１３ｎに入力
されているので、該ゲート回路１３１〜１３ｎの
次段にそれぞれ接続されている分周カウンタ１５
１，〜１５ｎのうちの１つが、作動しその分周カ
ウンタの分周率に応じた所定の繰り返し周期でキ
ヤリー出力パルスがゲート回路１６を介してサン
プリング・タイミング制御信号Ｓ１として出力さ
れ、データ収集回路６を制御する。従つて上述の
PFM回路８と同様な、機能を発揮できる。 In FIG. 5, reference numeral 11 denotes an A/D (analog--
A decoder 131 which selectively selects an output based on the output of the A/D converter 11, that is, outputs a logic "1" to one output corresponding to the input among the plurality of output terminals. ,132,...
13n is a gate circuit, 14 is an oscillator, 151,
152,...15n are frequency division counters with different frequency division ratios, and 16 is the frequency division counter 151 to 15.
This is a gate circuit that takes the logical sum of the respective carry outputs of n. That is, the output analog voltage signal S2 of the variable resistor 7 corresponding to the position of the bed 4 is digitized by the A/D converter 11, and the decoder 12 converts the gate circuit 13 based on the digital value.
Open one of 1-13n. On the other hand, oscillator 1
Since the output of 4 is input to the gate circuits 131 to 13n, the frequency dividing counter 15 connected to the next stage of the gate circuits 131 to 13n respectively
1, to 15n is activated, and a carry output pulse is output as the sampling timing control signal S1 via the gate circuit 16 at a predetermined repetition period according to the frequency division ratio of the frequency division counter, and data collection is performed. Controls circuit 6. Therefore, the above
It can perform the same function as PFM circuit 8.
さらに、この場合のデコーダを入力データに応
じた数値データを出力するものに代え該デコーダ
出力でプリセツトカウンタをプリセツトさせるよ
うにして、該プリセツトカウンタによる分周率を
制御させ所要周波数の信号を得るようにしても良
い。 Furthermore, the decoder in this case is replaced with one that outputs numerical data according to the input data, and the output of the decoder is used to preset a preset counter, and the frequency division rate of the preset counter is controlled to generate a signal of the desired frequency. You can also try to get it.
また、PFM回路８に代えていわゆるVCO（電
圧制御発振器）等のＶ／Ｆ（電圧−周波数）変換
器を用いても良い。 Further, instead of the PFM circuit 8, a V/F (voltage-frequency) converter such as a so-called VCO (voltage controlled oscillator) may be used.
もちろん、上述の構成の大部分はCTスキヤナ
と共用できるので、放射線源、放射線検出器、デ
ータ収集手段、記憶演算制御手段および表示手段
等を共用して上述の機能とCTスキヤナの機能を
兼備させ上述の機能を利用してCTスキヤナのス
ライス位置決定が正確に行なえる装置とすること
もできる。 Of course, most of the above configuration can be shared with the CT scanner, so the radiation source, radiation detector, data collection means, storage/computation control means, display means, etc. can be shared to provide the above functions and the functions of the CT scanner. Utilizing the above-mentioned functions, it is also possible to create an apparatus that can accurately determine the slice position of a CT scanner.
以上詳述したように、本発明によれば、１つの
平面上に扇形を形成する放射線ビームを発生する
放射線源と、該放射線ビームをそれぞれ予定角度
間隔で検出するように多数配列された検出器セル
からなる放射線検出器の両者を、被検体に対し相
対的にＸ方向に移動させることにより被検体透過
像を得、さらに放射線源−被検体間距離を変化し
得るようにするとともに該変化に対応したサンプ
リング・タイミングで前記放射線検出器の出力情
報を収集するようにすることにより、簡単な構成
であるにもかかわらず所望の拡大率の被検体透過
像を得ることを可能とする放射線診断装置を提供
することができる。 As detailed above, according to the present invention, there is provided a radiation source that generates a radiation beam forming a fan shape on one plane, and a large number of detectors arranged to detect the radiation beams at predetermined angular intervals. By moving both radiation detectors consisting of cells in the X direction relative to the subject, a transmitted image of the subject is obtained, and the distance between the radiation source and the subject can be changed, and the distance between the radiation source and the subject can be changed. A radiological diagnostic apparatus that makes it possible to obtain a transmitted image of a subject with a desired magnification despite having a simple configuration by collecting output information of the radiation detector at corresponding sampling timings. can be provided.
第１図は本発明の一実施例の構成を示すシステ
ム・ブロツク図、第２図はその要部構成を示す回
路図、第３図は各画素が正方形である正確なＸ線
透過像を説明するための図、第４図は、Ｘ方向と
Ｙ方向とで拡大率が異なるＸ線透過像を説明する
ための図、第５図は本発明の他の実施例の要部構
成を示す図である。
１……Ｘ線源、２……コリメータ、３……被検
体、４……寝台、５……Ｘ線検出器、６……デー
タ収集回路、７……可変抵抗、８……PFM回路、
９……記憶演算制御部、１０……表示装置、１１
……Ａ／Ｄ変換器、１２……デコーダ、１３１，
〜１３ｎ，１６……ゲート回路、１４……発振
器、１５１，〜１５ｎ……分周カウンタ。
Fig. 1 is a system block diagram showing the configuration of an embodiment of the present invention, Fig. 2 is a circuit diagram showing the main part configuration, and Fig. 3 explains an accurate X-ray transmission image in which each pixel is a square. FIG. 4 is a diagram for explaining an X-ray transmission image with different magnifications in the X direction and Y direction, and FIG. 5 is a diagram showing the main part configuration of another embodiment of the present invention. It is. 1... X-ray source, 2... Collimator, 3... Subject, 4... Bed, 5... X-ray detector, 6... Data acquisition circuit, 7... Variable resistor, 8... PFM circuit,
9... Memory calculation control unit, 10... Display device, 11
... A/D converter, 12 ... Decoder, 131,
~13n, 16... Gate circuit, 14... Oscillator, 151, ~15n... Frequency division counter.
Claims (1)
を発生する放射線源と、前記放射線ビームをそれ
ぞれ予定角度間隔毎に検出するように多数配列さ
れた検出器セルからなる放射線検出器と、前記扇
形を含む平面に対して直角の方向について被検体
と前記放射線源−前記放射線検出器系を相対的に
移動させる駆動手段と、前記被検体を前記放射線
源との間の距離を検出する距離検出手段と、前記
放射線検出器の出力信号をサンプリング入力し予
定の情報に変換するデータ収集手段と、前記距離
検出手段の出力信号に応じて前記データ収集手段
のサンプリング・タイミング制御するサンプリン
グ制御手段と、前記データ収集手段で収集された
情報を蓄積し前記被検体透過像を構成する記憶演
算制御手段と、この記憶演算制御手段で構成され
た透過像を表示する表示手段とを具備してなる放
射線診断装置。 ２ 特許請求の範囲第１項記載の放射線診断装置
において、放射線源として、Ｘ線管装置を用いた
ことを特徴とする放射線診断装置。 ３ 特許請求の範囲第１項記載の放射線診断装置
において、放射線源として、ガンマ線源を用いた
ことを特徴とする放射線診断装置。 ４ 特許請求の範囲第１項〜第３項のいずれかに
記載の放射線診断装置において、距離検出手段
は、被検体を支持する寝台の所定方向の動作に可
動端が連動する可変抵抗を用いて構成したことを
特徴とする放射線診断装置。 ５ 特許請求の範囲第４項記載の放射線診断装置
において、サンプリング制御手段は、可変抵抗の
可動端に発生し被検体−放射線源間距離に対応し
て変化するアナログ電圧信号を入力とするパルス
周波数変調（PFM）回路を用い、前記アナログ
電圧値に対応した繰返し周波数を持つパルス列を
サンプリング・タイミング信号として出力する構
成としたことを特徴とする放射線診断装置。 ６ 特許請求の範囲第４項記載の放射線診断装置
において、サンプリング制御手段は、可変抵抗の
可動端に発生し被検体−放射線源間距離に対応し
て変化するアナログ電圧信号をＡ／Ｄ変換器でデ
イジタル値に変換し該デイジタルデータをデコー
ダでデコードし、該デコード信号を発振器からの
出力を異なる分周率で分周する分周カウンタ群の
選択制御に用い、さらに各分周カウンタのキヤリ
出力信号の論理和をサンプリング・タイミング制
御信号として出力する構成としたことを特徴とす
る放射線診断装置。 ７ １つの平面上で扇形を形成する放射線ビーム
を発生する放射線源と、前記放射線ビームをそれ
ぞれ予定角度間隔毎に検出するように多数配列さ
れた検出器セルからなる放射線検出器と、前記扇
形を含む平面に対して直角の方向について被検体
と前記放射線源−前記放射線検出器系を相対的に
移動させる駆動手段と、前記被検体と前記放射線
源との間の距離を検出する距離検出手段と、前記
放射線検出器の出力信号をサンプリング入力し予
定の情報に変換するデータ収集手段と、前記距離
検出手段の出力信号に応じて前記データ収集手段
のサンプリング・タイミングを制御するサンプリ
ング制御手段と、前記データ収集手段で収集され
た情報を蓄積し前記被検体透過像を構成する記憶
演算制御手段と、この記憶演算制御手段で構成さ
れた透過像を表示する表示手段とを具備した放射
線診断装置において、放射線源、放射線検出器、
データ収集手段、記憶演算制御手段、および表示
手段をCTスキヤナの構成要素と共通としてCTス
キヤナを構成しさらに距離検出手段およびサンプ
リング制御手段の両者を付加したことを特徴とす
る放射線診断装置。[Claims] 1. Radiation detection comprising a radiation source that generates a radiation beam forming a fan shape on one plane, and a large number of detector cells arranged so as to detect each of the radiation beams at predetermined angular intervals. a drive means for relatively moving the subject and the radiation source-the radiation detector system in a direction perpendicular to a plane including the fan shape; distance detection means for detecting, data collection means for sampling and inputting the output signal of the radiation detector and converting it into scheduled information, and sampling for controlling the sampling timing of the data collection means according to the output signal of the distance detection means. A control means, a memory calculation control means for accumulating the information collected by the data collection means and forming the object transmission image, and a display means for displaying the transmission image formed by the storage calculation control means. Radiological diagnostic equipment. 2. A radiological diagnostic apparatus according to claim 1, characterized in that an X-ray tube device is used as a radiation source. 3. A radiological diagnostic apparatus according to claim 1, characterized in that a gamma ray source is used as a radiation source. 4. In the radiological diagnostic apparatus according to any one of claims 1 to 3, the distance detection means uses a variable resistor whose movable end is interlocked with movement in a predetermined direction of a bed supporting the subject. A radiation diagnostic apparatus characterized by comprising: 5. In the radiological diagnostic apparatus according to claim 4, the sampling control means receives as input an analog voltage signal generated at the movable end of the variable resistor and changes in accordance with the distance between the subject and the radiation source. 1. A radiation diagnostic apparatus characterized in that the radiation diagnostic apparatus is configured to use a modulation (PFM) circuit to output a pulse train having a repetition frequency corresponding to the analog voltage value as a sampling timing signal. 6. In the radiological diagnostic apparatus according to claim 4, the sampling control means converts the analog voltage signal generated at the movable end of the variable resistor and changes in accordance with the distance between the subject and the radiation source into an A/D converter. The decoder converts the digital data into a digital value, decodes the digital data with a decoder, and uses the decoded signal to select and control a group of frequency division counters that divide the output from the oscillator at different frequency division ratios. A radiation diagnostic apparatus characterized in that it is configured to output a logical sum of signals as a sampling timing control signal. 7. A radiation source that generates a radiation beam forming a fan shape on one plane, a radiation detector comprising a large number of detector cells arranged so as to detect the radiation beam at predetermined angular intervals, and a driving means for relatively moving the subject and the radiation source-the radiation detector system in a direction perpendicular to a plane containing the subject; and a distance detecting means for detecting a distance between the subject and the radiation source. , a data collection means for sampling the output signal of the radiation detector and converting it into scheduled information; a sampling control means for controlling the sampling timing of the data collection means according to the output signal of the distance detection means; A radiological diagnostic apparatus comprising a storage calculation control means for accumulating information collected by the data collection means and forming the subject transmission image, and a display means for displaying the transmission image formed by the storage calculation control means, radiation source, radiation detector,
What is claimed is: 1. A radiological diagnostic apparatus comprising a CT scanner having a data collection means, a storage calculation control means, and a display means common to the constituent elements of a CT scanner, and further comprising a distance detection means and a sampling control means.
Priority Applications (4)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP55147918A JPS5772629A (en) | 1980-10-22 | 1980-10-22 | Radioactive ray diagnostic apparatus |
| US06/311,965 US4464777A (en) | 1980-10-22 | 1981-10-16 | Radiography apparatus |
| EP81304875A EP0050510B1 (en) | 1980-10-22 | 1981-10-19 | Radiography apparatus |
| DE8181304875T DE3163232D1 (en) | 1980-10-22 | 1981-10-19 | Radiography apparatus |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP55147918A JPS5772629A (en) | 1980-10-22 | 1980-10-22 | Radioactive ray diagnostic apparatus |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5772629A JPS5772629A (en) | 1982-05-07 |
| JPS6343099B2 true JPS6343099B2 (en) | 1988-08-29 |
Family
ID=15441034
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP55147918A Granted JPS5772629A (en) | 1980-10-22 | 1980-10-22 | Radioactive ray diagnostic apparatus |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5772629A (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH02238290A (en) * | 1989-03-10 | 1990-09-20 | Godo Seitetsu Kk | Arc electric furnace |
| JP2009145266A (en) * | 2007-12-17 | 2009-07-02 | Aloka Co Ltd | X-ray measuring device |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP5697970B2 (en) * | 2010-12-22 | 2015-04-08 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | X-ray CT system |
-
1980
- 1980-10-22 JP JP55147918A patent/JPS5772629A/en active Granted
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH02238290A (en) * | 1989-03-10 | 1990-09-20 | Godo Seitetsu Kk | Arc electric furnace |
| JP2009145266A (en) * | 2007-12-17 | 2009-07-02 | Aloka Co Ltd | X-ray measuring device |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5772629A (en) | 1982-05-07 |
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