JP2006006805A - X-ray ct apparatus - Google Patents

X-ray ct apparatus Download PDF

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JP2006006805A
JP2006006805A JP2004191506A JP2004191506A JP2006006805A JP 2006006805 A JP2006006805 A JP 2006006805A JP 2004191506 A JP2004191506 A JP 2004191506A JP 2004191506 A JP2004191506 A JP 2004191506A JP 2006006805 A JP2006006805 A JP 2006006805A
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ray
control unit
group
converter
control
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JP2006006805A5 (en
JP4508746B2 (en
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Takuya Kadoshima
拓也 門嶋
Mitsuaki Ogata
光明 尾形
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Hitachi Healthcare Manufacturing Ltd
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Hitachi Medical Corp
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Abstract

<P>PROBLEM TO BE SOLVED: To provide an X-ray CT (computed tomography) apparatus capable of preventing noises such as high-frequency noise, or the like, from being introduced into output data from an X-ray detector and an AD converter equipped on a gantry side. <P>SOLUTION: The X-ray CT apparatus includes an X-ray detector 4 and a controlling part 5, which are connected by an optical cable 7. The X-ray detector 4 comprises an X-ray detector body 40, a multiplexer 41, preamplifiers 42, and AD converters 43. A connector 44, which is provided on output sides of the AD converters 43, is connected with the optical cable 7. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

本発明は、ガントリ側に搭載されているＸ線検出器及びＡＤ変換器の出力データへの高周波等ノイズの混入を防止するＸ線ＣＴ装置に関する。   The present invention relates to an X-ray CT apparatus for preventing mixing of noise such as high-frequency into output data of an X-ray detector and an AD converter mounted on a gantry side.

Ｘ線ＣＴ装置は、回転するガントリと静止側設置の画像処理装置とで構成される。回転するガントリには、Ｘ線管、それに対向配置されたＸ線検出器及びＸ線検出器の計測信号を取り込むマルチプレクサ、並びに増幅するプリアンプ等が搭載される。ガントリと画像処理装置との間はスリップリング機構を介して接続する。
こうしたスリップリング機構の中継手段として光転送を用いた従来例として、特許文献１がある。 The X-ray CT apparatus includes a rotating gantry and a stationary image processing apparatus. The rotating gantry is equipped with an X-ray tube, an X-ray detector disposed opposite to the X-ray tube, a multiplexer for taking in measurement signals of the X-ray detector, an amplifying preamplifier, and the like. The gantry and the image processing apparatus are connected via a slip ring mechanism.
As a conventional example using optical transfer as a relay means of such a slip ring mechanism, there is Patent Document 1.

特開平１１−３１８８８０号JP-A-11-318880

上記特許文献１は、スリップリング機構の中の送信側機構と受信側機構との伝送路上で、同時に発生するコモンモードノイズの除去を目的としたものである。
然るに、スリップリング機構以外でも高周波ノイズの問題がある。それは、Ｘ線検出器及びＡＤ変換器を含むＸ線検出器側と、それらの出力データを取り込む制御部と、の間で生ずる例である。以下、説明する。 The above-mentioned Patent Document 1 aims to remove common mode noise that occurs simultaneously on the transmission path between the transmission side mechanism and the reception side mechanism in the slip ring mechanism.
However, there is a problem of high frequency noise other than the slip ring mechanism. This is an example that occurs between the X-ray detector side including the X-ray detector and the AD converter, and the control unit that captures the output data thereof. This will be described below.

Ｘ線検出器のチャンネル数の増加、スライス幅の増加、並びに計測ビュー数の増加、に伴い回転するガントリ側では、高密度実装化された半導体回路、電子回路の使用が不可欠である。こうした要求の他にリアルタイムで再構成画像を得る目的や高速で高精細な再構成画像を得る目的からも、半導体回路、電子回路は、高密度の実装化並びに高速処理が要求されている。   On the gantry side that rotates with the increase in the number of channels of the X-ray detector, the increase in slice width, and the increase in the number of measurement views, it is indispensable to use semiconductor circuits and electronic circuits that are mounted with high density. In addition to these requirements, semiconductor circuits and electronic circuits are required to have high-density mounting and high-speed processing for the purpose of obtaining a reconstructed image in real time and for obtaining a high-speed, high-definition reconstructed image.

こうした高密度で高速処理の回路にあっては、高周波ノイズの影響を受けやすい。例えば、Ｘ線ＣＴ装置は高出力のＸ線を発生させるため、５０ｋＷ近くもの電源をＸ線管球に供給しており、Ｘ線高電圧発生装置への電源供給を２００Ｖで行った場合は２００Ａを越える電流が流れ、Ｘ線で１００ｋＶ以上の電圧をＸ線管に供給している。   Such high-density and high-speed processing circuits are susceptible to high-frequency noise. For example, since the X-ray CT apparatus generates high-power X-rays, nearly 50 kW of power is supplied to the X-ray tube, and the power supply to the X-ray high-voltage generator is 200 A when the power is supplied at 200 V. Current exceeding 100 flows, and a voltage of 100 kV or more is supplied to the X-ray tube by X-ray.

一方、Ｘ線管から発生されたＸ線は、被検体を透過してＸ線検出器へ入射するが、このＸ線検出器から取り出すことのできる信号は数μＡ程度である。このとき、Ｘ線高電圧発生装置側へ供給される電力により引き起こされるノイズが、Ｘ線高電圧発生装置から検出器部を制御する制御部に伝播し、制御部と検出器部が導電性のあるケーブルで接続されている場合は、そのノイズがさらに検出器部に混入してしまう。ところが、先に示したように、得られる信号が数μＡと小さいので、この混入したノイズにより、Ｘ線検出器から得られる信号が障害を受け、正しいデータが得られないという問題があった。   On the other hand, X-rays generated from the X-ray tube pass through the subject and enter the X-ray detector, but a signal that can be taken out from the X-ray detector is about several μA. At this time, noise caused by the power supplied to the X-ray high voltage generator propagates from the X-ray high voltage generator to the control unit that controls the detector unit, and the control unit and the detector unit are conductive. When connected with a certain cable, the noise further enters the detector section. However, as described above, since the obtained signal is as small as several μA, there is a problem that the signal obtained from the X-ray detector is disturbed by the mixed noise and correct data cannot be obtained.

本発明は、Ｘ線源と、それに対向配置されて被検体透過Ｘ線を検出するＸ線検出素子群と、Ｘ線検出素子群の検出信号をＡＤ変換するＡＤ変換器群と、Ｘ線検出素子群及びＡＤ変換器群の制御を行うと共にＡＤ変換器群の出力データを取り込む制御部と、制御部からの出力データを取り込み画像処理する画像処理部とを備えると共に、上記Ｘ線源とＸ線検出素子群とＡＤ変換器群と制御部とが回転するガントリに取り付けられており、画像処理部がガントリの外部の静止側に設けられ、制御部と画像処理部とがスリップリングを介して接続しているＸ線ＣＴ装置であって、
ＡＤ変換器群と制御部とのデータ伝送経路を光伝送手段で構成したＸ線ＣＴ装置を開示する。 The present invention relates to an X-ray source, an X-ray detection element group that is disposed opposite to the X-ray detection element group and detects a subject transmission X-ray, an AD converter group that AD-converts a detection signal of the X-ray detection element group, and an X-ray detection A control unit that controls the element group and the AD converter group and captures output data of the AD converter group, and an image processing unit that captures output data from the control unit and performs image processing, and the X-ray source and X The line detection element group, the AD converter group, and the control unit are attached to a rotating gantry, the image processing unit is provided on the stationary side outside the gantry, and the control unit and the image processing unit are connected via a slip ring. A connected X-ray CT apparatus,
An X-ray CT apparatus in which a data transmission path between an AD converter group and a control unit is configured by optical transmission means is disclosed.

更に本発明は、上記制御部は、Ｘ線検出素子群の出力切替制御及びＡＤ変換器群の変換タイミング制御、光伝送手段へのＡＤ変換器群出力データの分配制御、を行うものとし、光伝送手段は、これらの制御信号の制御部からＸ線検出素子群及びＡＤ変換器群への送出用にも使用するものとしたＸ線ＣＴ装置を開示する。   Further, according to the present invention, the control unit performs output switching control of the X-ray detection element group, conversion timing control of the AD converter group, and distribution control of the AD converter group output data to the optical transmission means. The transmission means discloses an X-ray CT apparatus that is also used for sending these control signals from the control unit to the X-ray detection element group and the AD converter group.

本発明によれば、ガントリ内のＡＤ変換器群とそれの制御及びその出力データを取り込む制御部との間を、光伝送手段で接続したが故に、この光伝送手段でデータを伝送することができ、外部からの電磁ノイズの混入を防止できた。   According to the present invention, since the AD converter group in the gantry and its control and the control unit for fetching the output data are connected by the optical transmission means, data can be transmitted by this optical transmission means. It was possible to prevent external electromagnetic noise from entering.

図１は本発明のＸ線ＣＴ装置の構成例図を示す。Ｘ線ＣＴ装置は、ガントリ１００と、その外部の静止側に設けた画像処理装置２００と、より成る。ガントリ１００は、開口部１と、その開口部１の外側の回転フレーム２と、このフレーム２に取り付けたＸ線管３と、Ｘ線管３に対向配置したＸ線検出器４とを備えると共に、更に制御部５と、Ｘ線高電圧発生装置６とを搭載する。制御部５はＸ線検出器４の制御及びＸ線高電圧発生装置６の指令等の制御を行う。   FIG. 1 shows a configuration example of an X-ray CT apparatus of the present invention. The X-ray CT apparatus includes a gantry 100 and an image processing apparatus 200 provided on the stationary side outside the gantry 100. The gantry 100 includes an opening 1, a rotating frame 2 outside the opening 1, an X-ray tube 3 attached to the frame 2, and an X-ray detector 4 disposed to face the X-ray tube 3. Further, a control unit 5 and an X-ray high voltage generator 6 are mounted. The control unit 5 controls the X-ray detector 4 and the command of the X-ray high voltage generator 6.

ガントリ１００の開口部１には、被検体を搭載した寝台（図示せず）が出入りする。
本実施例は、Ｘ線検出器４と制御部５との間を光伝送手段の有力な例としての光ケーブル７で接続した点が主たる特徴である。光ケーブル７は、検出器４側に設けた光コネクタ４、制御部５側に設けた光コネクタ５０を介して接続してある。光ケーブル７は、１本〜６本程度であり、データ等の伝送は、時分割で行う。例えば、１本の光ケーブルの場合には、全データが時分割伝送となる。例えば６本の光ケーブルの場合は、データを６群に分割し、各群が１本の光ケーブルを時分割で伝送する。 A bed (not shown) on which the subject is mounted enters and exits the opening 1 of the gantry 100.
The main feature of the present embodiment is that the X-ray detector 4 and the controller 5 are connected by an optical cable 7 as an effective example of the optical transmission means. The optical cable 7 is connected via an optical connector 4 provided on the detector 4 side and an optical connector 50 provided on the control unit 5 side. The number of optical cables 7 is about 1 to 6, and transmission of data and the like is performed in a time division manner. For example, in the case of one optical cable, all data is time-division transmission. For example, in the case of six optical cables, the data is divided into six groups, and each group transmits one optical cable in a time division manner.

光ケーブル７で伝送すべきデータ等とは、以下のものがある。
（イ）、ＡＤ変換器の出力、即ち計測データ…これはＸ線検出器本体で計測した透過Ｘ線対応のＸ線検出信号のプリアンプ後のＡＤ変換器結果であり、データの総数は、検出器本体のチャンネル数ｍ、スライス数ｎ、ビュー数ｐとすれば、（ｍ）×（ｎ）×（ｐ）となる。例えばｍ＝１０００、ｎ＝４、ｐ＝２０００であれば、データ総数８M個となる。これに、1データ当り１６ビットとすれば、ビット数は８×１６Ｍビットとなる。 The data to be transmitted by the optical cable 7 includes the following.
(B) Output of the AD converter, that is, measurement data: This is the AD converter result after pre-amplification of the X-ray detection signal corresponding to the transmission X-ray measured by the X-ray detector body, and the total number of data is detected Assuming that the number of channels m, the number of slices n, and the number of views p of the main body are (m) × (n) × (p). For example, if m = 1000, n = 4, and p = 2000, the total number of data is 8M. If the number of bits is 16 bits per data, the number of bits is 8 × 16M bits.

（ロ）、制御部５から検出器４への各種制御信号…検出器４は、本来のＸ線検出器本体（Ｘ線検出素子群）の他に図２の如き構成を有する。即ち、Ｘ線検出器４は、Ｘ線検出器本体４０、マルチプレクサ４０、プリアンプ群４２、ＡＤ変換器群４３、光コネクタ４４を持つ。Ｘ線検出器本体４０は、Ｘ線−光変換器群４０１と光−電気変換器群４０２とより成り、両者はチャンネルとスライスとで区分されたマトリックス構成であり、例えばフォトダイオードや半導体素子を使ったものがある。マルチプレクサ４１は、Ｘ線検出器本体４０の多数の出力を走査して選択出力する回路、プリアンプ群４２は、マルチプレクサ４０の各出力を増幅する素子群、ＡＤ変換器群４３は、プリアンプ群４２の各出力をＡＤ変換する素子群、光コネクタ４４は、ＡＤ変換器群４３の出力を時分割して電気−光に変換するデバイスである。多数ケーブル７の例であれば、時分割に際してデータ群を分類化し更に時分割化し、各ケーブルへの配分を行う機能を有する。
光コネクタ４４の内部に時分割、データ群分類の機能を持たせたが、光コネクタ４４の前段にその機能を達成する処理回路を設ける例もある。
こうした検出器４は、外部からの制御を必要とし、それを実現したのが制御部５である。制御部５が出力する制御信号を光ケーブル７で制御部５からＸ線検出器４へ送ることとしたのである。また制御信号の応答信号が制御部５に送られることもあり、これも光ケーブル７で送ることとした。かかる制御信号及び応答信号を送るために、光コネクタ４４と別個の光コネクタを設けてもよく、光コネクタ４４で兼用させてもよい。 (B) Various control signals from the control unit 5 to the detector 4... The detector 4 has a configuration as shown in FIG. 2 in addition to the original X-ray detector body (X-ray detection element group). That is, the X-ray detector 4 has an X-ray detector main body 40, a multiplexer 40, a preamplifier group 42, an AD converter group 43, and an optical connector 44. The X-ray detector body 40 includes an X-ray-to-optical converter group 401 and an optical-to-electrical converter group 402, both of which have a matrix configuration divided into channels and slices. There is what I used. The multiplexer 41 is a circuit that scans and selectively outputs a number of outputs from the X-ray detector main body 40, the preamplifier group 42 is an element group that amplifies each output of the multiplexer 40, and the AD converter group 43 is an element of the preamplifier group 42. An element group for AD-converting each output, the optical connector 44 is a device that time-divides the output of the AD converter group 43 and converts it into electrical-light. In the case of the multiple cables 7, the data group is classified in time division, further divided into time divisions, and distributed to each cable.
Although the optical connector 44 is provided with the functions of time division and data group classification, there is an example in which a processing circuit for achieving the functions is provided in the front stage of the optical connector 44.
Such a detector 4 requires external control, and the control unit 5 realizes it. The control signal output from the control unit 5 is sent from the control unit 5 to the X-ray detector 4 through the optical cable 7. Further, a response signal of the control signal may be sent to the control unit 5, and this is also sent by the optical cable 7. In order to send such a control signal and a response signal, an optical connector separate from the optical connector 44 may be provided, or the optical connector 44 may also be used.

制御信号には以下のものがある。
・Ｘ線検出器本体４０の感度調整信号。
・マルチプレクサ４１の走査信号。
・プリアンプ群４２のゲイン調整信号。
・ＡＤ変換器群４２のＡＤ変換タイミング信号。
・光伝送に際しての時分割化データ群分類の制御信号。
・その他 The control signals include the following.
A sensitivity adjustment signal of the X-ray detector main body 40.
A scanning signal of the multiplexer 41.
A gain adjustment signal for the preamplifier group 42.
AD conversion timing signal of the AD converter group 42
-Control signal for time-division data group classification for optical transmission.
・ Other

（ハ）、制御部５からの高電圧発生装置６への制御信号…制御部５は、高電圧発生装置６への制御を行うための制御信号を作り送出している。高電圧発生装置６は、交流電力を直流に変換するコンバータと、コンバータ直流電力を交流に変換するインバータと、インバータ交流出力を整流して直流に変換すると共に平滑化する整流回路、この出力を昇圧する昇圧回路等から成り、昇圧回路出力がＸ線管の駆動を行ってＸ線発生制御を行う。かかる高電圧発生装置６は、計測条件に応じた管電流、管電圧となるように昇圧回路出力の制御を全体の経路を通じて行っているが、この管電流指令、管電圧指令、高電圧発生装置６の起動指令、終了指令などの発生は、制御部５が受け持つ。かかる各指令も制御信号の一種であり、これらは、従来通り電気信号として制御部５が発生し、高電圧発生装置６へ送ることとしている。   (C) Control signal from the control unit 5 to the high voltage generator 6... The control unit 5 creates and sends a control signal for controlling the high voltage generator 6. The high voltage generator 6 includes a converter that converts alternating current power into direct current, an inverter that converts the converter direct current power into alternating current, a rectifier circuit that rectifies and converts the inverter alternating current output to direct current, and smoothes the output. The booster circuit output controls the X-ray generation by driving the X-ray tube. The high voltage generator 6 controls the booster circuit output through the entire path so as to obtain a tube current and a tube voltage corresponding to the measurement conditions. This tube current command, tube voltage command, and high voltage generator The control unit 5 takes charge of the generation of the start command, the end command, and the like. Each of these commands is also a kind of control signal, which is generated by the control unit 5 as an electric signal as usual and sent to the high voltage generator 6.

光コネクタ４４、５０は、電気−光変換器、光−電気変換器を兼用したものである。当然のことながら、図２でＡＤ変換器群４３の出力データを伝送するには、電気−光変換器が光コネクタ４４に必要であり、これに対応して制御部５の光コネクタ５０では光−電気変換器が必要である。更に、制御部５から制御信号を光ケーブル（図２の光ケーブルと別か否かは不問）を介してＸ線検出器４側に送るには、制御部５側の光コネクタが電気−光変換器、検出器４側の光コネクタが光−電気変換器を持つことが必要である。   The optical connectors 44 and 50 serve both as an electric-optical converter and an optical-electrical converter. As a matter of course, in order to transmit the output data of the AD converter group 43 in FIG. 2, an electrical-optical converter is required for the optical connector 44, and the optical connector 50 of the control unit 5 correspondingly transmits the optical data. -An electrical converter is required. Further, in order to send a control signal from the control unit 5 to the X-ray detector 4 side via an optical cable (regardless of whether it is different from the optical cable in FIG. 2), the optical connector on the control unit 5 side is an electro-optical converter. It is necessary that the optical connector on the detector 4 side has an optical-electrical converter.

図３は、制御部５の構成例図である。制御部５は、データ受信・出力回路５１、Ｘ線高電圧発生装置６への指令発生部５２、Ｘ線検出器４への指令・制御信号生成間・発生部５３を有する。回路５１は、光ケーブル７を介して得たＸ線検出器４の出力データを取り込み、これを画像処理装置２００へ送る。指令発生部５２は、操作卓から入力された計測条件をもとに、Ｘ線管３の管電圧・管電流指令を生成し、これをＸ線高電圧発生装置６に送る。生成・発生装置５３はＸ線検出器４の指令・制御信号を生成し、Ｘ線検出器４に送る。この経路は、光ケーブル７Ａを使用する。係る指令制御信号の内容は、前述した通りである。   FIG. 3 is a configuration example diagram of the control unit 5. The control unit 5 includes a data reception / output circuit 51, a command generation unit 52 for the X-ray high voltage generator 6, and a command / control signal generation / generation unit 53 for the X-ray detector 4. The circuit 51 takes in the output data of the X-ray detector 4 obtained via the optical cable 7 and sends it to the image processing apparatus 200. The command generator 52 generates a tube voltage / tube current command for the X-ray tube 3 based on the measurement conditions input from the console, and sends this to the X-ray high voltage generator 6. The generation / generation device 53 generates a command / control signal for the X-ray detector 4 and sends it to the X-ray detector 4. This route uses the optical cable 7A. The contents of the command control signal are as described above.

本実施例での効果を、図４、図５で対比して説明する。
図４は、光ケーブルを用いない事例であり、検出器４と制御部５との間は、電気ケーブル１１で接続し、制御部５とＸ線高電圧発生装置６との間も電気ケーブル１０で接続した。この結果、高電圧発生装置６からの電磁ノイズ１２がそのケーブル１０、１１を介して検出器４に混入することがあった。また無線で空間伝播くして電気ケーブル１１に或いは検出器４に直接ノイズとして入ることもあった。 The effects of this embodiment will be described in comparison with FIGS.
FIG. 4 shows an example in which an optical cable is not used. The detector 4 and the control unit 5 are connected by an electric cable 11, and the control unit 5 and the X-ray high voltage generator 6 are also connected by the electric cable 10. Connected. As a result, electromagnetic noise 12 from the high voltage generator 6 may be mixed into the detector 4 via the cables 10 and 11. In addition, the noise may be directly transmitted to the electric cable 11 or the detector 4 as noise due to space propagation by radio.

図５では、検出器４と制御部５との間を、光ケーブル７で接続したが故に、ノイズ１２は遮断され、データ伝送への悪影響はない。
特に、Ｘ線高電圧発生装置６には５０ｋＷを超える電力が供給され、その供給電力の発生するノイズは、空間を電磁波として伝播すると共に、導電体であるケーブルを通して、接続されているすべての部分に伝播される。空中を伝わる電磁波については、ノイズの影響を無くしたい部分に、導電体によるシールドを付加することにより、伝播を防止することができるが、ケーブル等の導電体による伝播は、導体を無くさない限り減衰はするが伝播を防ぐことはできない。本実施の形態では、光ケーブルによる非導電体を介して信号を伝送することにより、この問題を解決する。光ケーブルでＸ線検出器部と制御部を接続すると、ノイズは導電体が無いので伝播は無くなり、シールドの効果と合わせてノイズの影響を低減することができる。これにより、数μＡ以下の微小な信号でもノイズの影響を受けることなく性格に測定できるようになる。 In FIG. 5, since the detector 4 and the control unit 5 are connected by the optical cable 7, the noise 12 is blocked and there is no adverse effect on data transmission.
In particular, the X-ray high voltage generator 6 is supplied with electric power exceeding 50 kW, and noise generated by the supplied electric power propagates as electromagnetic waves in the space and is connected to all connected parts through cables that are conductors. Propagated to. Propagation of electromagnetic waves traveling in the air can be prevented by adding a shield with a conductor to the part where it is desired to eliminate the influence of noise, but propagation by a conductor such as a cable is attenuated unless the conductor is lost. Although it does not prevent propagation. In the present embodiment, this problem is solved by transmitting a signal via a non-conductor using an optical cable. When the X-ray detector unit and the control unit are connected by an optical cable, noise does not propagate because there is no conductor, and the influence of noise can be reduced together with the shielding effect. As a result, even a minute signal of several μA or less can be accurately measured without being affected by noise.

尚、光ケーブルの代わりにフォトカプラーにて電気的に接続を切り離すと共に光を空間伝播させるやり方もある。但し、フォトカプラーは光コネクタに比較して転送スピードが遅く、多スライス化によるデータ量の増大により、必要とされるフォトカプラーの数が多くなり、回路規模が大きくなるデメリットがある。
例えば、シングルスライス機では、
（１０００チャンネル）×（２０００ビュー）×（２０ビット）＝４０ＭＨｚ
でよかった転送レートが３２スライス機では、
（１０００チャンネル）×（３２スライス）×（２０００ビュー）×（２０ビット）＝１．２８ＧＨｚ
となり、フォトカプラーの転送速度は高速なものでも５０ＭＨｚ程度なので、１．２８ＧＨｚのデータを転送するには３０個近いフォトカプラーが必要となり、回路の実装上の制約となる。一方、光によるデータ転送は、２ＧＨｚ程度であれば１本のラインで転送でき、実装も容易となる。こうした欠点もあるが、Ｘ線検出器４と制御部５との距離が短く実装した場合には、フォトカプラーの使用の実益がある。 In addition, there is a method in which light is spatially propagated while electrically disconnecting with a photo coupler instead of an optical cable. However, the photocoupler has a disadvantage that the transfer speed is slower than that of the optical connector, and the number of photocouplers required is increased due to the increase in the amount of data due to the multi-slicing, and the circuit scale is increased.
For example, in a single slice machine,
(1000 channels) x (2000 views) x (20 bits) = 40 MHz
If the transfer rate was good with a 32-slice machine,
(1000 channels) × (32 slices) × (2000 views) × (20 bits) = 1.28 GHz
Therefore, even if the transfer speed of the photocoupler is high, it is about 50 MHz. Therefore, in order to transfer 1.28 GHz data, nearly 30 photocouplers are required, which is a limitation in circuit mounting. On the other hand, if the data transfer by light is about 2 GHz, it can be transferred by one line, and mounting becomes easy. Although there is such a drawback, when the distance between the X-ray detector 4 and the control unit 5 is short, there is an actual advantage of using a photocoupler.

本発明のＸ線ＣＴ装置の実施態様を示す図である。It is a figure which shows the embodiment of the X-ray CT apparatus of this invention. 本発明のＸ線検出器４の構成及び制御部５との光ケーブル接続例を示す図である。It is a figure which shows the example of an optical cable connection with the structure of the X-ray detector 4, and the control part 5 of this invention. 制御部５の具体例図である。FIG. 4 is a specific example diagram of a control unit 5. 従来のノイズによる影響を示す図である。It is a figure which shows the influence by the conventional noise. 本発明によるノイズ除去例を示す図である。It is a figure which shows the noise removal example by this invention.

符号の説明Explanation of symbols

１ 開口部
２ 回転フレーム
３ Ｘ線管
４ Ｘ線検出器
５ 制御部
６ Ｘ線高電圧発生装置
７ 光ケーブル
１００ ガントリ
２００ 画像処理装置
DESCRIPTION OF SYMBOLS 1 Opening part 2 Rotating frame 3 X-ray tube 4 X-ray detector 5 Control part 6 X-ray high voltage generator 7 Optical cable 100 Gantry 200 Image processing apparatus

Claims (2)

Ｘ線源と、それに対向配置されて被検体透過Ｘ線を検出するＸ線検出素子群と、Ｘ線検出素子群の検出信号をＡＤ変換するＡＤ変換器群と、Ｘ線検出器群及びＡＤ変換器群の制御を行うと共にＡＤ変換器群の出力データを取り込む制御部と、制御部からの出力データを取り込み画像処理する画像処理部とを備えると共に、上記Ｘ線源とＸ線検出素子群とＡＤ変換器群と制御部とが回転するガントリに取り付けられており、画像処理部がガントリの外部の静止側に設けられ、制御部と画像処理部とがスリップリングを介して接続しているＸ線ＣＴ装置であって、
ＡＤ変換器群と制御部とのデータ伝送経路を光伝送手段で構成したＸ線ＣＴ装置。 An X-ray source, an X-ray detection element group that is disposed opposite to the X-ray detection element and detects an object-transmitted X-ray, an AD converter group that AD converts a detection signal of the X-ray detection element group, an X-ray detector group, and an AD The X-ray source and the X-ray detection element group include a control unit that controls the converter group and captures output data of the AD converter group, and an image processing unit that captures output data from the control unit and performs image processing. The AD converter group and the control unit are attached to a rotating gantry, the image processing unit is provided on the stationary side outside the gantry, and the control unit and the image processing unit are connected via a slip ring. An X-ray CT apparatus,
An X-ray CT apparatus in which a data transmission path between an AD converter group and a control unit is configured by optical transmission means. 上記制御部は、Ｘ線検出素子群の出力切替制御及びＡＤ変換器群の変換タイミング制御、光伝送手段へのＡＤ変換器群出力データの分配制御、を行うものとし、光伝送手段は、これらの制御信号の制御部からＸ線検出素子群及びＡＤ変換器群への送出用にも使用するものとした請求項１のＸ線ＣＴ装置。
The control section performs output switching control of the X-ray detection element group, conversion timing control of the AD converter group, distribution control of AD converter group output data to the optical transmission means, and the optical transmission means 2. The X-ray CT apparatus according to claim 1, wherein the X-ray CT apparatus is also used for sending the control signal from the control unit to the X-ray detection element group and the AD converter group.
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CN102970934A (en) * 2011-07-06 2013-03-13 株式会社东芝 X-ray CT apparatus and data transmission method in X-ray CT apparatuses
US9149240B2 (en) 2011-07-06 2015-10-06 Kabushiki Kaisha Toshiba X-ray CT apparatus and data transmission method of X-ray CT apparatus

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