JP4891662B2 - Mammography equipment - Google Patents

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JP4891662B2
JP4891662B2 JP2006160129A JP2006160129A JP4891662B2 JP 4891662 B2 JP4891662 B2 JP 4891662B2 JP 2006160129 A JP2006160129 A JP 2006160129A JP 2006160129 A JP2006160129 A JP 2006160129A JP 4891662 B2 JP4891662 B2 JP 4891662B2
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奈央子 小ノ上
雅行 西木
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Toshiba Corp
Canon Medical Systems Corp
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本発明は、トモシンセシス撮影を可能とするマンモグラフィ装置に関する。   The present invention relates to a mammography apparatus that enables tomosynthesis imaging.

デジタル検出器を用いたマンモグラフィ装置の従来の技術では、診断画像発生のためのＸ線撮影を行う前に、予備的なＸ線撮影（プリ撮影）を行う必要がある。この予備的な撮影はＸ線撮影に関するＸ線発生条件を決めるために必要である。予備的なＸ線撮影は診断画像発生には用いないのが一般的であるが、予備的なＸ線撮影によって得られた画像データをその後の撮影によって得られた画像データに加算する技術がある（特許文献１を参照）。   In the conventional technique of a mammography apparatus using a digital detector, it is necessary to perform preliminary X-ray imaging (pre-imaging) before performing X-ray imaging for generating a diagnostic image. This preliminary imaging is necessary to determine the X-ray generation conditions for X-ray imaging. Although preliminary X-ray imaging is generally not used for generating diagnostic images, there is a technique for adding image data obtained by preliminary X-ray imaging to image data obtained by subsequent imaging. (See Patent Document 1).

マンモグラフィ装置において断層画像データを得る手法として、トモシンセシス撮影法がある。トモシンセシス撮影法はデジタル検出器を用い、Ｘ線管球を被検体に対し相対的に移動させながら複数回Ｘ線撮影を行う撮影法である。従来のトモシンセシス撮影法は、まず予備的なＸ線撮影を行い、その結果に基づいて、本撮影（メイン撮影）のＸ線発生条件を決定する。次に、得られた投影画像の画素値に基づいて決定されたＸ線発生条件で複数回Ｘ線撮影を行い、これを断層画像データ発生に用いる。
特開平７−１５３５９２号公報 As a technique for obtaining tomographic image data in a mammography apparatus, there is a tomosynthesis imaging method. The tomosynthesis imaging method is an imaging method that uses a digital detector and performs X-ray imaging a plurality of times while moving an X-ray tube relative to a subject. In the conventional tomosynthesis imaging method, preliminary X-ray imaging is first performed, and X-ray generation conditions for main imaging (main imaging) are determined based on the result. Next, X-ray imaging is performed a plurality of times under the X-ray generation condition determined based on the pixel value of the obtained projection image, and this is used for generating tomographic image data.
Japanese Patent Laid-Open No. 7-153592

本発明の目的は、被検体の被曝線量の低減を実現するトモシンセシス撮影を行うマンモグラフィ装置を提供することにある。   An object of the present invention is to provide a mammography apparatus that performs tomosynthesis imaging that realizes a reduction in the exposure dose of a subject.

上記目的を達成するために本発明は、第１局面において、Ｘ線を発生するＸ線管球と、前記Ｘ線管球に印加するための高電圧を発生する高電圧発生部と、被検体の***を透過した透過Ｘ線を検出するＸ線検出部と、前記Ｘ線管球と前記Ｘ線検出部とを移動可能に支持する支持機構と、前記高電圧発生部と前記検出部と前記支持機構とを制御してＸ線撮影を繰り返す撮影制御部と、前記繰り返されるＸ線撮影のうち１回目のＸ線撮影による前記Ｘ線検出部の出力に基づいて２回目のＸ線撮影におけるＸ線発生条件を決定し、前記１回目のＸ線撮影による前記Ｘ線検出部の出力に基づいて前記２回目のＸ線撮影のＸ線発生条件とは相違する３回目以降の各Ｘ線撮影におけるＸ線発生条件を決定する条件決定部と、前記繰り返されるＸ線撮影により収集される前記Ｘ線検出部の出力に基づいて前記被検体の***に関する断層画像データを発生する画像発生部とを具備する。     In order to achieve the above object, in the first aspect, the present invention provides an X-ray tube that generates X-rays, a high-voltage generator that generates a high voltage to be applied to the X-ray tube, and a subject. An X-ray detector that detects transmitted X-rays transmitted through the breast, a support mechanism that movably supports the X-ray tube and the X-ray detector, the high-voltage generator, the detector, and the An X-ray imaging unit that repeats X-ray imaging by controlling the support mechanism; and X in the second X-ray imaging based on the output of the X-ray detection unit by the first X-ray imaging among the repeated X-ray imaging X-ray generation conditions are determined, and each X-ray imaging after the third time is different from the X-ray generation conditions of the second X-ray imaging based on the output of the X-ray detection unit by the first X-ray imaging. A condition determining unit for determining an X-ray generation condition and the repeated X-ray imaging; Comprising an image generator for generating a tomographic image data for the breast of the subject based on an output of the X-ray detector which is collected.

本発明の第２局面において、Ｘ線を発生するＸ線管球と、前記Ｘ線管球に印加するための高電圧を発生する高電圧発生部と、被検体の***を透過した透過Ｘ線を検出するＸ線検出部と、前記Ｘ線管球と前記Ｘ線検出部とを移動可能に支持する支持機構と、前記高電圧発生部と前記検出部と前記支持機構とを制御してＸ線撮影を繰り返す撮影制御部と、前記繰り返されるＸ線撮影のうち１回目のＸ線撮影による前記Ｘ線検出部の出力に基づいて２回目以降の各Ｘ線撮影におけるＸ線発生条件を決定する条件決定部と、前記１回目と前記２回目以降の各Ｘ線撮影による前記Ｘ線検出部の出力とに応じたゲインで前記一回目のＸ線撮影により生じた投影画像にゲイン処理をする画像処理部と、前記２回目以降のＸ線撮影により収集される複数の投影画像と前記ゲイン処理を受けた１回目の投影画像とに基づいて、前記被検体の***に関する断層画像データを発生する結像処理部と画像発生部とを具備する。   In the second aspect of the present invention, an X-ray tube that generates X-rays, a high-voltage generator that generates a high voltage to be applied to the X-ray tube, and transmitted X-rays that have passed through the breast of the subject An X-ray detection unit for detecting the X-ray, a support mechanism for movably supporting the X-ray tube and the X-ray detection unit, the high-voltage generation unit, the detection unit, and the support mechanism to control X X-ray generation conditions in the second and subsequent X-ray imaging are determined based on the output of the imaging control unit that repeats X-ray imaging and the output of the X-ray detection unit by the first X-ray imaging among the repeated X-ray imaging An image for performing gain processing on the projection image generated by the first X-ray imaging with a gain according to the condition determining unit and the output of the X-ray detection unit by the first and second and subsequent X-ray imaging A processing unit and a plurality of projections collected by the second and subsequent X-ray imaging On the basis of the first projection image for which the gain processing and the image, said comprising an imaging processing unit and an image generator for generating a tomographic image data for the breast of the subject.

本発明によれば、被検体の被曝線量の低減を実現するトモシンセシス撮影を行うことが可能となる。   According to the present invention, it is possible to perform tomosynthesis imaging that achieves a reduction in the exposure dose of a subject.

（第１の実施形態）
以下図面を参照して本発明の実施形態を説明する。 (First embodiment)
Embodiments of the present invention will be described below with reference to the drawings.

図１は本発明の実施形態に係わるマンモグラフィ装置の構成を示している。マンモグラフィ装置はＸ線撮影台１を有している。Ｘ線撮影台１は、図２に示すように、フレーム２２とフレーム２３を有している。フレーム２２、２３は支柱１９に水平に取り付けられた軸部２０に接続されている。フレーム２２、２３は軸部２０の軸心を回転中心軸Ｒとして個別に回転可能なように支柱１９により支持される。この回転方向をβ方向とする。   FIG. 1 shows the configuration of a mammography apparatus according to an embodiment of the present invention. The mammography apparatus has an X-ray imaging table 1. As shown in FIG. 2, the X-ray imaging table 1 has a frame 22 and a frame 23. The frames 22 and 23 are connected to a shaft portion 20 attached horizontally to the support column 19. The frames 22 and 23 are supported by the support column 19 so as to be individually rotatable with the axis of the shaft portion 20 as the rotation center axis R. This rotation direction is defined as the β direction.

フレーム２３の端にはＸ線管装置２４が装備されている。Ｘ線管装置２４はＸ線管球２を収容する。Ｘ線管球２は高電圧発生部３から高電圧の印加とフィラメント電流の供給とを受けてＸ線を発生する。   An X-ray tube device 24 is provided at the end of the frame 23. The X-ray tube device 24 accommodates the X-ray tube 2. The X-ray tube 2 generates X-rays in response to application of a high voltage and supply of a filament current from the high voltage generator 3.

フレーム２２の端にはＸ線管球２に対向する向きにＸ線検出部５が装備されている。Ｘ線検出部５は、入射Ｘ線を直接的に電気信号に変換する直接変換形又は入射Ｘ線を蛍光体で光に変換しその光を電気信号に変換する間接変換形の複数の半導体検出素子を有する。複数の半導体検出素子は２次元格子状に配列される。Ｘ線入射に伴って複数の半導体検出素子で発生した信号電荷はデータ収集部６を介してデジタル信号として読み出される。Ｘ線検出部５はイメージインテンシファイアと光学的カメラとの組み合わせで代替可能である。   An X-ray detector 5 is provided at the end of the frame 22 in a direction facing the X-ray tube 2. The X-ray detection unit 5 is a direct conversion type that directly converts incident X-rays into electrical signals, or an indirect conversion type that converts incident X-rays into light with a phosphor and converts the light into electrical signals. It has an element. The plurality of semiconductor detection elements are arranged in a two-dimensional lattice pattern. Signal charges generated by a plurality of semiconductor detection elements as a result of X-ray incidence are read out as digital signals via the data acquisition unit 6. The X-ray detector 5 can be replaced by a combination of an image intensifier and an optical camera.

図２に示すように、フレーム２２の端にはＸ線検出部５とともに下側圧迫板１７が取り付けられている。下側圧迫板１７の背面にＸ線検出部５が配置される。上側圧迫板１８は下側圧迫板１７に対向し、下側圧迫板１７と接近／離反する方向に移動可能にフレーム２２に取り付けられている。ここで、回転中心軸ＲをＺ軸とし、Ｙ軸を焦点ｆと検出部５の有効面の中心とを結ぶ線（撮影軸）に規定し、Ｘ軸をＹＺ平面に垂直に規定する。なお、ＸＹＺ座標系はＺ軸を中心とした回転座標系を構成する。下側圧迫板１７と上側圧迫板１８間距離を矢印α方向とする。下側圧迫板１７は、フレーム２２に矢印α方向に関して移動可能に支持された上側圧迫板１８とともに、被検体の***をスラブ状に圧迫するために設けられている。   As shown in FIG. 2, the lower compression plate 17 is attached to the end of the frame 22 together with the X-ray detection unit 5. The X-ray detection unit 5 is disposed on the back surface of the lower compression plate 17. The upper compression plate 18 faces the lower compression plate 17 and is attached to the frame 22 so as to be movable in a direction approaching / separating from the lower compression plate 17. Here, the rotation center axis R is the Z-axis, the Y-axis is defined as a line (imaging axis) connecting the focal point f and the center of the effective surface of the detection unit 5, and the X-axis is defined perpendicular to the YZ plane. The XYZ coordinate system constitutes a rotating coordinate system with the Z axis as the center. A distance between the lower compression plate 17 and the upper compression plate 18 is defined as an arrow α direction. The lower compression plate 17 and the upper compression plate 18 supported by the frame 22 so as to be movable in the direction of the arrow α are provided to compress the breast of the subject in a slab shape.

本実施形態に係わるマンモグラフィ装置は、Ｘ線撮影台１とともに、システム制御部７、撮影制御部８、操作部９、画像記憶部１０、画像発生部１１、条件決定部１２、画像処理部１３、結像処理部１４、表示部１５を備えている。   The mammography apparatus according to this embodiment includes an X-ray imaging table 1, a system control unit 7, an imaging control unit 8, an operation unit 9, an image storage unit 10, an image generation unit 11, a condition determination unit 12, an image processing unit 13, An imaging processing unit 14 and a display unit 15 are provided.

トモシンセシス撮影はＸ線管球２の位置を順次変えて撮影を行うことによって断層画像データを得る撮影法である。このトモシンセシス撮影を行うために、システム制御部７はマンモグラフィ装置全体を制御する。撮影制御部８は、トモシンセシス撮影を行うための所定の手順に従って支持機構４制御し、Ｘ線発生条件（Ｘ線継続時間、管電流、管電圧）に基づいて高電圧発生部３制御することでＸ線管球２からＸ線を発生させ、データ収集部６を制御することでデジタル信号を得る。このように、撮影制御部８が繰り返し支持機構４とＸ線発生部３とデータ収集部６とを制御することでトモシンセシス撮影が可能となる。画像記憶部１０はＸ線撮影によって得られた複数の投影画像を記憶する。画像処理部１３は画像記憶部１０に記憶されている画像に任意の画像処理をする。この画像処理された画像は画像記憶部１０に記憶される。結像処理部１４はＸ線撮影で得られた複数の投影画像を結像する。なお、結像処理に使用する投影画像は画像処理部１３によって画像処理された画像であってもよい。ここで、結像して得られた画像のデータを断層画像データと称する。画像記憶部１０はこの断層画像データを記憶する。画像発生部１１は結像処理部１４によって得られた所望の断層画像データを表示部１５に発生させる。操作部９はＸ線撮影台１のフレーム２２、２３や上側圧迫板１８などの移動に関する操作や、表示部１５に表示された画像上の操作を行う。条件決定部１２はＸ線発生条件を決めるための入力値を受け、Ｘ線発生条件を決定する。   Tomosynthesis imaging is an imaging method in which tomographic image data is obtained by performing imaging while sequentially changing the position of the X-ray tube 2. In order to perform this tomosynthesis imaging, the system control unit 7 controls the entire mammography apparatus. The imaging control unit 8 controls the support mechanism 4 according to a predetermined procedure for performing tomosynthesis imaging, and controls the high voltage generation unit 3 based on the X-ray generation conditions (X-ray duration, tube current, tube voltage). A digital signal is obtained by generating X-rays from the X-ray tube 2 and controlling the data collection unit 6. As described above, the imaging control unit 8 repeatedly controls the support mechanism 4, the X-ray generation unit 3, and the data collection unit 6 to enable tomosynthesis imaging. The image storage unit 10 stores a plurality of projection images obtained by X-ray imaging. The image processing unit 13 performs arbitrary image processing on the image stored in the image storage unit 10. The image processed image is stored in the image storage unit 10. The imaging processing unit 14 forms a plurality of projection images obtained by X-ray imaging. Note that the projection image used for the imaging process may be an image that has been subjected to image processing by the image processing unit 13. Here, image data obtained by imaging is referred to as tomographic image data. The image storage unit 10 stores the tomographic image data. The image generation unit 11 causes the display unit 15 to generate desired tomographic image data obtained by the imaging processing unit 14. The operation unit 9 performs operations related to movement of the frames 22 and 23 and the upper compression plate 18 of the X-ray imaging table 1 and operations on the image displayed on the display unit 15. The condition determination unit 12 receives an input value for determining the X-ray generation condition and determines the X-ray generation condition.

まず、Ｘ線管球２の移動の手順を説明する
Ｘ線撮影は、Ｘ線管球２の位置と条件決定部１２が決定したＸ線発生条件（Ｘ線継続時間、管電圧、管電流）とに基づいて、撮影制御部８が高電圧発生部３、支持機構４、データ収集部６を制御することによって行われる。１回目のＸ線撮影はその後の２回目以降のＸ線発生条件（（ｂ）（ｃ））を決めるために行う。そのため、１回目のＸ線撮影を予備撮影又はプリ撮影と呼ぶものとし、その後の２回目以降のＸ線撮影を本撮影又はメイン撮影と呼ぶものとする。 First, the procedure for moving the X-ray tube 2 will be described. X-ray imaging is performed by determining the position of the X-ray tube 2 and the X-ray generation conditions determined by the condition determining unit 12 (X-ray duration, tube voltage, tube current). The imaging control unit 8 controls the high voltage generation unit 3, the support mechanism 4, and the data collection unit 6 based on the above. The first X-ray imaging is performed to determine the X-ray generation conditions ((b) (c)) for the second and subsequent times. Therefore, the first X-ray imaging is referred to as preliminary imaging or pre-imaging, and the second and subsequent X-ray imaging is referred to as main imaging or main imaging.

図３に示すように、撮影制御部８は所定の手順に従って支持機構４を制御し、Ｘ線管球２を適当な初期位置（Ｘ１）に移動させる。その移動した位置（Ｘ１）で１回目の撮影（予備撮影）を行う。２回目のＸ線撮影（１回目の本撮影）は、撮影制御部８の制御のもとで予備撮影と同じ位置（Ｘ１）で行われる。３回目のＸ線撮影（２回目の本撮影）は、撮影制御部８が支持機構４を制御し、Ｘ線管球２をＸ１からβ方向に関し一定間隔γで移動させる。その移動した位置（Ｘ２）で３回目のＸ線撮影（２回目の本撮影）が行われる。同様に４回目、５回目、…ｎ回目のＸ線撮影もＸ線管球２をβ方向に関し順次一定間隔γで移動させることにより行われる。Ｘ線発生時は、撮影制御部８は支持機構４を制御し、Ｘ線管球２を停止させる。   As shown in FIG. 3, the imaging control unit 8 controls the support mechanism 4 according to a predetermined procedure, and moves the X-ray tube 2 to an appropriate initial position (X1). The first shooting (preliminary shooting) is performed at the moved position (X1). The second X-ray imaging (first main imaging) is performed at the same position (X1) as the preliminary imaging under the control of the imaging control unit 8. In the third X-ray imaging (second main imaging), the imaging control unit 8 controls the support mechanism 4 to move the X-ray tube 2 from X1 in the β direction at a constant interval γ. A third X-ray imaging (second main imaging) is performed at the moved position (X2). Similarly, the fourth, fifth,..., N-th X-ray imaging is also performed by sequentially moving the X-ray tube 2 at a constant interval γ in the β direction. When X-rays are generated, the imaging control unit 8 controls the support mechanism 4 to stop the X-ray tube 2.

撮影制御部８は、条件決定部１２で決定された各Ｘ線発生条件に基づいたＸ線を発生するように高電圧発生部３を制御する。Ｘ線管球２で発生されたＸ線はＸ線検出部５の半導体検出素子に信号電荷を発生させる。撮影制御部８はデータ収集部６を制御し、Ｘ線検出部５にある半導体検出素子に発生した信号電荷をデジタル信号として読み出させる。   The imaging control unit 8 controls the high voltage generation unit 3 to generate X-rays based on the X-ray generation conditions determined by the condition determination unit 12. X-rays generated by the X-ray tube 2 generate signal charges in the semiconductor detection element of the X-ray detector 5. The imaging control unit 8 controls the data collection unit 6 to read out the signal charge generated in the semiconductor detection element in the X-ray detection unit 5 as a digital signal.

次に、Ｘ線発生条件の決定方法を説明する。   Next, a method for determining the X-ray generation condition will be described.

条件決定部１２は、予備又は本撮影各々のＸ線発生条件を決定する。予備撮影（１回目のＸ線撮影）のＸ線発生条件（ａ）は、操作者がフレーム２２によって取り付けられた下側圧迫板１７と上側圧迫板１８とで圧迫された被検体の***の***圧迫厚に基づいて決定される。一例として具体的な手順をあげると、まず、操作者が下側圧迫板１７と上側圧迫板１８とで被検体の***を圧迫する。次に、ロータリーエンコーダ等の位置センサの出力に基づいて下側圧迫板１７の上面と上側圧迫板１８の下面との間の距離（***圧迫厚）を測る。条件決定部１２には、***圧迫厚と予備撮影のＸ線発生条件（予備撮影のＸ線継続時間と管電流と管電圧）と予備撮影で得られた投影画像の画素値とＸ線撮影番号を示すコードとを入力とし、Ｘ線発生条件（Ｘ線継続時間、管電流、管電圧）を出力とする、入出力の対応関係を示すテーブルが記憶されている。Ｘ線発生条件（ａ）を決定する場合、条件決定部８は、***圧迫厚と予備撮影であることを示すコードとから、Ｘ線発生条件（ａ）を決定する。図４は各Ｘ線撮影で得られる投影画像の画素値とＸ線撮影番号、Ｘ線管球位置との関係を示す図であるが、図４に示すように、予備撮影のＸ線発生条件（ａ）は、被検体の***の内部構造がある程度認識できる程度でよく、例えば予備撮影によって得られる投影画像の画像中心の画素値（Ｉ１）が所望の画素値（Ｉｐ）の略１／２となるＸ線発生条件である。   The condition determination unit 12 determines the X-ray generation conditions for each of the preliminary and main imaging. The X-ray generation condition (a) of the preliminary imaging (first X-ray imaging) is that the operator presses the lower compression plate 17 and the upper compression plate 18 attached by the frame 22 and the breast of the subject's breast Determined based on compression thickness. As a specific example, first, the operator compresses the breast of the subject with the lower compression plate 17 and the upper compression plate 18. Next, the distance (breast compression thickness) between the upper surface of the lower compression plate 17 and the lower surface of the upper compression plate 18 is measured based on the output of a position sensor such as a rotary encoder. The condition determination unit 12 includes a breast compression thickness, preliminary imaging X-ray generation conditions (preliminary X-ray duration, tube current, and tube voltage), a pixel value of the projection image obtained by preliminary imaging, and an X-ray imaging number. A table indicating input / output correspondences is stored, in which an X-ray generation condition (X-ray duration, tube current, tube voltage) is output. When determining the X-ray generation condition (a), the condition determination unit 8 determines the X-ray generation condition (a) from the breast compression thickness and a code indicating preliminary imaging. FIG. 4 is a diagram showing the relationship between the pixel value of the projection image obtained by each X-ray imaging, the X-ray imaging number, and the X-ray tube position. As shown in FIG. (A) may be such that the internal structure of the subject's breast can be recognized to some extent. For example, the pixel value (I1) at the center of the projection image obtained by preliminary imaging is approximately ½ of the desired pixel value (Ip). This is the X-ray generation condition.

条件決定部１２は、予備撮影の結果に基づいて、１回目の本撮影（２回目のＸ線撮影）のＸ線発生条件（ｂ）と２回目以降の本撮影（３回目以降のＸ線撮影）の各撮影のＸ線発生条件（ｃ）とを決定する。   The condition determination unit 12 determines the X-ray generation condition (b) for the first main imaging (second X-ray imaging) and the second and subsequent main imaging (third and subsequent X-ray imaging) based on the result of the preliminary imaging. ) X-ray generation conditions (c) for each radiographing are determined.

２回目のＸ線発生条件（ｂ）を決める手順を示す。まず、予備撮影後、システム制御部７の制御のもと画像記憶部１０に記憶されている予備撮影で得た不鮮明な投影画像が表示部１５に表示される。次に、操作者が操作部９を介して投影画像上に関心領域（ＲＯＩ）を設定する。通常、関心領域は乳腺の位置に設定される。そして、条件決定部１２は、前記関心領域内の画素値の平均値（Ｉ１）と予備撮影のＸ線発生条件（ａ）と１回目の本撮影であることを示すコードとから、１回目の本撮影のＸ線発生条件（ｂ）を決定する。なお、画素値の平均値（Ｉ１）は画素値の中央値や最大値等であってもよい。１回目の本撮影のＸ線発生条件（ｂ）は、所望の画素値（Ｉｐ）と前記関心領域内の画素値（Ｉ１）との差が１回目の本撮影で得られるようなＸ線発生条件である。つまり、図４に示すように、予備撮影で得られた投影画像の画素値（Ｉ１）と１回目の本撮影で得られる投影画像の画素値（Ｉ２）との加算値が所望の画素値（Ｉｐ）に等価又は近似するように、１回目の本撮影のＸ線発生条件（ｂ）を決定する。   A procedure for determining the second X-ray generation condition (b) will be described. First, after preliminary shooting, a blurred projection image obtained by preliminary shooting stored in the image storage unit 10 under the control of the system control unit 7 is displayed on the display unit 15. Next, the operator sets a region of interest (ROI) on the projection image via the operation unit 9. Usually, the region of interest is set at the position of the mammary gland. Then, the condition determination unit 12 determines the first time from the average value (I1) of the pixel values in the region of interest, the X-ray generation condition (a) for preliminary imaging, and the code indicating the first main imaging. The X-ray generation condition (b) for main imaging is determined. The average value (I1) of the pixel values may be a median value or a maximum value of the pixel values. The X-ray generation condition (b) for the first actual imaging is such that the difference between the desired pixel value (Ip) and the pixel value (I1) in the region of interest is obtained by the first actual imaging. It is a condition. That is, as shown in FIG. 4, the sum of the pixel value (I1) of the projection image obtained by the preliminary photographing and the pixel value (I2) of the projection image obtained by the first actual photographing is a desired pixel value ( The X-ray generation condition (b) for the first main imaging is determined so as to be equivalent to or approximate to Ip).

２回目以降の本撮影のＸ線発生条件（ｃ）を決定する場合、条件決定部１２は、前記関心領域内の画素値（Ｉ１）と予備撮影のＸ線発生条件（ａ）と２回目以降の本撮影であることを示すコードとから、２回目以降の本撮影のＸ線発生条件（ｃ）を決定する。２回目以降の本撮影のＸ線発生条件（ｃ）は、前記関心領域において、所望の画素値（Ｉｐ）が１回のＸ線撮影で得られるようなＸ線発生条件である。つまり、図４に示すように、２回目以降の本撮影で得られる投影画像の画素値（Ｉ３）は所望の画素値（Ｉｐ）に等価又は近似するように、２回目以降の本撮影のＸ線発生条件（ｃ）を決定する。   When determining the X-ray generation condition (c) for the second and subsequent main imaging, the condition determination unit 12 determines the pixel value (I1) in the region of interest, the X-ray generation condition (a) for the preliminary imaging, and the second and subsequent times. The X-ray generation condition (c) for the second and subsequent main imaging is determined from the code indicating that the main imaging is performed. The X-ray generation condition (c) for the second and subsequent main imaging is an X-ray generation condition such that a desired pixel value (Ip) can be obtained by one X-ray imaging in the region of interest. That is, as shown in FIG. 4, the pixel values (I3) of the projection images obtained in the second and subsequent main shootings are equal to or approximate to the desired pixel values (Ip). The line generation condition (c) is determined.

次に、画像処理の手順について説明する。   Next, an image processing procedure will be described.

画像処理部１３は、予備撮影で得られた投影画像と１回目の本撮影で得られた投影画像とを合成し、一枚の投影画像を発生させる。この合成して得た投影画像は画像記憶部１０に記憶される。   The image processing unit 13 synthesizes the projection image obtained by the preliminary photographing and the projection image obtained by the first actual photographing to generate one projection image. The projected image obtained by the synthesis is stored in the image storage unit 10.

結像処理部１４は、画像処理部１１によって予備撮影で得られた投影画像の画素値（Ｉ１）と１回目の本撮影で得られた投影画像の画素値（Ｉ２）とを合成して得た投影画像と、２回目以降の本撮影によって得た複数の投影画像とを結像し、断層画像データを得る。この結像して得られた断層画像データは画像記憶部１０に記憶される。結像処理部１４によって得られた断層画像データは画像発生部１１によって表示部１５に表示される。   The imaging processing unit 14 synthesizes the pixel value (I1) of the projection image obtained by the preliminary photographing by the image processing unit 11 and the pixel value (I2) of the projection image obtained by the first actual photographing. The projected image and a plurality of projected images obtained by the second and subsequent main imaging are formed to obtain tomographic image data. The tomographic image data obtained by this image formation is stored in the image storage unit 10. The tomographic image data obtained by the imaging processing unit 14 is displayed on the display unit 15 by the image generation unit 11.

かくして第１の実施形態によれば、被検体の被曝線量の低減を実現するトモシンセシス撮影を行うことが可能となる。   Thus, according to the first embodiment, it is possible to perform tomosynthesis imaging that realizes a reduction in the exposure dose of the subject.

（第２の実施形態）
第２の実施形態に係わるマンモグラフィ装置の構成（図１）とＸ線撮影台の主要部の構成（図２）は第1の実施形態と同様なので説明は省略する。第１の実施形態と異なるのはＸ線管球２の移動の手順とＸ線発生条件の決定方法と画像処理の手順なので、以下その三点のみを説明する。 (Second Embodiment)
Since the configuration of the mammography apparatus according to the second embodiment (FIG. 1) and the configuration of the main part of the X-ray imaging table (FIG. 2) are the same as those of the first embodiment, description thereof is omitted. What is different from the first embodiment is the procedure for moving the X-ray tube 2, the method for determining the X-ray generation condition, and the procedure for image processing, and only the three points will be described below.

まず、Ｘ線管球２の移動の手順を説明する。   First, the procedure for moving the X-ray tube 2 will be described.

第２の実施形態においても第１の実施形態と同様に、１回目のＸ線撮影はその後に行われる２回目以降のＸ線撮影のＸ線発生条件（ｅ）を決めるために行う。そのため、１回目のＸ線撮影は予備撮影又はプリ撮影と呼ぶことにし、その後の２回目以降のＸ線撮影は本撮影又はメイン撮影と呼ぶことにする。   Also in the second embodiment, as in the first embodiment, the first X-ray imaging is performed to determine the X-ray generation condition (e) for the second and subsequent X-ray imaging performed thereafter. Therefore, the first X-ray imaging is referred to as preliminary imaging or pre-imaging, and the subsequent X-ray imaging after that is referred to as main imaging or main imaging.

図３に示すように、撮影制御部８は所定の手順に従って支持機構４を制御し、Ｘ線管球２を初期位置（Ｘ１）に移動させる。その移動した位置（Ｘ１）で１回目の撮影（予備撮影）を行う。２回目のＸ線撮影（１回目の本撮影）のために、撮影制御部８は支持機構４を制御し、Ｘ線管球２をＸ１からβ方向に関し一定間隔γで移動させる。その移動した位置（Ｘ２）で２回目の撮影（１回目の本撮影）が行われる。同様に３回目、４回目、…ｎ回目のＸ線撮影を、撮影制御部８は支持機構４を制御し、Ｘ線管球２をβ方向に関し順次一定間隔γで移動させて行う。Ｘ線発生時は、撮影制御部８は支持機構４を制御し、Ｘ線管球２を停止させる。   As shown in FIG. 3, the imaging control unit 8 controls the support mechanism 4 according to a predetermined procedure, and moves the X-ray tube 2 to the initial position (X1). The first shooting (preliminary shooting) is performed at the moved position (X1). For the second X-ray imaging (first main imaging), the imaging controller 8 controls the support mechanism 4 to move the X-ray tube 2 from the X1 in the β direction at a constant interval γ. The second shooting (first main shooting) is performed at the moved position (X2). Similarly, for the third, fourth,..., N-th X-ray imaging, the imaging control unit 8 controls the support mechanism 4 to sequentially move the X-ray tube 2 at a constant interval γ in the β direction. When X-rays are generated, the imaging control unit 8 controls the support mechanism 4 to stop the X-ray tube 2.

第２の実施形態における撮影制御部８の高電圧発生部３とデータ収集部６との制御の仕方は第１の実施形態と同様なので説明は省略する。   Since the method of controlling the high voltage generation unit 3 and the data collection unit 6 of the imaging control unit 8 in the second embodiment is the same as in the first embodiment, the description thereof is omitted.

次に、Ｘ線発生条件の決定方法を説明する。   Next, a method for determining the X-ray generation condition will be described.

図５は第２の実施形態における投影画像の画素値とＸ線撮影番号、Ｘ線管球位置との関係を示す図であり、図５に示すように、第２の実施形態における条件決定部１２は、二種類のＸ線発生条件を決定する。一つ目は予備撮影のＸ線発生条件（ｄ）で、二つ目が本撮影のＸ線発生条件（ｅ）である。第２の実施形態における予備撮影も第１の実施形態と同様に、その後に行われる２回目以降のＸ線撮影のＸ線発生条件を決めるために行う。そのため、予備撮影のＸ線発生条件（ｄ）は第１の実施形態のＸ線発生条件（ａ）と等しい。従って、予備撮影のＸ線発生条件（ｄ）の決定の手順は省略する。本撮影のＸ線発生条件（ｅ）は１回の撮影で所望の画素値（Ｉｐ）を得ることができるようなＸ線発生条件である。そのため、本撮影のＸ線発生条件（ｅ）は第１の実施形態のＸ線発生条件（ｃ）と同様である。従って、本撮影のＸ線発生条件（ｅ）の決定の手順も省略する。
次に、画像処理の手順について説明する。 FIG. 5 is a diagram showing the relationship between the pixel value of the projected image, the X-ray imaging number, and the X-ray tube position in the second embodiment. As shown in FIG. 5, the condition determining unit in the second embodiment 12 determines two types of X-ray generation conditions. The first is an X-ray generation condition (d) for preliminary imaging, and the second is an X-ray generation condition (e) for main imaging. Similarly to the first embodiment, the preliminary imaging in the second embodiment is also performed to determine the X-ray generation conditions for the second and subsequent X-ray imaging performed thereafter. Therefore, the preliminary imaging X-ray generation condition (d) is equal to the X-ray generation condition (a) of the first embodiment. Therefore, the procedure for determining the X-ray generation condition (d) for preliminary imaging is omitted. The X-ray generation condition (e) for the main imaging is an X-ray generation condition that enables a desired pixel value (Ip) to be obtained by one imaging. Therefore, the X-ray generation condition (e) of the main imaging is the same as the X-ray generation condition (c) of the first embodiment. Therefore, the procedure for determining the X-ray generation condition (e) for the main imaging is also omitted.
Next, an image processing procedure will be described.

画像処理部１３は、予備撮影を本撮影と同じ線量で撮影したように見せるため、予備撮影で得られた投影画像にゲインをかける。このゲイン処理を受けた投影画像は画像記憶部１０に記憶される。   The image processing unit 13 applies a gain to the projection image obtained by the preliminary photographing so that the preliminary photographing appears to be photographed at the same dose as the main photographing. The projected image that has undergone the gain processing is stored in the image storage unit 10.

結像処理部１４は、画像処理部１３によってゲイン処理をかけた投影画像と本撮影で得られた複数の投影画像とを結像し、断層画像データを得る。この結像して得られた断層画像データは画像記憶部１０に記憶される。結像処理部１４によって得られた断層画像は画像発生部１１によって表示部１５に表示される。   The image formation processing unit 14 forms an image of the projection image subjected to gain processing by the image processing unit 13 and a plurality of projection images obtained by the main imaging, and obtains tomographic image data. The tomographic image data obtained by this image formation is stored in the image storage unit 10. The tomographic image obtained by the imaging processing unit 14 is displayed on the display unit 15 by the image generation unit 11.

かくして第２の実施形態によれば、被検体の被曝線量の低減を実現するトモシンセシス撮影を行うことが可能となる。   Thus, according to the second embodiment, it is possible to perform tomosynthesis imaging that realizes a reduction in the exposure dose of the subject.

なお、本発明は上記実施形態そのままに限定されるものではなく、実施段階ではその要旨を逸脱しない範囲で構成要素を変形して具体化できる。また、上記実施形態に開示されている複数の構成要素の適宜な組み合わせにより、種々の発明を形成できる。例えば、実施形態に示される全構成要素から幾つかの構成要素を削除してもよい。さらに、異なる実施形態にわたる構成要素を適宜組み合わせてもよい。   Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

本発明の実施形態に係わるマンモグラフィ装置の構成を示す図。The figure which shows the structure of the mammography apparatus concerning embodiment of this invention. 図１のマンモグラフィ装置のＸ線撮影台の主要部構造を示す斜視図。The perspective view which shows the principal part structure of the X-ray imaging stand of the mammography apparatus of FIG. 本実施形態において、トモシンセシス撮影時のＸ線管球の動きを示す図。The figure which shows the motion of the X-ray tube at the time of tomosynthesis imaging | photography in this embodiment. 第１の実施形態における投影画像の画素値とＸ線撮影番号、Ｘ線管球位置との関係を示す図。The figure which shows the relationship between the pixel value of the projection image in 1st Embodiment, an X-ray imaging number, and an X-ray tube position. 第２の実施形態における投影画像の画素値とＸ線撮影番号、Ｘ線管球位置との関係を示す図。The figure which shows the relationship between the pixel value of a projection image in 2nd Embodiment, an X-ray imaging number, and an X-ray tube position.

符号の説明Explanation of symbols

１…Ｘ線撮影台、２…Ｘ線管球、３…高電圧発生部、４…支持機構、５…Ｘ線検出部、６…データ収集部、７…システム制御部、８…撮影制御部、９…操作部、１０…画像記憶部、１１…画像発生部、１２…条件決定部、１３…画像処理部、１４…結像処理部、１５…表示部。   DESCRIPTION OF SYMBOLS 1 ... X-ray imaging stand, 2 ... X-ray tube, 3 ... High voltage generation part, 4 ... Support mechanism, 5 ... X-ray detection part, 6 ... Data collection part, 7 ... System control part, 8 ... Imaging control part DESCRIPTION OF SYMBOLS 9 ... Operation part 10 ... Image memory | storage part 11 ... Image generation part 12 ... Condition determination part 13 ... Image processing part 14 ... Imaging process part 15 ... Display part.

Claims (11)

Ｘ線を発生するＸ線管球と、
前記Ｘ線管球に印加するための高電圧を発生する高電圧発生部と、
被検体の***を透過した透過Ｘ線を検出するＸ線検出部と、
前記Ｘ線管球と前記Ｘ線検出部とを移動可能に支持する支持機構と、
前記高電圧発生部と前記Ｘ線検出部と前記支持機構とを制御してＸ線撮影を繰り返す撮影制御部と、
前記繰り返されるＸ線撮影のうち１回目のＸ線撮影のＸ線発生条件を前記被検体の圧迫された***の***圧迫厚に基づいて決定するとともに、前記１回目のＸ線撮影による前記Ｘ線検出部の出力に基づいて２回目のＸ線撮影におけるＸ線発生条件を決定し、前記１回目のＸ線撮影による前記Ｘ線検出部の出力に基づいて前記２回目のＸ線撮影のＸ線発生条件とは相違する３回目以降の各Ｘ線撮影におけるＸ線発生条件を決定する条件決定部と、
前記繰り返されるＸ線撮影により収集される前記Ｘ線検出部の出力に基づいて前記被検体の***に関する断層画像データを発生する画像発生部とを具備するマンモグラフィ装置。 An X-ray tube that generates X-rays;
A high voltage generator for generating a high voltage to be applied to the X-ray tube;
An X-ray detector that detects transmitted X-rays transmitted through the breast of the subject;
A support mechanism for movably supporting the X-ray tube and the X-ray detector;
An imaging control unit that repeats X-ray imaging by controlling the high voltage generation unit, the X-ray detection unit, and the support mechanism;
The X-ray generation conditions of the first X-ray imaging among the repeated X-ray imaging are determined based on the breast compression thickness of the compressed breast of the subject, and the X-rays by the first X-ray imaging X-ray generation conditions in the second X-ray imaging are determined based on the output of the detection unit, and X-rays in the second X-ray imaging are determined based on the output of the X-ray detection unit in the first X-ray imaging. A condition determining unit for determining an X-ray generation condition in each X-ray imaging after the third time, which is different from the generation condition;
A mammography apparatus comprising: an image generation unit that generates tomographic image data relating to the breast of the subject based on an output of the X-ray detection unit collected by the repeated X-ray imaging. 前記条件決定部は、
前記１回目のＸ線撮影による投影画像上の関心領域内の画素値と所望の画素値とに基づいて前記３回目以降のＸ線発生条件を決定することを特徴とする請求項１記載のマンモグラフィ装置。 The condition determining unit
The mammography according to claim 1, wherein the third and subsequent X-ray generation conditions are determined based on a pixel value in a region of interest on a projection image obtained by the first X-ray imaging and a desired pixel value. Equipment . 前記条件決定部は、
前記３回目以降のＸ線撮影による投影画像の画素値が前記所望の画素値と等価又は近似するように、前記１回目のＸ線撮影による投影画像上の前記関心領域内の画素値に基づいて、前記３回目以降のＸ線発生条件を決定することを特徴とする請求項２記載のマンモグラフィ装置。 The condition determining unit
Based on the pixel value in the region of interest on the projection image obtained by the first X-ray photography so that the pixel value of the projection image obtained by the third and subsequent X-ray photography is equivalent or approximate to the desired pixel value. The mammography apparatus according to claim 2, wherein the third and subsequent X-ray generation conditions are determined. 前記条件決定部は、
前記所望の評価値と前記１回目のＸ線撮影による投影画像上の前記関心領域内の画素値との差に基づいて前記２回目のＸ線発生条件を決定することを特徴とする請求項１記載のマンモグラフィ装置。 The condition determining unit
The second X-ray generation condition is determined based on a difference between the desired evaluation value and a pixel value in the region of interest on a projection image obtained by the first X-ray imaging. The described mammography device . 前記条件決定部は、
前記１回目のＸ線撮影による投影画像上の前記関心領域内の画素値と前記２回目のＸ線撮影による投影画像の画素値との加算値が、前記所望の画素値と等価又は近似するように、前記１回目のＸ線撮影による投影画像上の前記関心領域内の画素値に基づいて、前記２回目のＸ線発生条件を決定することを特徴とする請求項４記載のマンモグラフィ装置。 The condition determining unit
An added value of the pixel value in the region of interest on the projection image obtained by the first X-ray photography and the pixel value of the projection image obtained by the second X-ray photography is equivalent to or approximate to the desired pixel value. The mammography apparatus according to claim 4, wherein the second X-ray generation condition is determined based on a pixel value in the region of interest on a projection image obtained by the first X-ray imaging. 前記撮影制御部は、
前記１回目のＸ線撮影と前記２回目のＸ線撮影とを同位置で行い、前記３回目以降のＸ線撮影は順次位置を変えて行うように支持機構を制御することを特徴とする請求項１記載のマンモグラフィ装置。 The photographing control unit
The support mechanism is controlled so that the first X-ray imaging and the second X-ray imaging are performed at the same position, and the third and subsequent X-ray imaging are sequentially performed at different positions. Item 2. A mammography apparatus according to Item 1. 前記マンモグラフィ装置は、
前記１回目のＸ線撮影で得られた投影画像の画素値と前記２回目のＸ線撮影で得られた投影画像の画素値とを加算する画像処理部と、
前記加算して得られた投影画像と前記３回目以降のＸ線撮影で得られた複数の投影画像とに基づいて前記被検体の***に関する断層画像データを発生する結像処理部と画像発生部とを具備することを特徴とする請求項１記載のマンモグラフィ装置。 The mammography device
An image processing unit for adding the pixel value of the projection image obtained by the first X-ray imaging and the pixel value of the projection image obtained by the second X-ray imaging;
An imaging processing unit and an image generation unit for generating tomographic image data relating to the breast of the subject based on the projection image obtained by the addition and a plurality of projection images obtained by the third and subsequent X-ray imaging The mammography apparatus according to claim 1, further comprising: Ｘ線を発生するＸ線管球と、
前記Ｘ線管球に印加するための高電圧を発生する高電圧発生部と、
被検体の***を透過した透過Ｘ線を検出するＸ線検出部と、
前記Ｘ線管球と前記Ｘ線検出部とを移動可能に支持する支持機構と、
前記高電圧発生部と前記Ｘ線検出部と前記支持機構とを制御してＸ線撮影を繰り返す撮影制御部と、
前記繰り返されるＸ線撮影のうち１回目のＸ線撮影のＸ線発生条件を前記被検体の圧迫された***の***圧迫厚に基づいて決定するとともに、前記１回目のＸ線撮影による前記Ｘ線検出部の出力に基づいて２回目以降の各Ｘ線撮影におけるＸ線発生条件を決定する条件決定部と、
前記１回目と前記２回目以降の各Ｘ線撮影による前記Ｘ線検出部の出力に応じたゲインで前記１回目のＸ線撮影により生じた投影画像にゲイン処理をする前記画像処理部と、
前記２回目以降のＸ線撮影により収集される複数の投影画像と前記ゲイン処理を受けた１回目の投影画像とに基づいて、前記被検体の***に関する断層画像データを発生する結像処理部と画像発生部とを具備するマンモグラフィ装置。 An X-ray tube that generates X-rays;
A high voltage generator for generating a high voltage to be applied to the X-ray tube;
An X-ray detector that detects transmitted X-rays transmitted through the breast of the subject;
A support mechanism for movably supporting the X-ray tube and the X-ray detector;
An imaging control unit that repeats X-ray imaging by controlling the high voltage generation unit, the X-ray detection unit, and the support mechanism;
The X-ray generation conditions of the first X-ray imaging among the repeated X-ray imaging are determined based on the breast compression thickness of the compressed breast of the subject, and the X-rays by the first X-ray imaging A condition determining unit that determines an X-ray generation condition in each X-ray imaging after the second time based on the output of the detecting unit;
Said image processing unit to the gain processing to the projection image generated by the first X-ray imaging with a gain corresponding to the output of said X-ray detector according to the X-ray imaging of the first and the second and subsequent,
An imaging processing unit for generating tomographic image data relating to the breast of the subject based on the plurality of projection images collected by the second and subsequent X-ray imaging and the first projection image subjected to the gain processing; A mammography apparatus comprising an image generation unit. 前記条件決定部は、
前記１回目のＸ線撮影による投影画像上の前記関心領域内の画素値と所望の画素値とに基づいて前記２回目以降のＸ線発生条件を決定することを特徴とする請求項８記載のマンモグラフィ装置。 The condition determining unit
9. The second and subsequent X-ray generation conditions are determined based on a pixel value in the region of interest on a projection image obtained by the first X-ray imaging and a desired pixel value. Mammography device . 前記条件決定部は、
前記２回目以降のＸ線撮影による投影画像の画素値が前記所望の画素値と等価又は近似するように、前記１回目のＸ線撮影による投影画像上の前記関心領域内の画素値に基づいて、前記２回目以降のＸ線発生条件を決定することを特徴とする請求項９記載のマンモグラフィ装置。 The condition determining unit
Based on the pixel value in the region of interest on the projection image obtained by the first X-ray photography so that the pixel value of the projection image obtained by the second and subsequent X-ray photography is equivalent to or approximate to the desired pixel value. The mammography apparatus according to claim 9, wherein the second and subsequent X-ray generation conditions are determined. 前記撮影制御部は、
前記１回目のＸ線撮影及び、前記２回目以降のＸ線撮影を順次位置を変えて行うように支持機構を制御することを特徴とする請求項８記載のマンモグラフィ装置。 The photographing control unit
9. The mammography apparatus according to claim 8, wherein the support mechanism is controlled so that the first X-ray imaging and the second and subsequent X-ray imaging are sequentially performed at different positions.
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