JP2002306483A - Medical diagnosis image processing equipment and method thereof - Google Patents
Medical diagnosis image processing equipment and method thereofInfo
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- JP2002306483A JP2002306483A JP2001120183A JP2001120183A JP2002306483A JP 2002306483 A JP2002306483 A JP 2002306483A JP 2001120183 A JP2001120183 A JP 2001120183A JP 2001120183 A JP2001120183 A JP 2001120183A JP 2002306483 A JP2002306483 A JP 2002306483A
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- 238000000034 method Methods 0.000 title claims description 20
- 238000003745 diagnosis Methods 0.000 title claims description 3
- 210000000056 organ Anatomy 0.000 claims abstract description 99
- 230000033001 locomotion Effects 0.000 claims abstract description 63
- 238000006073 displacement reaction Methods 0.000 claims abstract description 31
- 238000004364 calculation method Methods 0.000 claims abstract description 10
- 230000002123 temporal effect Effects 0.000 claims description 26
- 230000003287 optical effect Effects 0.000 claims description 25
- 230000006870 function Effects 0.000 claims description 8
- 238000002059 diagnostic imaging Methods 0.000 claims 1
- 238000002405 diagnostic procedure Methods 0.000 claims 1
- 238000000605 extraction Methods 0.000 abstract description 10
- 238000010586 diagram Methods 0.000 description 6
- 239000000284 extract Substances 0.000 description 2
- 239000003550 marker Substances 0.000 description 2
- 102100033041 Carbonic anhydrase 13 Human genes 0.000 description 1
- 101000867860 Homo sapiens Carbonic anhydrase 13 Proteins 0.000 description 1
- 101100280298 Homo sapiens FAM162A gene Proteins 0.000 description 1
- 101100402621 Homo sapiens MSANTD4 gene Proteins 0.000 description 1
- 102100031642 Myb/SANT-like DNA-binding domain-containing protein 4 Human genes 0.000 description 1
- 102100023788 Protein FAM162A Human genes 0.000 description 1
- 238000004590 computer program Methods 0.000 description 1
- 230000008602 contraction Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 210000005240 left ventricle Anatomy 0.000 description 1
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- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、超音波診断装置、
ＭＲＩ、Ｘ線ＣＴ等で撮られた画像データから、臓器の
運動状態を解析する医用画像診断装置及びその方法に関
する。TECHNICAL FIELD The present invention relates to an ultrasonic diagnostic apparatus,
The present invention relates to a medical image diagnostic apparatus and method for analyzing the motion state of an organ from image data taken by MRI, X-ray CT, or the like.
【０００２】[0002]
【従来の技術】従来、１つの断面画像から臓器輪郭を抽
出し、２次元的な臓器運動を解析する手段が考案されて
いるが、少数の複数断面画像から簡便に臓器輪郭を抽出
し、３次元的な臓器運動を解析する手段はない。2. Description of the Related Art Conventionally, means for extracting an organ contour from one cross-sectional image and analyzing two-dimensional organ motion has been devised. There is no means to analyze dimensional organ movements.
【０００３】また、従来、３次元データを基に輪郭抽出
する手段や、ＭＲ画像に対し磁気標識を付加し臓器運動
を解析する手法が考案されているが、磁気標識等を用い
ず画像データのみから臓器局所部分の実際の運動を反映
した臓器運動を抽出、表示、解析する手段はない。Conventionally, a means for extracting contours based on three-dimensional data and a method for adding a magnetic marker to an MR image to analyze organ motion have been devised. However, only image data is used without using a magnetic marker or the like. There is no means for extracting, displaying, and analyzing organ movements that reflect the actual movements of the local organs from the organs.
【０００４】[0004]
【発明が解決しようとする課題】そこで、本発明は、臓
器の３次元的輪郭を生成し、臓器運動の解析を可能に
し、また、臓器局所部分の実際の運動を反映した臓器運
動を抽出、表示、解析することを可能にすることを目的
とする。SUMMARY OF THE INVENTION Accordingly, the present invention provides a three-dimensional contour of an organ, enables analysis of organ motion, and extracts an organ motion that reflects the actual motion of a local organ. The purpose is to enable display and analysis.
【０００５】さらに、少数の複数断面から簡便に３次元
的な臓器輪郭を生成し、臓器運動の解析を可能にするこ
とを目的とする。It is another object of the present invention to easily generate a three-dimensional organ contour from a small number of cross sections and to enable analysis of organ motion.
【０００６】[0006]
【課題を解決するための手段】請求項１の発明は、生体
器官である臓器を撮影した複数時相の画像から前記臓器
に関する複数時相の３次元輪郭を算出する輪郭算出手段
と、算出した前記臓器に関する複数時相の３次元輪郭に
基づいて、前記臓器の３次元輪郭上の各点の時間的変位
量を算出する変位量算出手段と、算出した前記各点の時
間的変位量から前記臓器の輪郭の運動情報を算出する運
動算出手段と、を有することを特徴とする医用画像診断
装置である。According to the first aspect of the present invention, there is provided a contour calculating means for calculating a three-dimensional contour of a plurality of time phases related to an organ from an image of a plurality of time phases obtained by photographing an organ which is a living organ. A displacement amount calculating unit configured to calculate a temporal displacement amount of each point on the three-dimensional contour of the organ based on a three-dimensional contour of a plurality of time phases related to the organ; And a motion calculating unit that calculates motion information of the contour of the organ.
【０００７】請求項２の発明は、前記輪郭算出手段は、
前記臓器の複数断面が撮影された複数時相の２次元画像
に基づいて、前記各断面における前記臓器の輪郭を抽出
する輪郭抽出手段と、抽出された複数時相の前記各断面
における前記臓器における輪郭に基づいて、前記臓器に
関する複数時相の３次元輪郭を生成する輪郭生成手段
と、を有することを特徴とする請求項１記載の医用画像
診断装置である。According to a second aspect of the present invention, the contour calculating means includes:
Contour extraction means for extracting a contour of the organ in each section based on a two-dimensional image of a plurality of phases in which a plurality of sections of the organ are captured; 2. The medical image diagnostic apparatus according to claim 1, further comprising: a contour generating unit configured to generate a three-dimensional contour having a plurality of phases with respect to the organ based on the contour.
【０００８】請求項３の発明は、前記輪郭算出手段は、
前記臓器が撮影された複数時相の３次元画像に基づい
て、前記臓器に関する複数時相の３次元輪郭を算出する
ことを特徴とする請求項１記載の医用画像診断装置であ
る。According to a third aspect of the present invention, the contour calculating means includes:
The medical image diagnostic apparatus according to claim 1, wherein a three-dimensional contour of a plurality of phases with respect to the organ is calculated based on a three-dimensional image of the plurality of phases with which the organ is captured.
【０００９】請求項４の発明は、前記臓器の３次元輪郭
上の各点の時間的変位量が、前記３次元輪郭を構成する
頂点の時間的な移動ベクトルであることを特徴とする請
求項１記載の医用画像診断装置である。According to a fourth aspect of the present invention, the temporal displacement of each point on the three-dimensional contour of the organ is a temporal movement vector of a vertex constituting the three-dimensional contour. 1 is a medical image diagnostic apparatus.
【００１０】請求項５の発明は、前記臓器の３次元輪郭
上の各点の時間的変位量が、前記３次元輪郭を構成する
頂点近辺の画像データに基づき計算されるオプティカル
フローベクトルであることを特徴とする請求項１記載の
医用画像診断装置である。According to a fifth aspect of the present invention, the temporal displacement of each point on the three-dimensional contour of the organ is an optical flow vector calculated based on image data near a vertex constituting the three-dimensional contour. 2. The medical image diagnostic apparatus according to claim 1, wherein:
【００１１】請求項６の発明は、前記算出された前記臓
器の３次元輪郭上の各点の時間的変位量に基づき、時間
的に変位する頂点によって表現された前記臓器の３次元
輪郭を表示する表示手段を有したことを特徴とする請求
項１記載の医用画像診断装置である。According to a sixth aspect of the present invention, a three-dimensional contour of the organ represented by temporally displaced vertices is displayed based on the calculated temporal displacement of each point on the three-dimensional contour of the organ. The medical image diagnostic apparatus according to claim 1, further comprising a display unit that performs the operation.
【００１２】請求項７の発明は、生体器官である臓器を
撮影した複数時相の画像から前記臓器に関する複数時相
の３次元輪郭を算出する輪郭算出ステップと、算出した
前記臓器に関する複数時相の３次元輪郭に基づいて、前
記臓器の３次元輪郭上の各点の時間的変位量を算出する
変位量算出ステップと、算出した前記各点の時間的変位
量から前記臓器の輪郭の運動情報を算出する運動算出ス
テップと、を有することを特徴とする医用画像診断方法
である。The invention according to claim 7 is a contour calculating step of calculating a three-dimensional contour of a plurality of time phases related to the organ from an image of a plurality of time phases obtained by photographing an organ as a living body organ, and a plurality of time phases related to the calculated organ. A displacement amount calculating step of calculating a temporal displacement amount of each point on the three-dimensional contour of the organ based on the three-dimensional contour of the organ; and a motion information of the contour of the organ from the calculated temporal displacement amount of each point. And a motion calculating step of calculating a motion image.
【００１３】請求項８の発明は、生体器官である臓器を
撮影した複数時相の画像から前記臓器に関する複数時相
の３次元輪郭を算出する輪郭算出機能と、算出した前記
臓器に関する複数時相の３次元輪郭に基づいて、前記臓
器の３次元輪郭上の各点の時間的変位量を算出する変位
量算出機能と、算出した前記各点の時間的変位量から前
記臓器の輪郭の運動情報を算出する運動算出機能と、を
コンピュータによって実現することを特徴とする医用画
像診断方法のプログラムである。The invention according to claim 8 is a contour calculating function for calculating a three-dimensional contour of a plurality of time phases related to the organ from an image of a plurality of time phases obtained by photographing an organ as a living body organ, and a plurality of time phases related to the calculated organ. A displacement amount calculating function of calculating a temporal displacement amount of each point on the three-dimensional contour of the organ based on the three-dimensional contour of the organ; and motion information of the contour of the organ from the calculated temporal displacement amount of each point. And a motion calculation function for calculating a computer program.
【００１４】本発明によれば、臓器の３次元的輪郭を生
成し、臓器運動の解析が可能となる。According to the present invention, it is possible to generate a three-dimensional contour of an organ and analyze organ motion.
【００１５】また、臓器局所部分の実際の運動を反映し
た臓器運動を抽出、表示、解析することが可能となる。Further, it is possible to extract, display, and analyze an organ motion reflecting the actual motion of the local organ part.
【００１６】[0016]
【発明の実施の形態】＜第１実施例＞以下、本発明の第
１実施例について、図１から図１１を参照して説明す
る。DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS <First Embodiment> A first embodiment of the present invention will be described below with reference to FIGS.
【００１７】図１は第１実施例の医用画像診断装置１０
のブロック図であり、図２はその動作及び操作の流れを
示すフローチャートである。FIG. 1 shows a medical image diagnostic apparatus 10 according to a first embodiment.
FIG. 2 is a flowchart showing the flow of the operation and operation.
【００１８】第１実施例は、複数の断面画像から臓器輪
郭を自動的に抽出し、３次元輪郭を補間生成し、その輪
郭の運動情報の時間的変化を表示する例である。The first embodiment is an example in which an organ contour is automatically extracted from a plurality of cross-sectional images, a three-dimensional contour is generated by interpolation, and a temporal change in motion information of the contour is displayed.
【００１９】図１に示すように、コンピュータによって
構成される医用画像診断装置１０は、画像データを入力
する画像入力部１２と、入力された画像データを記憶す
るメモリ１４と、画像上の臓器輪郭を抽出する輪郭抽出
部１６と、抽出された複数輪郭を基に３次元輪郭を生成
する３次元輪郭生成部１８と、３次元輪郭の変形から運
動情報を算出する運動情報算出部２０と、算出された運
動情報を表示する表示部２２とで構成される。なお、下
記で説明する各機能はプログラムによって実現される。As shown in FIG. 1, a medical image diagnostic apparatus 10 constituted by a computer includes an image input unit 12 for inputting image data, a memory 14 for storing the input image data, an organ contour on the image. , A three-dimensional contour generating part 18 for generating a three-dimensional contour based on the plurality of extracted contours, a motion information calculating part 20 for calculating motion information from deformation of the three-dimensional contour, And a display unit 22 for displaying the obtained exercise information. Each function described below is realized by a program.
【００２０】以下、図２の処理の流れに沿って説明す
る。Hereinafter, description will be given along the processing flow of FIG.
【００２１】まず、例えば超音波診断装置、ＭＲＩ、Ｘ
線ＣＴ装置等で得られる複数断面画像データが画像入力
部１２を介して入力され、メモリ１４に記憶される（ス
テップＳ１）。First, for example, an ultrasonic diagnostic apparatus, MRI, X
Plural cross-sectional image data obtained by a line CT apparatus or the like is input via the image input unit 12 and stored in the memory 14 (step S1).
【００２２】この入力データは、ディジタル化された輝
度値データでも良いし、アナログ信号による画像でも良
い。アナログ信号の場合は、Ａ／Ｄ変換器によりディジ
タル化され入力される。The input data may be digitized luminance value data or an image based on an analog signal. In the case of an analog signal, it is digitized by an A / D converter and input.
【００２３】また、入力データは輝度値データのみに限
らず、例えば超音波診断装置におけるエコーの生信号デ
ータやドップラ速度データや、Ｘ線ＣＴ装置での生のＣ
Ｔ値データ等であっても良い。The input data is not limited to the brightness value data. For example, raw echo signal data and Doppler velocity data in an ultrasonic diagnostic apparatus, and raw C data in an X-ray CT apparatus are used.
It may be T value data or the like.
【００２４】さらに、複数断面画像は３次元データから
生成されたものであっても良い。Further, the plurality of cross-sectional images may be generated from three-dimensional data.
【００２５】次に、輪郭抽出部１６において半自動的に
臓器輪郭が抽出され、輪郭情報がメモリ１４に記憶され
る（ステップＳ２）。Next, the contour extracting section 16 semi-automatically extracts the organ contour, and stores the contour information in the memory 14 (step S2).
【００２６】輪郭抽出は、例えば手動で設定された初期
輪郭を基に画像輝度値のエッジ探索を行う動的輪郭モデ
ルを用いた手法や、画像輝度値の閾値処理による領域抽
出後に輪郭を検出するような手法を用いると良い。The contour extraction is performed by, for example, a method using a dynamic contour model for performing an edge search of an image luminance value based on a manually set initial contour, or detecting the contour after extracting an area by threshold processing of the image luminance value. It is good to use such a technique.
【００２７】また、輪郭を手動でトレースしても良い。The contour may be traced manually.
【００２８】この輪郭抽出処理は、複数の断面画像に対
して行われる。輪郭は、例えば図３に示すように複数の
頂点により表現され、それらの複数頂点の座標値が輪郭
情報としてメモリ１４に記憶される。This contour extraction processing is performed on a plurality of cross-sectional images. The contour is represented by a plurality of vertices as shown in FIG. 3, for example, and the coordinate values of the vertices are stored in the memory 14 as contour information.
【００２９】次に、３次元輪郭生成部１８が複数の輪郭
情報を基に、３次元輪郭を生成し、３次元輪郭情報をメ
モリ１４に記憶する（ステップＳ３）。Next, the three-dimensional contour generator 18 generates a three-dimensional contour based on the plurality of pieces of contour information, and stores the three-dimensional contour information in the memory 14 (step S3).
【００３０】３次元輪郭の生成は例えば次の処理により
行われる。The generation of a three-dimensional contour is performed, for example, by the following processing.
【００３１】まず、入力された複数断面の位置関係によ
り、ステップＳ２でメモリ１４に記憶された輪郭座標を
３次元座標に変換する。First, the contour coordinates stored in the memory 14 are converted into three-dimensional coordinates in step S2 according to the input positional relationship of the plurality of cross sections.
【００３２】次に、複数輪郭間の輪郭情報を補間処理し
３次元輪郭全体を生成する。Next, the contour information between a plurality of contours is interpolated to generate an entire three-dimensional contour.
【００３３】複数断面が１つの軸の周りに回転する場合
について、具体的計算例を以下に示す。A specific calculation example in the case where a plurality of cross sections rotate around one axis is shown below.
【００３４】ステップＳ２で記憶された輪郭の頂点座標
を（ｘｉ，ｙｉ）と表す。ここで、複数断面で共通の回
転軸がｙ軸と等しくなるように座標軸を設定する（図９
参照）。断面１を基準とし、ｎ番目の断面の３次元空間
内での角度をθｎとすると、次式により、各断面内の２
次元輪郭頂点座標（ｘｉ，ｙｉ）は、３次元空間内の座
標（ｘ’ｉ，ｙ’ｉ，ｚ’ｉ）に変換される。The vertex coordinates of the contour stored in step S2 are represented as (x i , y i ). Here, coordinate axes are set such that a common rotation axis is equal to the y-axis in a plurality of cross sections (FIG. 9).
reference). Assuming that the angle of the n-th cross section in the three-dimensional space with respect to the cross section 1 is θ n , 2
The dimensional contour vertex coordinates (x i , y i ) are converted to coordinates (x ′ i , y ′ i , z ′ i ) in the three-dimensional space.
【００３５】[0035]
【数１】 次に、複数断面の間の仮想的な断面での輪郭頂点座標を
補間生成し３次元輪郭を生成する。図１０は、断面ｎと
断面ｎ＋１間の頂点の３次元的な補間生成を示したもの
である。(Equation 1) Next, three-dimensional contours are generated by interpolating and generating contour vertex coordinates in a virtual cross section among a plurality of cross sections. FIG. 10 shows three-dimensional interpolation generation of a vertex between the cross section n and the cross section n + 1.
【００３６】図４は、断面画像から輪郭抽出を経て３次
元輪郭が生成されるまでの処理を、心室を例にして模式
的に示したものである。FIG. 4 schematically shows the processing from the cross-sectional image through contour extraction to generation of a three-dimensional contour, taking a ventricle as an example.
【００３７】また、図５は、管状の臓器の３次元輪郭を
模式的に例示したものである。３次元輪郭は、複数頂点
の３次元座標で表現され、各点の３次元座標が３次元輪
郭情報としてメモリ１４に記憶される。FIG. 5 schematically shows a three-dimensional contour of a tubular organ. The three-dimensional contour is represented by three-dimensional coordinates of a plurality of vertices, and the three-dimensional coordinates of each point are stored in the memory 14 as three-dimensional contour information.
【００３８】次に、運動情報算出部２０がステップＳ３
でメモリ１４に記憶された３次元輪郭情報から、臓器輪
郭の各局所部分の運動情報を算出し、メモリ１４に記憶
する（ステップＳ４）。Next, the exercise information calculating section 20 executes step S3.
Then, the motion information of each local portion of the organ contour is calculated from the three-dimensional contour information stored in the memory 14 and stored in the memory 14 (step S4).
【００３９】「運動情報」とは、移動距離や移動速度等
である。移動距離の算出は、例えば３次元輪郭の対応す
る頂点番号の頂点間の時間的移動距離によって算出す
る。"Motion information" refers to a moving distance, a moving speed, and the like. The moving distance is calculated, for example, based on the temporal moving distance between the vertices of the corresponding vertex numbers of the three-dimensional contour.
【００４０】移動距離の他の算出方法として、３次元輪
郭面の法線方向の移動距離により算出する方法や、臓器
の運動モデルに基づき算出する方法を用いても良い。As another method of calculating the moving distance, a method of calculating based on a moving distance in a normal direction of the three-dimensional contour surface or a method of calculating based on a motion model of an organ may be used.
【００４１】本実施例は、運動情報の算出方法には制限
されない。また、運動情報として、移動距離や移動速度
以外の数値を算出しても良い。The present embodiment is not limited to the method for calculating exercise information. Further, a numerical value other than the moving distance and the moving speed may be calculated as the exercise information.
【００４２】最後に、算出された運動情報を表示部２２
で表示する（ステップＳ５）。Finally, the calculated exercise information is displayed on the display unit 22.
Is displayed (step S5).
【００４３】この運動情報の表示は、３次元輪郭上に色
の違いや数値等で表示しても良いし（図６参照）、例え
ばブルズアイマップのように模式的に示しても良い（図
７参照）。また、部位毎の運動情報の時間的変化を心電
図等と共にグラフ化しても良い（図８参照）。The motion information may be displayed on a three-dimensional contour by color differences, numerical values, or the like (see FIG. 6), or may be schematically shown, for example, as a bullseye map (FIG. 7). reference). Further, a temporal change of the exercise information for each part may be graphed together with an electrocardiogram or the like (see FIG. 8).
【００４４】以上の処理内容を行う場合の、ユーザの操
作手順について図１１に基づいて以下に説明する。The operation procedure of the user when performing the above processing contents will be described below with reference to FIG.
【００４５】ユーザは、まず１つの断面動画像または複
数時相の画像を入力する（ステップＳ１１）。First, the user inputs one section moving image or images of a plurality of time phases (step S11).
【００４６】次に、輪郭抽出処理を行う（ステップＳ１
２）。輪郭抽出処理を自動で行う場合は、ユーザは自動
輪郭抽出のための初期位置の指定のみ行えば良い。Next, a contour extraction process is performed (step S1).
2). When performing the contour extraction processing automatically, the user need only specify the initial position for automatic contour extraction.
【００４７】次に、各断面動画像において３次元輪郭生
成に用いる動画区間または複数時相を選択する（ステッ
プＳ１３）。ここで、時相とは、時系列で入力された動
画像の各画像における時間をいう。Next, a moving image section or a plurality of time phases to be used for generating a three-dimensional contour in each section moving image is selected (step S13). Here, the time phase refers to a time in each image of a moving image input in time series.
【００４８】ステップＳ１３は、例えば心臓の拡張末期
から収縮末期までの区間の３次元輪郭を生成したいとい
った場合に、各断面動画像においてはフレーム番号と心
臓の拡張収縮の時相との関係がばらばらであるため、使
用する動画区間を指定するものである。In step S13, for example, when it is desired to generate a three-dimensional contour in a section from the end-diastole to the end-systole of the heart, the relationship between the frame number and the time phase of the diastole and contraction of the heart varies in each cross-sectional moving image. Therefore, the moving image section to be used is specified.
【００４９】ステップＳ１１からステップＳ１３までを
断面数分だけ繰り返す。Steps S11 to S13 are repeated for the number of sections.
【００５０】最後に、ユーザは表示実行を指示すると
（ステップＳ１４）、３次元輪郭生成、運動情報算出が
自動的に行われ、結果が表示部２２に表示される。Finally, when the user instructs display execution (step S14), three-dimensional contour generation and motion information calculation are automatically performed, and the results are displayed on the display unit 22.
【００５１】以上のように、本実施例によれば簡便な操
作で３次元的な輪郭及びその運動情報を定量的に得るこ
とができる。As described above, according to this embodiment, a three-dimensional contour and its motion information can be quantitatively obtained by a simple operation.
【００５２】第１の実施例では複数断面を利用する例を
示したが、本実施例を用いて１断面から輪郭を抽出し３
次元輪郭を補間生成しても良い。In the first embodiment, an example in which a plurality of cross sections are used has been described.
A dimensional contour may be generated by interpolation.
【００５３】また、複数断面として例えば心臓を対象と
した超音波診断画像における、心尖部四腔断面像、心尖
部二腔断面像、心尖部左室長軸断面像を用いると、３断
面のみから左心室の代表的部位を網羅した壁運動情報を
得ることができる。When a plurality of slices, for example, an apical four-chamber cross-sectional image, an apical two-chamber cross-sectional image, and an apical left ventricle long-axis cross-sectional image in an ultrasonic diagnostic image of the heart are used, only three cross-sections are used. It is possible to obtain wall motion information covering a representative portion of the ventricle.
【００５４】＜第２実施例＞次に、第２実施例について
図１２から図１７を参照して説明する。<Second Embodiment> Next, a second embodiment will be described with reference to FIGS.
【００５５】第２実施例は、３次元画像データからオプ
ティカルフローを算出し、算出された速度ベクトルをも
とに３次元輪郭の時間的変位量や時間的変位速度といっ
た運動情報を算出し、その運動情報を反映するように輪
郭表示をすることで、より実際に近い運動の様子を表示
する例である。In the second embodiment, an optical flow is calculated from three-dimensional image data, and motion information such as a temporal displacement amount and a temporal displacement speed of a three-dimensional contour is calculated based on the calculated velocity vector. This is an example in which a contour is displayed so as to reflect exercise information, thereby displaying a more realistic exercise state.
【００５６】図１２は第２実施例の医用画像診断装置１
１０のブロック図であり、図１３は動作の流れを示す。FIG. 12 shows a medical image diagnostic apparatus 1 according to the second embodiment.
10 is a block diagram, and FIG. 13 shows an operation flow.
【００５７】図１２に示すように、第２実施例のコンピ
ュータによって構成される医用画像診断装置１１０は、
画像データを入力する画像入力部１１２と、入力された
画像データを記憶するメモリ１１４と、画像上の臓器輪
郭を抽出する輪郭抽出部１１６と、抽出された複数輪郭
を基に３次元輪郭を生成する３次元輪郭生成部１１８
と、画像データからオプティカルフローを算出するオプ
ティカルフロー算出部１１９と、３次元輪郭の変形から
運動情報を算出する運動情報算出部１２０と、算出され
た運動情報を表示する表示部１２２とで構成される。な
お、下記で説明する各機能はプログラムによって実現さ
れる。As shown in FIG. 12, the medical image diagnostic apparatus 110 constituted by the computer of the second embodiment has
An image input unit 112 for inputting image data, a memory 114 for storing the input image data, a contour extraction unit 116 for extracting an organ contour on the image, and a three-dimensional contour based on the plurality of extracted contours 3D contour generator 118
An optical flow calculation unit 119 that calculates an optical flow from image data; a motion information calculation unit 120 that calculates motion information from deformation of a three-dimensional contour; and a display unit 122 that displays the calculated motion information. You. Each function described below is realized by a program.
【００５８】以下、図１３の処理の流れに沿って説明す
る。Hereinafter, description will be made along the processing flow of FIG.
【００５９】まず、３次元画像データが画像入力部１１
２で入力されメモリ１１４に記憶される（ステップＳ２
１）。First, the three-dimensional image data is transferred to the image input unit 11.
2 and stored in the memory 114 (step S2
1).
【００６０】次に、３次元輪郭抽出部１１６で３次元画
像データから３次元輪郭が抽出され、３次元輪郭情報が
メモリ１１４に記憶される（ステップＳ２２）。Next, a three-dimensional contour is extracted from the three-dimensional image data by the three-dimensional contour extracting unit 116, and the three-dimensional contour information is stored in the memory 114 (step S22).
【００６１】次に、オプティカルフロー算出部１１９で
画像データからオプティカルフローを算出する（ステッ
プＳ２３）。Next, the optical flow calculation unit 119 calculates an optical flow from the image data (step S23).
【００６２】オプティカルフローは、画像上の対象物の
ある点が時間と共に画像上のどこへ移動したかを示すも
のである。オプティカルフローの算出は、勾配法やブロ
ックマッチングによる方法等の方法を用いれば良い。The optical flow indicates where an object on the image has moved over time in the image. The optical flow may be calculated using a method such as a gradient method or a method using block matching.
【００６３】オプティカルフローは、連続するフレーム
間で算出しても良いし、基準フレームと現フレームとの
間で算出しても良い。The optical flow may be calculated between consecutive frames, or may be calculated between a reference frame and the current frame.
【００６４】次に、運動情報算出部１２０においてオプ
ティカルフロー情報に基づき、３次元輪郭上の各部分に
おける時間的変位量や時間的変位速度等の運動情報を算
出し、メモリ１４に記憶する（ステップＳ２４）。Next, based on the optical flow information, the motion information calculation unit 120 calculates motion information such as a temporal displacement amount and a temporal displacement speed in each part on the three-dimensional contour, and stores them in the memory 14 (step). S24).
【００６５】オプティカルフローは画像上の全ての部分
において算出可能ではないので、オプティカルフローの
ない部分は、近隣のオプティカルフロー値を補間して生
成すると良い。Since the optical flow cannot be calculated in all parts on the image, the part without the optical flow may be generated by interpolating neighboring optical flow values.
【００６６】例えば、図１４のように、頂点近傍のオプ
ティカルフローの線形和や、その補間により頂点に対応
したオプティカルフローを生成することができる。For example, as shown in FIG. 14, an optical flow corresponding to a vertex can be generated by a linear sum of optical flows near the vertex or by interpolation.
【００６７】次に、運動情報をもとに３次元輪郭情報を
修正し、表示用３次元輪郭情報を生成する（ステップＳ
２５）。Next, the three-dimensional contour information is corrected based on the motion information to generate three-dimensional contour information for display (step S).
25).
【００６８】表示用３次元輪郭情報の生成の方法を以下
に説明する。A method for generating the display three-dimensional contour information will be described below.
【００６９】表示用３次元輪郭の形状は３次元輪郭抽出
部１１６で抽出された３次元輪郭の形状と同じである
が、２つの時相の表示用３次元輪郭を構成する各頂点の
変位量が、オプティカルフローから算出された変位量に
最も近くなるように各点を配置し、表示用３次元輪郭を
生成する（図１５参照）。つまり、表示用３次元輪郭を
構成する各点の運動が、臓器の局所運動を近似するよう
に、表示用３次元輪郭を構成する各頂点を配置する。The shape of the three-dimensional contour for display is the same as the shape of the three-dimensional contour extracted by the three-dimensional contour extracting unit 116, but the displacement of each vertex constituting the three-dimensional contour for display in two phases is shown. Arranges each point so as to be closest to the displacement calculated from the optical flow, and generates a display three-dimensional contour (see FIG. 15). That is, the vertices constituting the display three-dimensional contour are arranged such that the movement of each point constituting the display three-dimensional contour approximates the local movement of the organ.
【００７０】このように、オプティカルフロー情報に基
づき輪郭の頂点座標を決定すれば、第１実施例に示した
ような、輪郭決定後に頂点番号のみを基準に頂点を対応
付ける方法に比べ、より正確な運動状態を表すことがで
きる。また、後述する表示方法を用いれば、臓器の実際
の運動の様子をより正確に知ることができる。As described above, when the vertex coordinates of the contour are determined based on the optical flow information, a more accurate vertex coordinate is obtained as compared with the method of associating the vertices only based on the vertex numbers after the contour is determined as shown in the first embodiment. Exercise state can be represented. Further, if a display method described later is used, it is possible to more accurately know the state of the actual movement of the organ.
【００７１】上記実施例は、３次元輪郭形状は画像デー
タから求めた輪郭形状を保持し、頂点座標を輪郭表面上
で修正する例であるが、画像データに基づく３次元輪郭
よりもオプティカルフロー情報を重視して、基準フレー
ム以降の３次元輪郭形状をオプティカルフロー情報から
生成しても良い。あるいは、画像データに基づく3次元
輪郭形状とオプティカルフローに基づく３次元輪郭形状
の双方の線形和により輪郭形状を決定しても良い。The above embodiment is an example in which the three-dimensional contour shape holds the contour shape obtained from the image data and corrects the vertex coordinates on the contour surface. , The three-dimensional contour shape after the reference frame may be generated from the optical flow information. Alternatively, the contour shape may be determined by a linear sum of both the three-dimensional contour shape based on the image data and the three-dimensional contour shape based on the optical flow.
【００７２】最後に、表示部１２２がステップＳ２５で
生成された表示用３次元輪郭情報と運動情報を表示する
（ステップＳ２６）。Finally, the display unit 122 displays the display three-dimensional contour information and the motion information generated in step S25 (step S26).
【００７３】３次元輪郭表示は、例えば運動情報により
色付けされた輪郭上に、輪郭を構成する点間を直線で結
んだメッシュ表示を重ね合わせると良い。In the three-dimensional contour display, it is preferable to superimpose a mesh display in which points constituting the contour are connected by a straight line on a contour colored by, for example, motion information.
【００７４】この様に、輪郭を構成する各点を表示する
ことで、臓器局所の運動情報をより正確に得ることがで
き、臓器のねじれ運動等を反映した表示ができる（図１
６，図１７）。By displaying each point constituting the contour in this manner, it is possible to more accurately obtain the local motion information of the organ, and to display the torsion motion and the like of the organ (FIG. 1).
6, FIG. 17).
【００７５】第２実施例では３次元画像データを入力し
直接３次元輪郭を抽出する例を示したが、複数の断面画
像を利用し、断面内でのオプティカルフローを算出して
も良い。ただし、その場合は断面内の運動は反映される
が、断面以外の方向の運動は反映されない。In the second embodiment, an example in which three-dimensional image data is input and three-dimensional contours are directly extracted has been described. However, an optical flow in a cross section may be calculated using a plurality of cross-sectional images. However, in that case, the motion in the cross section is reflected, but the motion in a direction other than the cross section is not reflected.
【００７６】[0076]
【発明の効果】本発明によれば、臓器の３次元的輪郭を
生成し、臓器運動の解析が可能となる。また、臓器局所
部分の実際の運動を反映した臓器運動を抽出、表示、解
析することが可能となる。これにより、臓器の診断が大
幅に効率良く適切に行え、その効果は多大である。According to the present invention, it is possible to generate a three-dimensional contour of an organ and analyze the motion of the organ. Further, it is possible to extract, display, and analyze an organ motion that reflects an actual motion of a local part of the organ. Thereby, the diagnosis of the organ can be performed efficiently and appropriately, and the effect is great.
【図１】第１実施例の構成図である。FIG. 1 is a configuration diagram of a first embodiment.
【図２】第１実施例の処理の流れのフローチャートであ
る。FIG. 2 is a flowchart of a processing flow of the first embodiment.
【図３】第１実施例の輪郭表現の一例である。FIG. 3 is an example of a contour expression according to the first embodiment;
【図４】第１実施例における３次元輪郭生成までの処理
の模式図である。FIG. 4 is a schematic diagram of a process up to the generation of a three-dimensional contour in the first embodiment.
【図５】第１実施例における管状の３次元輪郭の模式図
である。FIG. 5 is a schematic view of a tubular three-dimensional contour in the first embodiment.
【図６】本発明の運動情報の表示例である。FIG. 6 is a display example of exercise information according to the present invention.
【図７】本発明の運動情報の表示例である。FIG. 7 is a display example of exercise information according to the present invention.
【図８】本発明の運動情報の表示例である。FIG. 8 is a display example of exercise information according to the present invention.
【図９】複数断面が１つの軸の周りに回転する場合の断
面図である。FIG. 9 is a cross-sectional view when a plurality of cross sections rotate around one axis.
【図１０】断面ｎと断面ｎ＋１間の頂点の３次元的な補
間生成を示した図である。FIG. 10 is a diagram showing three-dimensional interpolation generation of a vertex between a cross section n and a cross section n + 1.
【図１１】ユーザの操作の流れを示すフローチャートで
ある。FIG. 11 is a flowchart illustrating a flow of a user operation.
【図１２】第２実施例の構成図である。FIG. 12 is a configuration diagram of a second embodiment.
【図１３】第２実施例の処理の流れのフローチャートで
ある。FIG. 13 is a flowchart illustrating a flow of a process according to a second embodiment.
【図１４】頂点近傍のオプティカルフローの線形和や、
その補間により頂点に対応したオプティカルフローを生
成する図である。FIG. 14 shows a linear sum of optical flows near a vertex,
FIG. 6 is a diagram for generating an optical flow corresponding to a vertex by the interpolation.
【図１５】第２実施例の表示用３次元輪郭の生成例であ
る。FIG. 15 is an example of generating a display three-dimensional contour according to the second embodiment.
【図１６】オプティカルフローを反映しない場合の３次
元輪郭の例である。FIG. 16 is an example of a three-dimensional contour when an optical flow is not reflected;
【図１７】オプティカルフローを反映した場合の３次元
輪郭の例である。FIG. 17 is an example of a three-dimensional contour when an optical flow is reflected;
１０ 医用画像診断装置 １２ 画像入力部 １４ メモリ １６ 輪郭抽出部 １８ ３次元輪郭生成部 ２０ 運動情報算出部 ２２ 表示部 DESCRIPTION OF SYMBOLS 10 Medical image diagnostic apparatus 12 Image input part 14 Memory 16 Contour extraction part 18 Three-dimensional contour generation part 20 Motion information calculation part 22 Display part
───────────────────────────────────────────────────── フロントページの続き (51)Int.Cl.7 識別記号 ＦＩ テーマコート゛(参考） Ｇ０６Ｔ 7/20 Ｇ０１Ｎ 24/02 ５２０Ｙ Ｆターム(参考） 4C093 AA22 CA50 FF16 FF24 FF42 4C096 AB41 AC04 AD14 DC19 DC25 DC36 4C301 EE13 EE15 JC01 JC08 JC11 KK17 LL03 5B057 AA07 AA09 CA02 CA08 CA13 CA16 CB08 CB13 CB16 DC16 DC30 5L096 AA06 AA09 BA06 FA06 HA04──────────────────────────────────────────────────続 き Continued on the front page (51) Int.Cl. 7 Identification symbol FI Theme coat ゛ (Reference) G06T 7/20 G01N 24/02 520Y F-term (Reference) 4C093 AA22 CA50 FF16 FF24 FF42 4C096 AB41 AC04 AD14 DC19 DC25 DC36 4C301 EE13 EE15 JC01 JC08 JC11 KK17 LL03 5B057 AA07 AA09 CA02 CA08 CA13 CA16 CB08 CB13 CB16 DC16 DC30 5L096 AA06 AA09 BA06 FA06 HA04
Claims (8)
画像から前記臓器に関する複数時相の３次元輪郭を算出
する輪郭算出手段と、 算出した前記臓器に関する複数時相の３次元輪郭に基づ
いて、前記臓器の３次元輪郭上の各点の時間的変位量を
算出する変位量算出手段と、 算出した前記各点の時間的変位量から前記臓器の輪郭の
運動情報を算出する運動算出手段と、 を有することを特徴とする医用画像診断装置。1. A contour calculating means for calculating a three-dimensional contour of a plurality of time phases related to an organ from an image of a plurality of time phases obtained by photographing an organ which is a living body organ; Displacement amount calculating means for calculating a temporal displacement amount of each point on the three-dimensional contour of the organ based on the motion amount calculating means for calculating motion information of the contour of the organ from the calculated temporal displacement amount of each point Means, and a medical image diagnostic apparatus comprising:
に基づいて、前記各断面における前記臓器の輪郭を抽出
する輪郭抽出手段と、 抽出された複数時相の前記各断面における前記臓器にお
ける輪郭に基づいて、前記臓器に関する複数時相の３次
元輪郭を生成する輪郭生成手段と、 を有することを特徴とする請求項１記載の医用画像診断
装置。2. The contour calculating means includes: a contour extracting means for extracting a contour of the organ in each of the cross sections based on a two-dimensional image of a plurality of time phases in which a plurality of cross sections of the organ are photographed; 2. The medical image diagnostic apparatus according to claim 1, further comprising: a contour generating unit configured to generate a three-dimensional contour having a plurality of phases with respect to the organ based on the contour of the organ in each of the cross sections with a plurality of phases. .
て、前記臓器に関する複数時相の３次元輪郭を算出する
ことを特徴とする請求項１記載の医用画像診断装置。3. The three-dimensional contour of a plurality of phases related to the organ is calculated based on a three-dimensional image of the plurality of phases in which the organ is captured. Medical diagnostic imaging device.
位量が、前記３次元輪郭を構成する頂点の時間的な移動
ベクトルであることを特徴とする請求項１記載の医用画
像診断装置。4. The medical image according to claim 1, wherein the temporal displacement of each point on the three-dimensional contour of the organ is a temporal movement vector of a vertex constituting the three-dimensional contour. Diagnostic device.
位量が、前記３次元輪郭を構成する頂点近辺の画像デー
タに基づき計算されるオプティカルフローベクトルであ
ることを特徴とする請求項１記載の医用画像診断装置。5. The method according to claim 1, wherein the temporal displacement of each point on the three-dimensional contour of the organ is an optical flow vector calculated based on image data near a vertex constituting the three-dimensional contour. Item 2. The medical image diagnostic apparatus according to Item 1.
各点の時間的変位量に基づき、時間的に変位する頂点に
よって表現された前記臓器の３次元輪郭を表示する表示
手段を有したことを特徴とする請求項１記載の医用画像
診断装置。6. A display means for displaying a three-dimensional contour of the organ represented by a temporally displaced vertex based on the calculated temporal displacement of each point on the three-dimensional contour of the organ. 2. The medical image diagnostic apparatus according to claim 1, wherein:
画像から前記臓器に関する複数時相の３次元輪郭を算出
する輪郭算出ステップと、 算出した前記臓器に関する複数時相の３次元輪郭に基づ
いて、前記臓器の３次元輪郭上の各点の時間的変位量を
算出する変位量算出ステップと、 算出した前記各点の時間的変位量から前記臓器の輪郭の
運動情報を算出する運動算出ステップと、 を有することを特徴とする医用画像診断方法。7. A contour calculating step of calculating a three-dimensional contour of a plurality of time phases related to the organ from an image of a plurality of time phases obtained by photographing an organ which is a living body organ; A displacement amount calculating step of calculating a temporal displacement amount of each point on the three-dimensional contour of the organ based on the motion amount; calculating a motion information of the contour of the organ from the calculated temporal displacement amount of each point; A medical image diagnostic method, comprising:
画像から前記臓器に関する複数時相の３次元輪郭を算出
する輪郭算出機能と、 算出した前記臓器に関する複数時相の３次元輪郭に基づ
いて、前記臓器の３次元輪郭上の各点の時間的変位量を
算出する変位量算出機能と、 算出した前記各点の時間的変位量から前記臓器の輪郭の
運動情報を算出する運動算出機能と、 をコンピュータによって実現することを特徴とする医用
画像診断方法のプログラム。8. A contour calculating function for calculating a three-dimensional contour of a plurality of time phases related to said organ from an image of a plurality of time phases obtained by photographing an organ which is a living body organ; A displacement amount calculating function for calculating a temporal displacement amount of each point on the three-dimensional contour of the organ based on the motion information; and a motion calculation for calculating motion information of the contour of the organ from the calculated temporal displacement amount of each point. A program for a medical image diagnosis method, wherein the functions are realized by a computer.
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