JP2000284058A - X-ray image pickup device - Google Patents
X-ray image pickup deviceInfo
- Publication number
- JP2000284058A JP2000284058A JP11090319A JP9031999A JP2000284058A JP 2000284058 A JP2000284058 A JP 2000284058A JP 11090319 A JP11090319 A JP 11090319A JP 9031999 A JP9031999 A JP 9031999A JP 2000284058 A JP2000284058 A JP 2000284058A
- Authority
- JP
- Japan
- Prior art keywords
- ray
- time
- frame
- charge
- reading
- 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.)
- Granted
Links
- 238000001514 detection method Methods 0.000 claims abstract description 20
- 238000009825 accumulation Methods 0.000 claims abstract description 14
- 238000003384 imaging method Methods 0.000 claims description 18
- 230000001678 irradiating effect Effects 0.000 claims description 3
- 230000015654 memory Effects 0.000 abstract description 7
- 238000000034 method Methods 0.000 abstract description 6
- 230000006870 function Effects 0.000 abstract description 3
- 230000007274 generation of a signal involved in cell-cell signaling Effects 0.000 abstract description 3
- 239000003990 capacitor Substances 0.000 description 8
- 238000006243 chemical reaction Methods 0.000 description 8
- 238000010586 diagram Methods 0.000 description 7
- 239000011159 matrix material Substances 0.000 description 4
- 230000001360 synchronised effect Effects 0.000 description 4
- 230000000087 stabilizing effect Effects 0.000 description 2
- 239000010409 thin film Substances 0.000 description 2
- 229910004613 CdTe Inorganic materials 0.000 description 1
- 229910004611 CdZnTe Inorganic materials 0.000 description 1
- OAICVXFJPJFONN-UHFFFAOYSA-N Phosphorus Chemical compound [P] OAICVXFJPJFONN-UHFFFAOYSA-N 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 239000010408 film Substances 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 239000000758 substrate Substances 0.000 description 1
Landscapes
- Measurement Of Radiation (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、医療分野、工業分
野、原子力分野等の２次元のＸ線画像を撮像するための
装置に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an apparatus for capturing a two-dimensional X-ray image in a medical field, an industrial field, a nuclear field, or the like.
【０００２】[0002]
【従来の技術】一般に、Ｘ線撮像装置は、Ｘ線を電荷信
号に変換して蓄積する２次元状に配列した複数個のＸ線
検出素子、この複数個のＸ線検出素子に蓄積された電荷
信号を時系列で順番に読み出す手段、読み出された１フ
レーム分のデータを２次元状に再構成してＸ線画像を得
る手段等で構成されているが、従来、このＸ線撮像装置
には、Ｘ線照射のタイミングと、電荷蓄積およびフレー
ム読み出しのタイミングとを同期させる機構は設けられ
ていない。また一般的に、即時描画性を重視するため電
荷蓄積時間はＸ線照射時間と同じ値以下に設定されてい
る。2. Description of the Related Art Generally, an X-ray imaging apparatus converts a plurality of X-rays into a charge signal and stores the X-rays in a two-dimensional array. The X-ray imaging apparatus includes a means for sequentially reading out the charge signals in time series, a means for reconstructing the read data for one frame in a two-dimensional manner to obtain an X-ray image. Does not provide a mechanism for synchronizing the timing of X-ray irradiation with the timing of charge accumulation and frame reading. In general, the charge storage time is set to be equal to or less than the X-ray irradiation time in order to emphasize the immediate drawing property.
【０００３】[0003]
【発明が解決しようとする課題】この状態でＸ線照射が
行われた場合、例えば、図４に示すように必ず２フレー
ム以上にまたがってＸ線画像データが読み出されること
になる。ここで、ＴxはＸ線照射時間であり、ｔｒは、
Ｘ線検出器の各検出素子の電荷読み出し時間であり、Ｔ
ｃは検出素子を構成しているコンデンサの電荷蓄積時間
である。When X-ray irradiation is performed in this state, for example, as shown in FIG. 4, X-ray image data is always read over two or more frames. Here, Tx is the X-ray irradiation time, and tr is
This is the charge readout time of each detection element of the X-ray detector.
c is the charge accumulation time of the capacitor constituting the detection element.
【０００４】検出器の第１番目の検出素子から第Ｎ番目
の検出素子までの、フレーム２の電荷読み出し信号がＸ
線照射時間内に存在してしまい、Ｘ線照射時のデータが
フレーム２とフレーム３との間に分散されてしまうの
で、複数個のフレームメモリーを設けて加算処理する等
の手段が必要となる。これはたとえ電荷蓄積時間をＸ線
照射時間よりも長くしたとしても、Ｘ線照射のタイミン
グを電荷蓄積およびフレーム読み出しのタイミングと同
期させなければ、図５に示すように第１番目の画素から
第ｎ番目の画素までのＸ線画像データについては２フレ
ームにまたがってしまう。The charge readout signal of frame 2 from the first detection element to the Nth detection element of the detector is X
Since the data exists during the line irradiation time and the data at the time of X-ray irradiation is dispersed between the frame 2 and the frame 3, a means such as providing a plurality of frame memories and performing an addition process is required. . This is because even if the charge accumulation time is longer than the X-ray irradiation time, unless the X-ray irradiation timing is synchronized with the charge accumulation and frame readout timing, as shown in FIG. The X-ray image data up to the n-th pixel extends over two frames.
【０００５】また逆に、Ｘ線照射のタイミングを電荷蓄
積およびフレーム読み出しのタイミングと同期させたと
しても、電荷蓄積時間をＸ線照射時間と１フレーム分の
電荷読み出しに要する時間とを加算した値以上に長くし
てやらなければ、やはり図６に示すようにＸ線画像デー
タが２フレームにまたがる場合が生じる。Conversely, even if the timing of X-ray irradiation is synchronized with the timing of charge storage and frame reading, the charge storage time is a value obtained by adding the X-ray irradiation time and the time required for reading charges for one frame. Otherwise, the X-ray image data may span two frames as shown in FIG.
【０００６】したがって、従来、複数個のフレームメモ
リーを設けて加算処理する等の手段が必要となり、装置
も複雑で高価なものとなる。本発明は、上記課題を解決
するために創案されたものであり、Ｘ線照射時間内にす
べての検出素子から得られるデータを１フレームのみに
納め、最小限のフレームメモリーだけで画像データ処理
が行えるＸ線撮像装置を提供することを目的としてい
る。Therefore, conventionally, means such as providing a plurality of frame memories and performing addition processing is required, and the apparatus becomes complicated and expensive. The present invention has been made in order to solve the above-mentioned problems, and stores data obtained from all the detection elements within one X-ray irradiation time in only one frame, so that image data processing can be performed with only a minimum frame memory. It is an object of the present invention to provide an X-ray imaging apparatus that can perform the operation.
【０００７】[0007]
【課題を解決するための手段】上記目的を達成するため
に、本発明のＸ線撮像装置は、Ｘ線を電荷信号に変換し
て蓄積する複数個のＸ線検出素子と、前記複数個のＸ線
検出素子に蓄積された電荷信号を時系列で順番に読み出
す手段と、読み出された１フレーム分のデータに基づい
てＸ線画像を得るＸ線撮像装置において、所定のＸ線照
射時間に基づき、各Ｘ線検出素子の電荷蓄積時間を、前
記所定のＸ線照射時間と１フレーム分の電荷読み出しに
要する時間とを加算した値以上に自動設定する機能をも
ち、読み出し中の１フレームの最後の画素の電荷読み出
しを終えた直後にＸ線照射を開始させ、前記所定のＸ線
照射時間だけＸ線照射を行うシーケンスを有する制御手
段を備えたことを特徴としている。In order to achieve the above object, an X-ray imaging apparatus according to the present invention comprises: a plurality of X-ray detection elements for converting X-rays into charge signals and storing the charge signals; Means for sequentially reading out the charge signals accumulated in the X-ray detecting element in time series, and an X-ray imaging apparatus for obtaining an X-ray image based on the read data for one frame, a predetermined X-ray irradiation time. A function for automatically setting the charge storage time of each X-ray detection element to a value obtained by adding the predetermined X-ray irradiation time and the time required for reading out charges for one frame, and Control means having a sequence for starting X-ray irradiation immediately after the charge readout of the last pixel is completed and performing X-ray irradiation for the predetermined X-ray irradiation time is provided.
【０００８】本発明では、各Ｘ線検出素子の電荷蓄積時
間を、所定のＸ線照射時間と１フレーム分の電荷読み出
しに要する時間とを加算した値以上に設定し、かつ、Ｘ
線照射のタイミングを、電荷蓄積およびフレーム読み出
しのタイミングと同期させている。具体的には、トリガ
ー信号発生手段と、該トリガー信号の入力を受けた時点
で蓄積電荷の読み出しタイミングに同期させてＸ線照射
のＯＮ・ＯＦＦ動作をコントロールする制御手段とを設
け、前記制御手段には、事前に設定されたＸ線照射時間
に基づき、各Ｘ線検出素子の電荷蓄積時間を、前記所定
のＸ線照射時間と１フレーム分の電荷読み出しに要する
時間とを加算した値以上に自動設定する機能をもたせ、
かつ、トリガー信号の入力時点で読み出し中の１フレー
ムの最後の画素の電荷読み出しを終えた直後にＸ線照射
を開始させ、前記所定のＸ線照射時間だけＸ線照射をＯ
Ｎにするシーケンスを設定しておく。In the present invention, the charge storage time of each X-ray detecting element is set to a value obtained by adding a predetermined X-ray irradiation time and a time required to read out charges for one frame, and
The timing of line irradiation is synchronized with the timing of charge accumulation and frame reading. Specifically, there is provided a trigger signal generating means, and a control means for controlling ON / OFF operation of X-ray irradiation in synchronization with a readout timing of the accumulated charge when the trigger signal is input, wherein the control means The charge accumulation time of each X-ray detection element is set to be equal to or greater than the value obtained by adding the predetermined X-ray irradiation time and the time required to read out charges for one frame based on a preset X-ray irradiation time. With the function of automatic setting,
X-ray irradiation is started immediately after the charge readout of the last pixel of one frame being read out at the time of input of the trigger signal, and the X-ray irradiation is performed for the predetermined X-ray irradiation time.
A sequence for setting N is set.
【０００９】この制御手段によって、図１に示すよう
に、トリガー信号の入力時点で読み出し中の１フレーム
の最後の画素の電荷読み出しを終えた直後にＸ線照射が
開始されるために、全ての画素のＸ線画像データを、必
ずトリガー信号入力時点で読み出し中のフレームの次の
フレーム以降で読み出すことが可能になる。またさら
に、各Ｘ線検出素子の電荷蓄積時間をＸ線照射時間と１
フレーム分の電荷読み出しに要する時間とを加算した値
以上に設定しているために、全ての画素のＸ線画像デー
タが、トリガー信号入力時点で読み出し中のフレームの
次のフレームのみに収まり、トリガー信号入力時点で読
み出し中のフレームの次のフレームのみを読み出すだけ
でＸ線画像を得ることが可能となる。By this control means, as shown in FIG. 1, X-ray irradiation is started immediately after the charge readout of the last pixel of one frame being read out at the time of input of the trigger signal. The X-ray image data of the pixel can be read out in a frame subsequent to the frame being read out at the time of input of the trigger signal. Further, the charge accumulation time of each X-ray detection element is set to be 1
Since the time required for reading the charge for the frame is set to be equal to or greater than the sum of the X-ray image data of all the pixels, the X-ray image data of all the pixels is contained only in the frame next to the frame being read at the time of input of the trigger signal, and the trigger An X-ray image can be obtained simply by reading out only the frame next to the frame being read out at the time of signal input.
【００１０】[0010]
【発明の実施の形態】以下、図面を参照して本発明のＸ
線撮像装置の一実施例を説明する。図２は本発明の具体
的構成を示す図である。Ｘ線検出パネル１は、光電変換
素子１１と、２次元マトリクス状に配列された電荷蓄積
用のコンデンサ１２及びＦＥＴスイッチ１３とからな
り、それぞれ図３に示す回路で接続されている。ここ
で、１個の電荷蓄積用のコンデンサ１２及びこれに接続
された１個のＦＥＴスイッチ１３と、このコンデンサに
対応する領域部分の光電変換素子１１で１個のＸ線検出
素子を構成しており、この場合、Ｘ線検出パネル１は、
コンデンサ１２の個数分だけＸ線検出素子を有している
ことになる。BRIEF DESCRIPTION OF THE DRAWINGS FIG.
An embodiment of the line imaging device will be described. FIG. 2 is a diagram showing a specific configuration of the present invention. The X-ray detection panel 1 includes a photoelectric conversion element 11, a charge storage capacitor 12 and a FET switch 13 arranged in a two-dimensional matrix, and each is connected by a circuit shown in FIG. Here, one charge storage capacitor 12, one FET switch 13 connected thereto, and one photoelectric conversion element 11 in a region corresponding to the capacitor constitute one X-ray detection element. In this case, the X-ray detection panel 1
The number of the X-ray detecting elements is equal to the number of the capacitors 12.
【００１１】ＦＥＴスイッチ１３のゲート端子１４は、
マトリクスの行ごとに共通に接続され、それぞれの行の
ラインはゲートドライバ５の各ライン出力端子に接続さ
れている。また、ＦＥＴスイッチ１３のドレイン端子１
５は、マトリクスの列ごとに共通に接続され、それぞれ
の列のラインは、列ごとに設けた電荷−電圧変換回路６
を介してマルチプレクサ７の各入力端子に接続されてい
る。前記ゲートドライバ５は、読み出し・Ｘ線照射制御
装置４によって与えられる所定の時間間隔で、各ライン
出力端子から順番にパルス信号を出力し、行ごとに順番
にＦＥＴスイッチ１３をＯＮ動作させていく。The gate terminal 14 of the FET switch 13 is
The lines are commonly connected for each row of the matrix, and the lines of each row are connected to each line output terminal of the gate driver 5. The drain terminal 1 of the FET switch 13
5 is connected in common for each column of the matrix, and the line of each column is a charge-voltage conversion circuit 6 provided for each column.
Is connected to each input terminal of the multiplexer 7. The gate driver 5 sequentially outputs a pulse signal from each line output terminal at a predetermined time interval given by the readout / X-ray irradiation control device 4, and turns on the FET switch 13 sequentially for each row. .
【００１２】また、前記マルチプレクサ７は、１行のＯ
Ｎ動作中に、読み出し・Ｘ線照射制御装置４によって与
えられる所定の時間間隔で、各入力端子に入力される信
号をそれぞれで順番に取り込んで、その出力端子に接続
されたＡ／Ｄ変換器８によってデジタル値に変換して順
に出力する。出力されたデータは、画像処理及び表示装
置９によってノイズ除去等適切な画像処理の後、２次元
画像に再構成されて表示される。Further, the multiplexer 7 is provided with one row of O
During the N operation, at predetermined time intervals given by the readout / X-ray irradiation control device 4, the signals inputted to the respective input terminals are sequentially taken in, and the A / D converter connected to the output terminal thereof 8 and converted into digital values and output in order. The output data is reconstructed into a two-dimensional image and displayed after appropriate image processing such as noise removal by the image processing and display device 9.
【００１３】以上の例で挙げたＸ線検出素子１に用いら
れる光電変換素子１１は、ＣｄＴｅ、ＣｄＺｎＴｅ、Ｐ
ｂＩ２、ＴｌＢｒ、ａ−Ｓｅ等の直接型光電変換素子
や、ＣｓＩ等の蛍光体とフォトダイオードとの組み合わ
せからなる間接型光電変換素子のいずれであってもよ
い。またその形態は、電荷蓄積コンデンサ１２とＦＥＴ
スイッチ１３に対応して画素分割されている場合でも、
画素分割されていない場合でも、また、電極のみ、およ
び、フォトダイオードのみが分割されている場合のいず
れであってもよい。また、２次元マトリクス状に配列さ
れた電荷蓄積コンデンサ１２、ＦＥＴスイッチ１３の例
として、ガラス等の基板上にＳｉ薄膜を用いて形成した
ＴＦＴ（薄膜トランジスタ）パネル等が挙げられる。The photoelectric conversion element 11 used in the X-ray detection element 1 described in the above example is composed of CdTe, CdZnTe, Pd
Any of a direct photoelectric conversion element such as bI2, TlBr, a-Se, or an indirect photoelectric conversion element including a combination of a phosphor such as CsI and a photodiode may be used. The form is the charge storage capacitor 12 and FET
Even if the pixel is divided according to the switch 13,
Even when the pixel is not divided, it may be either the electrode alone or the photodiode alone. Examples of the charge storage capacitors 12 and the FET switches 13 arranged in a two-dimensional matrix include a TFT (thin film transistor) panel formed using a Si thin film on a substrate such as glass.
【００１４】以上の構成において、本発明のＸ線撮像装
置の動作の説明を以下に述べる。Ｘ線撮影前に、まずＸ
線発生装置１０にあらかじめＸ線管に与える管電圧、管
電流、照射時間Ｔｘ等を設定しておく。この際、読み出
し・Ｘ線照射制御装置４にもＸ線照射時間Ｔｘの情報が
伝達され、電荷蓄積時間Ｔｃとして、前記Ｘ線照射時間
Ｔｘ、１フレーム分の電荷読み出しに要する時間Ｔｒ、
所定のマージンＴｄのそれぞれを加算した値、式（１）
が算出される。 Ｔｃ ＝ Ｔｘ + Ｔｒ + Ｔｄ …… （１） ここで、全画素数をＮ、１画素の電荷読み出しに要する
時間をｔｒとすると、Ｔｒ＝Ｎ×ｔｒである。またマー
ジンＴｄは、Ｘ線照射開始信号を発してから実際にＸ線
が発生するまでの時間Ｔｄ１と、Ｘ線照射が終了して電
荷蓄積を止めるまでの時間Ｔｄ２の和である。読み出し
・Ｘ線照射制御装置４からはこのＴｃに基づく制御信号
がゲートドライバ５とマルチプレクサ７に伝達され、Ｔ
ｃの間の電荷蓄積と読み出しとが交互に行われるように
ゲートドライバ５とマルチプレクサ７は制御される。次
に、トリガー信号発生手段３からトリガー信号が発せら
れ、読み出し・Ｘ線照射制御装置４に入力されると、読
み出し・Ｘ線照射制御装置４は、その時点で読み出し中
の１フレームの最後の画素の電荷読み出しを終えた直後
に、Ｘ線照射を開始させる信号をＸ線発生装置１０に送
る。The operation of the X-ray imaging apparatus of the present invention having the above configuration will be described below. Before X-ray photography,
A tube voltage, a tube current, an irradiation time Tx, and the like to be applied to the X-ray tube are set in the X-ray generator 10 in advance. At this time, information on the X-ray irradiation time Tx is also transmitted to the readout / X-ray irradiation control device 4, and as the charge accumulation time Tc, the X-ray irradiation time Tx, the time Tr required for reading out one frame of charge,
Value obtained by adding each of the predetermined margins Td, Expression (1)
Is calculated. Tc = Tx + Tr + Td (1) Here, assuming that the total number of pixels is N and the time required for reading the charge of one pixel is tr, Tr = N × tr. The margin Td is the sum of the time Td1 from when the X-ray irradiation start signal is issued to the time when X-rays are actually generated and the time Td2 when the X-ray irradiation ends and the charge accumulation is stopped. A control signal based on this Tc is transmitted from the readout / X-ray irradiation control device 4 to the gate driver 5 and the multiplexer 7, and
The gate driver 5 and the multiplexer 7 are controlled so that the charge accumulation and the reading during c are performed alternately. Next, when a trigger signal is issued from the trigger signal generation means 3 and input to the readout / X-ray irradiation control device 4, the readout / X-ray irradiation control device 4 outputs the last one frame of the currently readout frame. Immediately after the completion of the charge reading of the pixel, a signal for starting X-ray irradiation is sent to the X-ray generator 10.
【００１５】マージン時間Ｔｄ１の後開始されるＸ線照
射はＸ線照射時間Ｔｘの後に終了し、電荷蓄積時間Ｔｃ
が式（１）のように設定されているために、マージン時
間Ｔｄ２の後にフレーム読み出しが開始される。読み出
し・Ｘ線照射制御装置４からＸ線照射を開始させる信号
がＸ線発生装置に送られる時に、同時に画像処理及び表
示装置にも信号が送られるような仕組みを設けておけ
ば、その信号を受けた直後に読み出された１フレームが
Ｘ線画像データが収まったフレームであると判断するこ
とが容易にできる。このフレームデータを画像処理及び
表示装置９によってノイズ除去等適切な画像処理を行っ
た後、２次元画像に再構成することで、余分なフレーム
メモリーや、フレーム加算等の演算手段を必要とせずに
Ｘ線画像を得ることができる。以上述べた手段におい
て、トリガー信号入力以前のフレームデータにはＸ線入
射による情報は含まれていない。The X-ray irradiation started after the margin time Td1 ends after the X-ray irradiation time Tx, and the charge accumulation time Tc
Is set as in Expression (1), frame reading is started after the margin time Td2. When a signal for starting X-ray irradiation is sent from the readout / X-ray irradiation control device 4 to the X-ray generator, a signal is also sent to the image processing and display device at the same time. It is easy to determine that one frame read immediately after receiving is a frame in which X-ray image data is stored. The frame data is subjected to appropriate image processing such as noise removal by the image processing and display device 9 and then reconstructed into a two-dimensional image, thereby eliminating the need for an extra frame memory or arithmetic means such as frame addition. An X-ray image can be obtained. In the means described above, the frame data before the input of the trigger signal does not include information based on the incidence of X-rays.
【００１６】この時点では、Ｘ線検出素子の暗電流によ
って蓄積された電荷の読み出しが行われる。この動作
は、Ｘ線検出素子の動作と読み出し手段の動作とを安定
させる効果をもっている。通常、Ｘ線の発生には、フィ
ラメント（陰極）の電流とターゲット（陽極）の回転を
安定させるために数秒の時間を必要とする。そのため通
常ののＸ線撮像装置では、Ｘ線管を安定させるためのス
タンバイスイッチを設けて、スタンバイスイッチＯＮ
後、所定の時間経過後でなければＸ線照射スイッチがＯ
Ｎできないような仕組みを設けている。そこで、このＸ
線照射スイッチとトリガー信号発生手段３とが連動する
ようにしておけば、装置は簡単に構成できる。At this point, the charge stored by the dark current of the X-ray detecting element is read. This operation has the effect of stabilizing the operation of the X-ray detection element and the operation of the reading means. Usually, generation of X-rays requires several seconds to stabilize the current of the filament (cathode) and the rotation of the target (anode). Therefore, in a normal X-ray imaging apparatus, a standby switch for stabilizing the X-ray tube is provided, and the standby switch is turned on.
After that, unless the predetermined time has elapsed, the X-ray irradiation switch is turned on.
There is a mechanism that does not allow N. So this X
If the line irradiation switch and the trigger signal generating means 3 are linked, the device can be easily configured.
【００１７】ただし、この場合でも、実際のＸ線照射
は、読み出し・Ｘ線照射制御装置４のシーケンスに基づ
き制御される。またさらに、スタンバイスイッチＯＮ後
の所定の遅延時間経過後に自動的にＸ線管からＸ線を照
射するための信号を出力する回路が設けられている場
合、トリガー信号発生手段３がこの回路と連動ようにし
ておけば、装置はより簡単に構成することができる。こ
の場合も実際のＸ線照射は、読み出し・Ｘ線照射制御装
置４のシーケンスに基づき制御されることは言うまでも
ない。また同様に、スタンバイスイッチＯＮ後に、電荷
蓄積およびフレーム読み出しのタイミングと同期した所
定の遅延時間後にトリガー信号が自動的に発生されるよ
うあらかじめ読み出し・Ｘ線照射制御装置４に設定され
たものであってもよい。However, even in this case, the actual X-ray irradiation is controlled based on the sequence of the readout / X-ray irradiation control device 4. Further, when a circuit for automatically outputting a signal for irradiating X-rays from the X-ray tube after a predetermined delay time has elapsed after the standby switch is turned on is provided, the trigger signal generating means 3 operates in conjunction with this circuit. If so, the device can be configured more easily. Also in this case, it goes without saying that the actual X-ray irradiation is controlled based on the sequence of the readout / X-ray irradiation control device 4. Similarly, after the standby switch is turned on, the readout / X-ray irradiation control device 4 is set in advance so that a trigger signal is automatically generated after a predetermined delay time synchronized with the timing of charge accumulation and frame readout. You may.
【００１８】以上述べた方法において、トリガー信号発
生手段３、読み出し・Ｘ線照射制御装置４それぞれを、
Ｘ線管の管電圧、管電流、照射時間等を設定してＸ線管
のスタンバイ、照射をコントロールするためのＸ線制御
卓に組み込むことで、装置はさらに簡単に構成すること
ができる。In the method described above, the trigger signal generating means 3 and the readout / X-ray irradiation control device 4
By setting the tube voltage, tube current, irradiation time, and the like of the X-ray tube and incorporating them in an X-ray control console for controlling the standby and irradiation of the X-ray tube, the apparatus can be further simplified.
【００１９】[0019]
【発明の効果】本発明のＸ線撮像装置によれば、Ｘ線照
射時間内にすべての検出素子から得られるデータを１フ
レームのみに納め、最小限のフレームメモリーだけで画
像データ処理が行えるように構成しているので、Ｘフィ
ルムレスで即時描画が可能なＸ線撮像装置を、余分なフ
レームメモリーや、フレーム加算等の演算手段を必要と
せずに低コストで提供できる。According to the X-ray imaging apparatus of the present invention, data obtained from all the detection elements within the X-ray irradiation time is stored in only one frame, and image data processing can be performed with only a minimum frame memory. Therefore, an X-ray imaging apparatus capable of instantaneous drawing without an X-film can be provided at low cost without requiring an extra frame memory or an arithmetic unit such as frame addition.
【図１】本発明の時間タイミングを示す図である。FIG. 1 is a diagram showing time timing of the present invention.
【図２】本発明のＸ線撮像装置の一実施例を示す図であ
る。FIG. 2 is a diagram showing an embodiment of the X-ray imaging apparatus of the present invention.
【図３】Ｘ線検出素子１の回路構成を示す図である。FIG. 3 is a diagram showing a circuit configuration of the X-ray detection element 1.
【図４】従来の電荷読み出し方法を示す図である。FIG. 4 is a diagram showing a conventional charge reading method.
【図５】従来の電荷読み出し方法を示す図である。FIG. 5 is a diagram showing a conventional charge reading method.
【図６】従来の電荷読み出し方法を示す図である。FIG. 6 is a diagram showing a conventional charge reading method.
１ Ｘ線検出パネル ３ トリガー信号発生手段 ４ 読み出し・Ｘ線照射制御装置 ５ ゲートドライバ ６ 電荷−電圧変換回路 ７ マルチプレクサ ８ A/D変換器 ９ 画像処理及び表示装置 １０ Ｘ線発生装置 １１ 光電変換素子 １２ 電荷蓄積コンデンサ １３ ＦＥＴスイッチ １４ ゲート端子 １５ ドレイン端子 DESCRIPTION OF SYMBOLS 1 X-ray detection panel 3 Trigger signal generation means 4 Readout / X-ray irradiation control device 5 Gate driver 6 Charge-voltage conversion circuit 7 Multiplexer 8 A / D converter 9 Image processing and display device 10 X-ray generation device 11 Photoelectric conversion element 12 Charge storage capacitor 13 FET switch 14 Gate terminal 15 Drain terminal
Claims (4)
個のＸ線検出素子と、前記複数個のＸ線検出素子に蓄積
された電荷信号を時系列で順番に読み出す手段と、読み
出された１フレーム分のデータに基づいてＸ線画像を得
るＸ線撮像装置において、所定のＸ線照射時間に基づ
き、各Ｘ線検出素子の電荷蓄積時間を、前記所定のＸ線
照射時間と１フレーム分の電荷読み出しに要する時間と
を加算した値以上に自動設定する機能をもち、読み出し
中の１フレームの最後の画素の電荷読み出しを終えた直
後にＸ線照射を開始させ、前記所定のＸ線照射時間だけ
Ｘ線照射を行うシーケンスを有する制御手段を備えたこ
とを特徴とするＸ線撮像装置。A plurality of X-ray detecting elements for converting X-rays into charge signals and storing the converted signals; a means for sequentially reading out the charge signals stored in the plurality of X-ray detecting elements in time series; In an X-ray imaging apparatus that obtains an X-ray image based on the output data for one frame, based on a predetermined X-ray irradiation time, a charge accumulation time of each X-ray detection element is set to the predetermined X-ray irradiation time. A function of automatically setting the time required for reading the charge of one frame to be equal to or more than the sum thereof, starting X-ray irradiation immediately after finishing reading the charge of the last pixel of one frame being read, and An X-ray imaging apparatus comprising a control unit having a sequence for performing X-ray irradiation for the X-ray irradiation time.
ガー信号の入力を受けた時点でＸ線検出素子の蓄積電荷
の読み出しタイミングに同期させてＸ線照射のＯＮ・Ｏ
ＦＦ動作をコントロールすることを特徴とする請求項１
に記載のＸ線撮像装置。And a trigger signal generating means for turning on / off the X-ray irradiation in synchronism with the timing of reading the accumulated charge of the X-ray detecting element at the time of receiving the trigger signal.
2. The FF operation is controlled.
3. The X-ray imaging apparatus according to claim 1.
うためのスイッチと連動するものであって、実際のＸ線
照射のタイミングは読み出し中の１フレームの最後の画
素の電荷読み出しを終えた直後であることを特徴とする
請求項２に記載のＸ線撮像装置。3. The trigger signal generating means is interlocked with a switch for irradiating X-rays, and the timing of the actual X-ray irradiation has finished reading out the charge of the last pixel of one frame being read out. The X-ray imaging apparatus according to claim 2, wherein the X-ray imaging apparatus is immediately after.
管をスタンバイ状態にするためのスイッチであって、こ
のスイッチが押された後の所定の遅延時間後に自動的に
Ｘ線管からＸ線を照射するための信号を出力する回路と
連動するものであることを特徴とする請求項３に記載の
Ｘ線撮像装置。4. A switch for performing X-ray irradiation is a switch for setting the X-ray tube in a standby state, and automatically switches from the X-ray tube after a predetermined delay time after the switch is pressed. The X-ray imaging apparatus according to claim 3, wherein the X-ray imaging apparatus is linked with a circuit that outputs a signal for irradiating X-rays.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP09031999A JP4207300B2 (en) | 1999-03-30 | 1999-03-30 | X-ray imaging device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP09031999A JP4207300B2 (en) | 1999-03-30 | 1999-03-30 | X-ray imaging device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JP2000284058A true JP2000284058A (en) | 2000-10-13 |
| JP4207300B2 JP4207300B2 (en) | 2009-01-14 |
Family
ID=13995216
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP09031999A Expired - Lifetime JP4207300B2 (en) | 1999-03-30 | 1999-03-30 | X-ray imaging device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP4207300B2 (en) |
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2003000136A1 (en) * | 2001-06-22 | 2003-01-03 | Hitachi Medical Corporation | X-ray image diagnosing device, and x-ray image data correcting method |
| JP2006296494A (en) * | 2005-04-15 | 2006-11-02 | Toshiba Corp | X-ray diagnostic apparatus and its controlling method |
| JP2006333898A (en) * | 2005-05-31 | 2006-12-14 | Canon Inc | Radiographic imaging system |
| JP2008154600A (en) * | 2006-12-20 | 2008-07-10 | Shimadzu Corp | Radiographic device |
| WO2009075172A1 (en) * | 2007-12-10 | 2009-06-18 | Konica Minolta Medical & Graphic, Inc. | X-ray image photographing system |
| JP2015134030A (en) * | 2014-01-16 | 2015-07-27 | 株式会社東芝 | X-ray computer tomographic apparatus |
| JP2020062404A (en) * | 2018-10-12 | 2020-04-23 | キヤノンメディカルシステムズ株式会社 | X-ray ct apparatus and imaging planning apparatus |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS61286843A (en) * | 1985-06-14 | 1986-12-17 | Shimadzu Corp | Fluoroscopic fast photography system |
| JPH067333A (en) * | 1992-06-25 | 1994-01-18 | Toshiba Corp | X-ray diagnostic system |
| JPH0938071A (en) * | 1995-08-03 | 1997-02-10 | Toshiba Medical Eng Co Ltd | X-ray diagnostic device |
| JPH09131337A (en) * | 1995-11-07 | 1997-05-20 | Toshiba Medical Eng Co Ltd | X-ray image pickup device |
| JPH09140691A (en) * | 1995-11-27 | 1997-06-03 | Toshiba Medical Eng Co Ltd | X-ray photographing apparatus |
| JPH09266903A (en) * | 1996-01-31 | 1997-10-14 | Toshiba Corp | Tomograph |
| JPH09294229A (en) * | 1996-02-26 | 1997-11-11 | Canon Inc | Photoelectric conversion device and driving method for the device |
| JPH09321267A (en) * | 1996-02-22 | 1997-12-12 | Canon Inc | Photoelectric conveter and driving method therefor |
-
1999
- 1999-03-30 JP JP09031999A patent/JP4207300B2/en not_active Expired - Lifetime
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS61286843A (en) * | 1985-06-14 | 1986-12-17 | Shimadzu Corp | Fluoroscopic fast photography system |
| JPH067333A (en) * | 1992-06-25 | 1994-01-18 | Toshiba Corp | X-ray diagnostic system |
| JPH0938071A (en) * | 1995-08-03 | 1997-02-10 | Toshiba Medical Eng Co Ltd | X-ray diagnostic device |
| JPH09131337A (en) * | 1995-11-07 | 1997-05-20 | Toshiba Medical Eng Co Ltd | X-ray image pickup device |
| JPH09140691A (en) * | 1995-11-27 | 1997-06-03 | Toshiba Medical Eng Co Ltd | X-ray photographing apparatus |
| JPH09266903A (en) * | 1996-01-31 | 1997-10-14 | Toshiba Corp | Tomograph |
| JPH09321267A (en) * | 1996-02-22 | 1997-12-12 | Canon Inc | Photoelectric conveter and driving method therefor |
| JPH09294229A (en) * | 1996-02-26 | 1997-11-11 | Canon Inc | Photoelectric conversion device and driving method for the device |
Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2003000136A1 (en) * | 2001-06-22 | 2003-01-03 | Hitachi Medical Corporation | X-ray image diagnosing device, and x-ray image data correcting method |
| US6944267B2 (en) * | 2001-06-22 | 2005-09-13 | Hitachi Medical Corporation | X-ray image diagnostic device, and x-ray image data correcting method |
| JP2006296494A (en) * | 2005-04-15 | 2006-11-02 | Toshiba Corp | X-ray diagnostic apparatus and its controlling method |
| JP4632845B2 (en) * | 2005-04-15 | 2011-02-16 | 株式会社東芝 | X-ray diagnostic equipment |
| JP2006333898A (en) * | 2005-05-31 | 2006-12-14 | Canon Inc | Radiographic imaging system |
| JP4684747B2 (en) * | 2005-05-31 | 2011-05-18 | キヤノン株式会社 | Radiation generator and control method |
| JP2008154600A (en) * | 2006-12-20 | 2008-07-10 | Shimadzu Corp | Radiographic device |
| WO2009075172A1 (en) * | 2007-12-10 | 2009-06-18 | Konica Minolta Medical & Graphic, Inc. | X-ray image photographing system |
| JPWO2009075172A1 (en) * | 2007-12-10 | 2011-04-28 | コニカミノルタエムジー株式会社 | X-ray imaging system |
| JP2015134030A (en) * | 2014-01-16 | 2015-07-27 | 株式会社東芝 | X-ray computer tomographic apparatus |
| JP2020062404A (en) * | 2018-10-12 | 2020-04-23 | キヤノンメディカルシステムズ株式会社 | X-ray ct apparatus and imaging planning apparatus |
| JP7337642B2 (en) | 2018-10-12 | 2023-09-04 | キヤノンメディカルシステムズ株式会社 | X-ray CT device |
Also Published As
| Publication number | Publication date |
|---|---|
| JP4207300B2 (en) | 2009-01-14 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US7227926B2 (en) | Imaging apparatus and imaging system | |
| US5818898A (en) | X-ray imaging apparatus using X-ray planar detector | |
| US7031431B2 (en) | Radiological imaging apparatus and method | |
| US8785870B2 (en) | Imaging apparatus, radiation imaging system, and control method of image sensor | |
| US7724874B2 (en) | Radiation imaging apparatus, driving method thereof and radiation imaging system | |
| US7123687B2 (en) | Method for displaying digital X-ray image data at high resolution | |
| US8680471B2 (en) | Imaging apparatus, imaging system, method of controlling the apparatus and the system, and program | |
| US6944267B2 (en) | X-ray image diagnostic device, and x-ray image data correcting method | |
| US20120170827A1 (en) | Imaging apparatus, imaging system, method of controlling the apparatus and the system, and program | |
| JP2018149047A (en) | Radiographic imaging system | |
| JPS61286843A (en) | Fluoroscopic fast photography system | |
| JP6695260B2 (en) | Radiation image capturing apparatus, radiation image capturing method, and radiation image capturing program | |
| JP4207300B2 (en) | X-ray imaging device | |
| JPH09140691A (en) | X-ray photographing apparatus | |
| US6160260A (en) | Photoelectric conversion device, and system and image reading method using the device | |
| JP5241047B2 (en) | Digital radiation imaging apparatus, information processing apparatus, radiation imaging apparatus, control method for digital radiation imaging apparatus, control method for information processing apparatus, and control method for radiation imaging apparatus | |
| JP2006192150A (en) | Radiographing apparatus | |
| JP2018192024A (en) | Radiographic system | |
| JP2006158608A (en) | Radiographic equipment | |
| JP4649061B2 (en) | Imaging apparatus, imaging method, storage medium, and program | |
| JPS61172488A (en) | Solid-state image pickup device | |
| JP4731732B2 (en) | Imaging apparatus, imaging method, recording medium, and program | |
| WO2019239755A1 (en) | Radiation imaging device, radiation imaging system, and method for controlling radiation imaging device | |
| JP4632845B2 (en) | X-ray diagnostic equipment | |
| JP2024060903A (en) | Radiation imaging apparatus and control method thereof |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| A621 | Written request for application examination |
Free format text: JAPANESE INTERMEDIATE CODE: A621 Effective date: 20040713 |
|
| A977 | Report on retrieval |
Free format text: JAPANESE INTERMEDIATE CODE: A971007 Effective date: 20060630 |
|
| A131 | Notification of reasons for refusal |
Free format text: JAPANESE INTERMEDIATE CODE: A131 Effective date: 20070724 |
|
| A521 | Request for written amendment filed |
Free format text: JAPANESE INTERMEDIATE CODE: A523 Effective date: 20070921 |
|
| A02 | Decision of refusal |
Free format text: JAPANESE INTERMEDIATE CODE: A02 Effective date: 20080408 |
|
| A521 | Request for written amendment filed |
Free format text: JAPANESE INTERMEDIATE CODE: A523 Effective date: 20080609 |
|
| A911 | Transfer to examiner for re-examination before appeal (zenchi) |
Free format text: JAPANESE INTERMEDIATE CODE: A911 Effective date: 20080618 |
|
| A131 | Notification of reasons for refusal |
Free format text: JAPANESE INTERMEDIATE CODE: A131 Effective date: 20080826 |
|
| A521 | Request for written amendment filed |
Free format text: JAPANESE INTERMEDIATE CODE: A523 Effective date: 20080903 |
|
| TRDD | Decision of grant or rejection written | ||
| A01 | Written decision to grant a patent or to grant a registration (utility model) |
Free format text: JAPANESE INTERMEDIATE CODE: A01 Effective date: 20080930 |
|
| A01 | Written decision to grant a patent or to grant a registration (utility model) |
Free format text: JAPANESE INTERMEDIATE CODE: A01 |
|
| A61 | First payment of annual fees (during grant procedure) |
Free format text: JAPANESE INTERMEDIATE CODE: A61 Effective date: 20081013 |
|
| R150 | Certificate of patent or registration of utility model |
Free format text: JAPANESE INTERMEDIATE CODE: R150 |
|
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20111031 Year of fee payment: 3 |
|
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20111031 Year of fee payment: 3 |
|
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20121031 Year of fee payment: 4 |
|
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20121031 Year of fee payment: 4 |
|
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20131031 Year of fee payment: 5 |
|
| EXPY | Cancellation because of completion of term |