JPH0838466A - Computer tomography apparatus - Google Patents
Computer tomography apparatusInfo
- Publication number
- JPH0838466A JPH0838466A JP7177475A JP17747595A JPH0838466A JP H0838466 A JPH0838466 A JP H0838466A JP 7177475 A JP7177475 A JP 7177475A JP 17747595 A JP17747595 A JP 17747595A JP H0838466 A JPH0838466 A JP H0838466A
- Authority
- JP
- Japan
- Prior art keywords
- cathode
- ring
- anode
- cathodes
- detector
- 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.)
- Withdrawn
Links
- 238000002591 computed tomography Methods 0.000 title claims description 15
- 230000001960 triggered effect Effects 0.000 claims abstract description 4
- 238000010894 electron beam technology Methods 0.000 claims abstract description 3
- 238000010438 heat treatment Methods 0.000 abstract description 7
- 238000001514 detection method Methods 0.000 abstract description 2
- 238000005259 measurement Methods 0.000 description 5
- 239000011521 glass Substances 0.000 description 3
- 238000010586 diagram Methods 0.000 description 2
- 238000007689 inspection Methods 0.000 description 2
- 230000001678 irradiating effect Effects 0.000 description 2
- 238000003384 imaging method Methods 0.000 description 1
- 230000001360 synchronised effect Effects 0.000 description 1
- 238000004804 winding Methods 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/032—Transmission computed tomography [CT]
- A61B6/035—Mechanical aspects of CT
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/032—Transmission computed tomography [CT]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/40—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4007—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units
- A61B6/4014—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units arranged in multiple source-detector units
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/40—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4021—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis involving movement of the focal spot
- A61B6/4028—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis involving movement of the focal spot resulting in acquisition of views from substantially different positions, e.g. EBCT
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4275—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis using a detector unit almost surrounding the patient, e.g. more than 180°
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/24—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/26—Measuring, controlling or protecting
- H05G1/30—Controlling
- H05G1/52—Target size or shape; Direction of electron beam, e.g. in tubes with one anode and more than one cathode
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、環状陽極、該環状
陽極により囲繞されていて、当該環状陽極に対して同軸
線状に配置された検出器環及び同様に前記陽極に対して
同軸線状に配置された陰極環を有しており、該陰極環
は、一連の陰極を有しており、該陰極の電子ビームは、
前記陽極の方に向かってステップ状にトリガされるよう
にしたコンピュータ断層撮影（トモグラフ）装置（請求
範囲１記載の上位概念による）に関する。FIELD OF THE INVENTION The present invention relates to an annular anode, a detector ring which is surrounded by the annular anode and is arranged coaxially with respect to the annular anode, and also coaxially with respect to the anode. Having a cathode ring disposed on, the cathode ring having a series of cathodes, the electron beam of the cathode being
It relates to a computed tomography device (according to the preamble of claim 1) adapted to be triggered in steps towards the anode.
【０００２】[0002]
【従来の技術】この形式のコンピュータ断層撮影装置の
場合、扇形のＸ線ビーム束により種々の角度で検査対象
を照射しつつ走査している間、陽極も検出器環及び陰極
環も固定されている。従って、３６０°の全角度に亘っ
て、検査対象を非常に速く照射することができる。従っ
て、画像撮影時間は、極めて短くすることができる。2. Description of the Related Art In the case of a computer tomography apparatus of this type, both the anode and the detector ring and the cathode ring are fixed during scanning while irradiating an inspection object at various angles with a fan-shaped X-ray beam bundle. There is. Therefore, the inspection object can be illuminated very quickly over the entire 360 ° angle. Therefore, the image capturing time can be made extremely short.
【０００３】しかし、陰極環の各個別陰極装置は、夫々
同様の幅を有しているので、陰極環内に装着することが
できる各陰極装置の個数、従って、照射し得る焦点位置
の個数には限りがある。更に、各陰極の加熱用の電力消
費量は、かなり高い。However, since each individual cathode device of the cathode ring has the same width, the number of each cathode device that can be mounted in the cathode ring, and thus the number of focal positions that can be irradiated, is limited. Is limited. Moreover, the power consumption for heating each cathode is rather high.
【０００４】[0004]
【発明が解決しようとする課題】本発明の課題は、冒頭
に記載した形式のコンピュータ断層撮影装置（請求項１
の上位概念による）を、各陰極の加熱用の電力消費量を
僅小にしたまま、各焦点位置の個数を増大して、そうす
ることによって画質を向上することができるように構成
することにある。SUMMARY OF THE INVENTION An object of the present invention is to provide a computer tomography apparatus of the type described at the beginning (claim 1).
(By the superordinate concept), while increasing the number of each focus position while keeping the power consumption for heating each cathode small, the image quality can be improved by doing so. is there.
【０００５】[0005]
【課題を解決するための手段】この課題は、本発明によ
ると、冒頭に記載した形式のコンピュータ断層撮影装置
において、一方では陰極と他方では陽極並びに検出器環
との間の相対運動用の手段が設けられているようにして
解決される。This object is achieved according to the invention by means of a computer tomography apparatus of the type described at the outset for relative movement between the cathode on the one hand and the anode and the detector ring on the other hand. Will be solved.
【０００６】[0006]
【発明の実施の形態】図１は、本発明の技術思想の説明
に供するコンピュータ断層撮影装置の一実施例の断面略
図及びブロック接続図を示し、図１ａは、図１のコンピ
ュータ断層撮影装置の一部分を示し、図２は、図１の一
点鎖線ＩＩ−ＩＩでコンピュータ断層撮影装置を切断し
て矢印方向で見た図を示す。1 shows a schematic cross-sectional view and a block connection diagram of an embodiment of a computer tomography apparatus for explaining the technical idea of the present invention, and FIG. 1a shows a computer tomography apparatus of FIG. FIG. 2 shows a part of the computer tomography apparatus taken along the alternate long and short dash line II-II in FIG.
【０００７】図１，１ａ，２に示したコンピュータ断層
撮影装置は、ケーシング１を有しており、ケーシング１
は、水平軸線３を中心にして回動し得るように２つの支
承部２に支承されている。軸線３を中心にしてケーシン
グ１を回動することによって、被検撮影対象の所望の横
断層の位置を選定することができる。ケーシング１内に
は、Ｘ線源４が設けられており、Ｘ線源４は、真空にさ
れたガラス環５を有しており、ガラス環５内には、同様
に、環として構成された陽極６が設けられている。陽極
６には、多数の陰極７，８，９，１０等が配属して設け
られている。各陰極７等は、切換装置１１に接続されて
おり、切換装置１１は、高電圧整流器１２の負極（高電
圧変圧器１３によって給電される）をステップ状に各陰
極７等に接続する。高周波電圧整流器１２の正極は、陽
極６と接続されている。高電圧変圧器１３の一次巻線
は、主スイッチ１４を介して電源に接続することができ
る。The computer tomography apparatus shown in FIGS. 1, 1a and 2 has a casing 1.
Are supported on two bearings 2 so that they can rotate about a horizontal axis 3. By rotating the casing 1 around the axis 3, it is possible to select the desired position of the transverse layer of the object to be imaged. An X-ray source 4 is provided in the casing 1, and the X-ray source 4 has a vacuumed glass ring 5, and the glass ring 5 is similarly configured as a ring. An anode 6 is provided. The cathode 6 is provided with a large number of cathodes 7, 8, 9, 10 and the like assigned thereto. Each cathode 7 etc. is connected to the switching device 11, and the switching device 11 connects the negative electrode of the high voltage rectifier 12 (powered by the high voltage transformer 13) to each cathode 7 etc. stepwise. The positive electrode of the high frequency voltage rectifier 12 is connected to the positive electrode 6. The primary winding of the high voltage transformer 13 can be connected to the power supply via the main switch 14.
【０００８】Ｘ線源４は、同様に円環として構成された
ビーム受信器１５を同心的に囲繞しており、ビーム受信
器１５は、一連の各個別検出器から構成されており、各
個別検出器の個数は、所望の測定値の個数に依存する。
扇状Ｘ線ビーム束１６ａ，ｂ，ｃの焦点調整のために、
絞り装置２８が設けられている。The X-ray source 4 concentrically surrounds a beam receiver 15, which is likewise configured as an annulus, the beam receiver 15 being composed of a series of individual detectors, each individual detector. The number of detectors depends on the number of desired measurements.
In order to adjust the focus of the fan-shaped X-ray beam bundles 16a, 16b, 16c,
A diaphragm device 28 is provided.
【０００９】図１の実施例の場合、相互に変位された３
つのＸ線ビーム束１６ａ，ｂ，ｃが設けられており、従
って、撮影対象の非常に高速な走査が可能である。即
ち、一つのＸ線ビーム束は、約１２０°の角度部分しか
照射しながら移動する必要がない。本発明の範囲では、
散乱ビーム補正に応じて、Ｘ線ビーム束を２つ又は一つ
しか使用しないようにすることもできる。この場合、Ｘ
線ビーム束は、１８０°乃至３６０°の角度部分を照射
しながら移動しなければならない。その場合でも、焦点
を電子的に連続切換するために、非常に高速な走査を行
なうことができるようになる。In the case of the embodiment of FIG.
Two X-ray beam bundles 16a, 16b, 16c are provided so that a very fast scanning of the object to be imaged is possible. That is, one X-ray beam bundle needs to move while irradiating only an angular portion of about 120 °. Within the scope of the invention,
Depending on the scattered beam correction, it is also possible to use only two or one X-ray beam bundle. In this case, X
The line beam bundle must move while illuminating the 180 ° to 360 ° angular portion. Even in that case, a very high-speed scanning can be performed because the focal point is continuously switched electronically.
【００１０】切換装置１１の構成は、複数（実施例で
は、３つ）のＸ線ビーム束１６ａ，ｂ，ｃを同時に種々
の方向から患者に透過照射して、相互に同じステップで
同期しつつ移動するようにされている。その際、Ｘ線ビ
ーム束１６ａ，ｂ，ｃの各中心ビームは、１２０°ずつ
相互にずらされている。The configuration of the switching device 11 is such that a plurality of (three in the embodiment) X-ray beam bundles 16a, 16b, 16c are simultaneously transmitted through the patient from various directions and synchronized with each other at the same step. It is supposed to move. At this time, the central beams of the X-ray beam bundles 16a, 16b, 16c are displaced from each other by 120 °.
【００１１】ビーム受信器１５は、環状のスリット絞り
部３７の側方に設けられており、スリット絞り部は、層
平面に対して垂直方向にＸ線ビーム束１６ａ，ｂ，ｃを
制限し、撮影対象の方に向けられたＸ線ビームの遮蔽の
ために突出部３８，３９を有している。The beam receiver 15 is provided on the side of the annular slit diaphragm 37, which restricts the X-ray beam bundles 16a, 16b, 16c in the direction perpendicular to the layer plane. The projections 38 and 39 are provided to shield the X-ray beam directed toward the object to be imaged.
【００１２】ケーシング１は、中心開口部１７を有して
おり、この開口部の中には、患者が載置された寝台が挿
入配置される。The casing 1 has a central opening 17, into which a bed on which a patient is placed is inserted.
【００１３】ビーム受信器１５は、測定値変換器２０に
接続されており、測定値変換器は、各測定値から患者の
Ｘ線透過横断層の画像が算出されて、その再生は映像装
置２１で行なわれる。The beam receiver 15 is connected to a measurement value converter 20, which calculates an image of the patient's X-ray transmissive transverse layer from each measurement value and reproduces it by a video device 21. Done in.
【００１４】Ｘ線ビーム束１６ａ，ｂ，ｃ及びビーム受
信器１５の相互の配向は、Ｘ線ビーム束がビーム方向で
見て先ずビーム受信器１５の側方の位置２２の傍を通過
し、Ｘ線ビーム束が患者に透過された場合、Ｘ線ビーム
束が、ビーム受信器１５に照射（当たる）されるように
されている。The mutual orientation of the X-ray beam bundles 16a, b, c and the beam receiver 15 is such that the X-ray beam bundle first passes by a side position 22 lateral to the beam receiver 15 in the beam direction, When the X-ray beam bundle is transmitted to the patient, the X-ray beam bundle is made to irradiate (impact) the beam receiver 15.
【００１５】患者の検査のため、即ち、層画像の撮影の
ため、先ず、切換装置１１のスイッチが接続される。そ
れにより、高電圧が陽極と３つの陰極との間に印加さ
れ、Ｘ線ビーム束１６ａ，ｂ，ｃが、例えば、図１に示
した方向で照射される。測定値変換器２０がビーム受信
器１５の各測定値を処理した後、測定値変換器は、切換
装置１１に、このスイッチを開いて、次のスイッチを閉
じるための信号を送出する。それ故、Ｘ線ビーム束の対
称軸線は、例えば、０．１°だけ時計の針の方向に位置
がずらされている。測定値変換器２０が再びビーム受信
器１５の各測定値を検知した後、測定値変換器は、切換
装置１１に、このスイッチを開いて、次のスイッチを閉
じるための信号を送出する。このようにして、Ｘ線ビー
ム束の対称軸線は、繰返し０．１°だけずらされるよう
になる。Ｘ線ビーム束のステップ状の回動は、夫々のＸ
線ビーム束が所定の角度領域（例えば、１２０°）を照
射するようになる迄繰り返される。それから、画像の撮
影が終了し、算出された横断画像が、映像装置２１で再
生される。For the examination of the patient, that is to say for the acquisition of layer images, the switch of the switching device 11 is first connected. Thereby, a high voltage is applied between the anode and the three cathodes, and the X-ray beam bundles 16a, 16b, 16c are irradiated, for example, in the directions shown in FIG. After the measured value converter 20 has processed each measured value of the beam receiver 15, the measured value converter sends a signal to the switching device 11 for opening this switch and closing the next switch. Therefore, the axis of symmetry of the X-ray beam bundle is displaced in the direction of the clock hands, for example by 0.1 °. After the measured value converter 20 again detects each measured value of the beam receiver 15, the measured value converter sends a signal to the switching device 11 for opening this switch and closing the next switch. In this way, the axis of symmetry of the X-ray beam bundle is repeatedly displaced by 0.1 °. The stepwise rotation of the X-ray beam bundle is
This is repeated until the line beam bundle illuminates a predetermined angular region (eg 120 °). Then, the shooting of the image is completed, and the calculated cross-sectional image is reproduced by the video device 21.
【００１６】図１から分かるように、Ｘ線ビーム束１６
ａ，ｂ，ｃは、扇状であり、層平面において、患者全体
が同時に透過されるような大きさである。Ｘ線ビーム束
の、層平面に対して垂直な拡がりは、層強度にほぼ等し
い。As can be seen from FIG. 1, the X-ray beam bundle 16
Each of a, b, and c is fan-shaped and has a size such that the entire patient is simultaneously transmitted in the layer plane. The spread of the X-ray beam bundle perpendicular to the layer plane is approximately equal to the layer intensity.
【００１７】図３に示されている様に、陰極環４２（こ
れに、ここには図示していない陰極７等が取り付けられ
ている）の外側には、歯４３が設けられており、この歯
には、ウォーム４１が噛み合っており、ウォームは、モ
ータ４０によって回転される。それにより、陰極環４２
を、陽極６並びに検出器環１５に対してモータにより回
転させることができる。As shown in FIG. 3, teeth 43 are provided on the outer side of the cathode ring 42 (to which the cathode 7 and the like not shown are attached). A worm 41 meshes with the teeth, and the worm is rotated by the motor 40. Thereby, the cathode ring 42
Can be rotated by a motor with respect to the anode 6 and the detector ring 15.
【００１８】固定される陰極環の実施例： 周囲 ３．０００ｍｍ 陰極の個数： ３．０００個（間隔１ｍｍ
で） １陰極につき１０Ｗの加熱電力の場合、固定された陰極
環４２では、加熱のためだけで全部で３０ｋＷも必要で
ある。Examples of fixed cathode rings: circumference 3,000 mm Number of cathodes: 3,000 (spacing 1 mm
For a heating power of 10 W per cathode, a fixed cathode ring 42 requires a total of 30 kW just for heating.
【００１９】それに対して、本発明実施例の場合、陰極
の個数は、１０ｍｍ間隔で、均等配置した３００個の陰
極に低減することができ、陰極環４２は、相応数の測定
値を形成するために回転する。加熱電力は、僅か３ｋＷ
でしかない。１００ｍｓの画像撮影時間が実現できるよ
うにするためには、緩慢な回転運動によって、１０ｍｍ
の陰極間隔が１００ｍｓの間照射される必要がある。所
要回転速度は、１００ｍｍ／ｓである。従って、連続的
な回転の場合、陰極環４２は、３０秒の間に一回３６０
°回転すればよい。この際、陰極は、時間パターンに従
って制御され、有利には、簡単に、陰極の幾何学的な連
続シーケンスで制御される。３００回のトリガ状の照射
後、最初の陰極が新たに制御される。しかし、この陰極
は、この間に、僅かに、即ち、１０ｍｓ×１００ｍｍ／
＝１ｍｍだけしか移動していない。On the other hand, in the case of the embodiment of the present invention, the number of cathodes can be reduced to 300 evenly arranged cathodes at intervals of 10 mm, and the cathode ring 42 forms a corresponding number of measured values. To rotate. Heating power is only 3kW
There is nothing. In order to achieve an image capturing time of 100 ms, it is necessary to use a slow rotary motion to achieve 10 mm.
It is necessary to irradiate the cathode for 100 ms. The required rotation speed is 100 mm / s. Therefore, in the case of continuous rotation, the cathode ring 42 is 360 times once in 30 seconds.
Rotate °. Here, the cathodes are controlled according to a time pattern, advantageously simply in a geometrically continuous sequence of cathodes. After 300 triggered irradiations, the first cathode is newly controlled. However, during this period, the cathode slightly changed, namely, 10 ms × 100 mm /
It has moved only = 1 mm.
【００２０】比較的短い撮影時間が実現されなければな
らない場合、陰極環４２は、比較的高速で回転されなけ
ればならない。３００個の陰極の有利な実施例の場合、
３．０００個の焦点位置が５０ｍｓ内で実現でき、その
際、陰極環４２は、１５ｓの間に一回回転する。陰極の
個数は、回転時間に反比例して簡単に変えることができ
る。つまり、陰極の個数を少なくすればする程、陰極環
４２の方は、より高速で回転しなければならないのであ
る。If a relatively short shooting time has to be realized, the cathode ring 42 has to be rotated at a relatively high speed. In the case of the preferred embodiment of 300 cathodes,
3.000 focus positions can be achieved in 50 ms, with the cathode ring 42 rotating once during 15 s. The number of cathodes can be easily changed in inverse proportion to the rotation time. That is, the smaller the number of cathodes, the faster the cathode ring 42 must rotate.
【００２１】[0021]
【発明の効果】本発明のコンピュータ断層撮影装置の場
合、測定データ検出の間、一方では各陰極と他方では陽
極並びに検出器環との相対運動を小さな回転速度で行な
うようにして、各陰極の個数及び陰極毎の加熱電力を低
減することができる。According to the computer tomography apparatus of the present invention, during the detection of the measurement data, the relative movement of each cathode on the one hand and the anode and the detector ring on the other hand is carried out at a small rotational speed so that each cathode is moved. The number and heating power for each cathode can be reduced.
【図１】本発明の技術思想の説明に供するコンピュータ
断層撮影装置の一実施例の断面略図及びブロック接続図
である。FIG. 1 is a schematic sectional view and block connection diagram of an embodiment of a computer tomography apparatus for explaining the technical idea of the present invention.
【図２】図１の一点鎖線ＩＩ−ＩＩでコンピュータ断層
撮影装置を切断して矢印方向で見た図である。FIG. 2 is a view of the computer tomography apparatus taken along the alternate long and short dash line II-II in FIG. 1 and viewed in the direction of the arrow.
【図３】図１及び２のコンピュータ断層撮影装置の相対
運動用手段部を示す図である。FIG. 3 is a view showing means for relative movement of the computer tomography apparatus of FIGS. 1 and 2.
１ ケーシング、 ２ 支承部、 ４ Ｘ線源、 ５
ガラス環、 ６ 環状陽極、 ７，８，９，１０ 陰
極、 １１切換装置、 １５ ビーム受信器、２０ 測
定値変換器、 ２１ 映像装置、 ２８ 絞り装置1 casing, 2 bearings, 4 X-ray source, 5
Glass ring, 6 ring anode, 7, 8, 9, 10 cathode, 11 switching device, 15 beam receiver, 20 measurement value converter, 21 imaging device, 28 diaphragm device
Claims (2)
されていて、当該環状陽極に対して同軸線状に配置され
た検出器環（１５）及び同様に前記陽極（６）に対して
同軸線状に配置された陰極環（４２）を有しており、該
陰極環は、一連の陰極（７，８，９，１０，…）を有し
ており、該陰極の電子ビームは、前記陽極（６）の方に
向かってステップ状にトリガされるようにしたコンピュ
ータ断層撮影装置において、一方では陰極（７，８，
９，１０，…）と他方では検出器環（１５）並びに陽極
（６）との間の相対運動用の手段（４０〜４３）が設け
られていることを特徴とするコンピュータ断層撮影装
置。1. An annular anode (6), a detector ring (15) surrounded by said annular anode and arranged coaxially to said annular anode and also to said anode (6). It has a cathode ring (42) arranged coaxially, the cathode ring has a series of cathodes (7, 8, 9, 10, ...) And the electron beam of the cathode is In a computed tomography apparatus adapted to be triggered stepwise towards the anode (6), on the one hand the cathode (7,8,
, 10) on the one hand and detector means (40 to 43) on the other hand for relative movement between the detector ring (15) and the anode (6).
能である請求項１記載のコンピュータ断層撮影装置。2. The computed tomography apparatus according to claim 1, wherein the cathode ring (42) is rotatable by a motor.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE4424742.7 | 1994-07-13 | ||
| DE19944424742 DE4424742C1 (en) | 1994-07-13 | 1994-07-13 | Computer tomograph |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH0838466A true JPH0838466A (en) | 1996-02-13 |
Family
ID=6523066
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP7177475A Withdrawn JPH0838466A (en) | 1994-07-13 | 1995-07-13 | Computer tomography apparatus |
Country Status (3)
| Country | Link |
|---|---|
| JP (1) | JPH0838466A (en) |
| CN (1) | CN1116305A (en) |
| DE (1) | DE4424742C1 (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2010139361A (en) * | 2008-12-11 | 2010-06-24 | Denso Corp | Traveling plan creating device |
| US9782136B2 (en) | 2014-06-17 | 2017-10-10 | The University Of North Carolina At Chapel Hill | Intraoral tomosynthesis systems, methods, and computer readable media for dental imaging |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7274772B2 (en) * | 2004-05-27 | 2007-09-25 | Cabot Microelectronics Corporation | X-ray source with nonparallel geometry |
| CN103908277B (en) * | 2012-12-31 | 2017-03-08 | 清华大学 | CT Apparatus for () and method therefor |
| CN103908281B (en) * | 2012-12-31 | 2016-12-28 | 清华大学 | CT Apparatus for () and method therefor |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE2650237C2 (en) * | 1976-11-02 | 1985-05-02 | Siemens AG, 1000 Berlin und 8000 München | X-ray diagnostic device for the production of transverse slice images |
| US4239972A (en) * | 1978-04-24 | 1980-12-16 | U.S. Philips Corporation | Device for computed tomography |
| EP0466956A1 (en) * | 1990-07-18 | 1992-01-22 | Siemens Aktiengesellschaft | Tomography apparatus |
-
1994
- 1994-07-13 DE DE19944424742 patent/DE4424742C1/en not_active Expired - Fee Related
-
1995
- 1995-07-12 CN CN 95109978 patent/CN1116305A/en active Pending
- 1995-07-13 JP JP7177475A patent/JPH0838466A/en not_active Withdrawn
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2010139361A (en) * | 2008-12-11 | 2010-06-24 | Denso Corp | Traveling plan creating device |
| US9782136B2 (en) | 2014-06-17 | 2017-10-10 | The University Of North Carolina At Chapel Hill | Intraoral tomosynthesis systems, methods, and computer readable media for dental imaging |
| US9907520B2 (en) | 2014-06-17 | 2018-03-06 | The University Of North Carolina At Chapel Hill | Digital tomosynthesis systems, methods, and computer readable media for intraoral dental tomosynthesis imaging |
Also Published As
| Publication number | Publication date |
|---|---|
| CN1116305A (en) | 1996-02-07 |
| DE4424742C1 (en) | 1995-08-31 |
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