JP4598652B2 - Ultrasonic diagnostic equipment - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to an ultrasonic diagnostic apparatus that tracks a specific part in a tissue.

  In an ultrasonic diagnostic apparatus, a technique is known in which a straight line or a curve is set in a B-mode image, and the time change of image data on the straight line (or on the curve) and the time change of velocity data on the straight line are displayed in M mode. (See Patent Documents 1 and 2).

  In addition, a technique for tracking a specific part of a tissue based on image data in an ultrasonic diagnostic apparatus is known. For example, a technique is known in which a similar part of an image is extracted by pattern matching on a B-mode image to track a specific part that moves with the movement of the tissue (see Patent Documents 3 to 5).

  Incidentally, Patent Document 6 describes a technique in which a virtual contraction center is set in a two-dimensional image and a velocity component toward the virtual contraction center is corrected by a Doppler angle. Using this velocity component, it is possible to estimate and track the position of the tracking point that moves toward the virtual contraction center direction.

JP-A-8-173430 JP-A-10-711147 JP 2004-313535 A JP 2004-313545 A JP 2004-31551 A JP 2003-175041 A

  The above-described technique for displaying the mode change of the image data on the straight line in the M mode is suitable for, for example, diagnosing the myocardial motion state. In other words, by setting a straight line in the thickness direction of the myocardium and forming an M-mode image, changes in the thickness of the myocardium can be visually captured by the image, or the myocardial thickness is calculated and numerically changed. It becomes possible to catch.

  In this case, it is desirable that the straight line set for the myocardium is set so as to follow a specific part that moves with the movement of the myocardium. In other words, it is desirable to measure the thickness of the myocardium in that portion while always capturing the same tissue portion.

  The specific part that moves with the movement of the tissue can be tracked by using the pattern matching method described above. For example, a specific point inside the myocardium and a specific point outside the myocardium can be tracked by a pattern matching method, respectively. Then, by setting a straight line connecting a specific point inside the myocardium and a specific point outside the myocardium, a suitable straight line following the movement of the myocardium can be obtained.

  However, the pattern matching method using image data can track the edge of the tissue such as the myocardium (the boundary with other tissues) relatively accurately, but it can accurately identify specific points inside the tissue. It is difficult to track. That is, the echo reflected from the inside of the tissue such as the myocardium is obtained as a speckle pattern, so that it is theoretically difficult to accurately extract the same specific point from the image data.

  For this reason, the conventional ultrasonic diagnostic apparatus cannot accurately track a specific part inside the myocardium, for example, a part at a boundary position set to distinguish between the intima and the outer film of the myocardium. It was.

  The present invention has been made in such a background, and an object thereof is to provide a technique for accurately tracking a specific site in a tissue.

  In order to achieve the above object, an ultrasonic diagnostic apparatus according to a preferred aspect of the present invention includes a transmission / reception unit that transmits and receives an ultrasonic wave in a space including a target tissue to obtain an echo signal, and an echo signal obtained from the echo signal. A line segment setting means for setting a line segment to the target tissue for each frame in accordance with the movement of the target tissue in a data space composed of data to be processed, and a reference point set on the line segment of the reference frame Specific part tracking means for tracking a specific part of the target tissue corresponding to the reference frame over a plurality of frames, and the specific part tracking means is based on the velocity information of the reference point set in the reference frame. The temporary movement point of the specific part is set on the line segment of the specific point, and the movement point of the specific part is set on the line segment of the frame of interest based on the speed information of the temporary movement point and the speed information of the reference point. And

  In the above configuration, the line segment set by the line segment setting means is set, for example, while always capturing the same tissue portion in the target tissue so as to follow the movement of the target tissue. Then, the specific part tracking means sets the moving point of the specific part on the line segment of the frame of interest using the speed information. The velocity information includes, for example, Doppler information obtained from the echo signal.

  With the configuration described above, it is possible to accurately track the characteristic site in the tissue, which has conventionally been difficult to accurately track, using the velocity information. For this reason, for example, it becomes possible to set a line segment in the thickness direction of the myocardium by the line segment setting means, and to track the boundary part between the intima and outer membrane of the myocardium by the specific part tracking means. It is possible to obtain the change in thickness on the membrane side and the outer membrane side independently.

  In a desirable mode, the velocity information of the reference point includes the velocity in the ultrasonic beam direction at the reference point and the angle of the ultrasonic beam direction with respect to the line segment on which the reference point is set, and the temporary moving point The velocity information includes a velocity in the ultrasonic beam direction at the temporary moving point and an angle in the ultrasonic beam direction with respect to the line segment where the temporary moving point is set.

  In a desirable mode, the specific part tracking means includes a speed in the line segment direction at the reference point obtained from the speed information of the reference point, and a speed in the line segment direction at the temporary movement point obtained from the speed information of the temporary movement point. The movement amount of the specific part is calculated based on the average value of the two velocities in the line segment direction, and the movement point of the specific part is set on the line segment of the frame of interest.

  In a preferred aspect, the specific part tracking means includes an average value of two velocities consisting of the velocity in the ultrasonic beam direction included in the velocity information of the reference point and the velocity in the ultrasonic beam direction included in the velocity information of the temporary moving point. And the average value of the two angles consisting of the angle of the ultrasonic beam direction included in the velocity information of the reference point and the angle of the ultrasonic beam direction included in the velocity information of the temporary moving point, The amount is calculated, and the moving point of the specific part is set on the line segment of the frame of interest.

  In order to achieve the above object, an ultrasonic diagnostic apparatus according to a preferred aspect of the present invention includes a transmission / reception unit that transmits and receives ultrasonic waves in a space including the myocardium to obtain an echo signal, and an echo signal obtained from the echo signal. In the data space composed of data, the line segment connecting the intima specific part and the epicardial specific part of the myocardium is set, and the intima specific part and the epicardial specific part that move with the movement of the myocardium are tracked. A line segment setting means for setting a line segment for each frame, and a specific site tracking for tracking a specific site in the myocardial tissue specified by a reference point set on the line segment of the reference frame over a plurality of frames And the specific part tracking means sets a temporary movement point of the specific part on a line segment of the frame of interest based on speed information of the reference point set in the reference frame, and the speed of the temporary movement point Information and reference point velocity information There sets the movement point of the specific portion on a line of interest frame, characterized in that.

  In a preferred aspect, the specific part tracking means uses the speed information of the set moving point, and further, on the line segment of the frame of interest based on the speed information of the moving point and the speed information of the reference point. The moving point of the specific part is reset. In a preferred aspect, the line segment setting means tracks the intima specific part and the epicardial specific part by pattern matching processing on image data obtained from an echo signal. In a preferred aspect, the specific part tracking means tracks a specific part corresponding to the boundary between the intima and the epicardium of the myocardium specified by the reference point over a plurality of frames.

  The present invention makes it possible to accurately track a specific site within a tissue. For this reason, for example, it is possible to track the boundary between the intima and the adventitia of the myocardium, and it is possible to independently determine the change in thickness of the intima side and the adventitia side of the myocardium.

  DESCRIPTION OF EXEMPLARY EMBODIMENTS Hereinafter, preferred embodiments of the invention will be described with reference to the drawings.

  First, the principle of the tracking process executed in this embodiment will be described with reference to FIGS. This process is executed in the ultrasonic diagnostic apparatus, but may be executed in a computer that acquires data from the ultrasonic diagnostic apparatus.

  FIG. 1 shows an ultrasound image including a myocardium that is a target tissue. That is, the ultrasonic image shown in FIG. 1 is a B-mode image formed from echo signals obtained by transmitting and receiving ultrasonic waves in a space including the myocardium 1. In the present embodiment, a color Doppler image that expresses the velocity of the myocardium 1 or blood flow by color may be formed as the ultrasound image. That is, based on the Doppler information obtained from the echo signal, the color Doppler image that calculates the velocity for each position of the blood flow in the myocardium 1 and the heart chamber surrounded by the myocardium 1 and expresses the calculated velocity by color. May be formed.

  The myocardium 1 functions as a pump that circulates blood throughout the body by changing its thickness. For this reason, in evaluating the function of the heart, the evaluation of the thickness of the myocardium 1 is an important evaluation factor. For example, when the symptoms of myocardial infarction progress, the thickness change of the myocardium 1 is affected.

  In the present embodiment, the thickness of the myocardium 1 can be accurately measured. Furthermore, it is possible to know changes in the thicknesses of the inner and outer membranes of the myocardium 1. Myocardial infarction progresses from the intimal side of the myocardium 1. For example, at the initial stage of myocardial infarction, the intima changes in thickness so that the intima causes an infarction and the outer membrane makes up for it, so it is difficult to know the presence of the initial stage of myocardial infarction from the thickness of the entire myocardium. As myocardial infarction progresses, the outer membrane also infarcts, affecting the thickness change of the entire myocardium. However, if it can be determined that the infarction is before the entire myocardium is affected, it will be very useful for early treatment. Hereinafter, a method for measuring the thickness of the myocardium 1 according to the present embodiment will be described.

  First, for the myocardium 1, an inner end point 3 and an outer end point 4 are set, and a line segment 2 passing through these two end points is set. Then, the reference point 5 is set at an intermediate position between the end point 3 and the end point 4 on the line segment 2. Each of the end point 3 and the end point 4 is set to a desired position while the user views the ultrasonic image, for example. The reference point 5 is a reference adopted as a point indicating the boundary between the intima and adventitia. For example, it is desirable to set the reference point 5 at an intermediate position between the end points 3 and 4 at the end diastole of the heart. . However, the reference point 5 is not limited to an intermediate position between the end point 3 and the end point 4, and the user may set the reference point 5 at a desired position on the line segment 2 while watching the ultrasonic image.

  FIG. 2 is a diagram for explaining a change in the thickness of the myocardium 1, and is an enlarged view in the vicinity of the line segment 4 in FIG. As a result of changing the thickness of the myocardium 1, the intima surface (solid line) 6 and the outer membrane surface (solid line) are shown in FIG. 2 from the contours indicated by the intima surface (dashed line) 6 ′ and the outer membrane surface (dashed line) 11 ′. It changes to the contour shown by 11. At this time, the tissue sites at the positions of the end points 3 and 4 set for the myocardium 1 move to the positions of the moving point 7 and the moving point 10, respectively.

  The movement of the end points 3 and 4 can be confirmed from the B-mode image by a pattern matching method. That is, for example, the B-mode image of the frame in which the end point 3 and the end point 4 are set (previous frame) and the B-mode image of the frame in which the moving point 7 and the moving point 10 are detected (current frame) are compared. The moving point 7 is detected by extracting an image similar to the image in the vicinity of the current frame from the current frame, and the moving point 10 is detected by extracting an image similar to the image in the vicinity of the end point 4 from the current frame. Can do. Examples of the pattern matching technique include known techniques such as a template matching method and a PG matching method. Of course, in this embodiment, other pattern matching techniques may be used.

  As a result of the movement of the end points 3 and 4, the line segment 2 also moves to the line segment 8. As a result, the reference point 5 also moves to the moving point 9 on the line segment 8. However, it is virtually impossible to accurately detect the movement of the tissue site corresponding to the reference point 5 by pattern matching of the B-mode image. That is, since the reference point 5 is inside the tissue of the myocardium 1, an echo reflected from the vicinity of the reference point 5 is obtained as a speckle pattern, and it is theoretically possible to accurately extract the same part from the image data. Because it is difficult. For this reason, in this embodiment, the specific site | part of the myocardium 1 specified by the reference | standard point 5 is tracked using the Doppler information obtained from an echo signal.

When Doppler information is acquired by scanning an ultrasonic beam, the velocity of the tissue in the direction of the ultrasonic beam is measured. Therefore, the velocity of the ultrasound beam direction at the reference point 5 and V _1. When the angle between the line segment 2 and the ultrasonic beam from which the velocity V ₁ is measured is θ ₁ , the velocity component V _{r1 in the} direction of the segment 2 of the reference point 5 is V _r1 = V ₁ / cos θ _1. Is required. Note that the velocity V _{1 in the} ultrasonic beam direction may be estimated using velocity information in the vicinity of the reference point 5. When the time difference between frames is Δt, the moving distance d _{1 in} which the reference point 5 moves between the frames in the direction of the line segment 2 is obtained by d ₁ = V _r1 × Δt = V ₁ / cos θ ₁ × Δt.

なお、数１において、速度Ｖ（ｔ）と移動距離ｄは、各々、方向を持ったベクトルで表現されている。 However, in practice, the speed of the reference point 5 may change during Δt, and the position of the line segment 2 may also change, and the angle with the ultrasonic beam may also change. Therefore, an accurate moving distance d after Δt time is calculated by integration of the following equation from the velocity V (t) at a certain time point and the angle θ (t) of the ultrasonic beam with respect to the direction of the velocity V (t). Is done.

In Equation 1, the velocity V (t) and the moving distance d are each expressed by a vector having a direction.

  An accurate moving distance d can be calculated by the integration calculation shown in Equation 1. However, when the Doppler information is obtained for each frame by scanning the ultrasonic beam, the speed change and the angle change between the frames are not measured. Therefore, in the present embodiment, the moving point 9 that is the movement destination of the reference point 5 is obtained using the Doppler information (speed information) in the line segment 8 that is the movement destination of the line segment 2. Further, in the present embodiment, the reference point 5 is tracked by sequentially obtaining the movement destination of the reference point 5 over a plurality of frames. The tracking method will be described in detail below.

  3 and 4 are flowcharts showing the tracking procedure of the reference point 5 in the present embodiment. Hereinafter, the processing content of each step of FIG. 3 and FIG. 4 is demonstrated. 2 will be described using the reference numerals in FIG.

  First, in S100, an inner end point 3 and an outer end point 4 of the myocardium are set. For example, the operator sets the end point 3 and the end point 4 at desired positions while viewing the ultrasonic image. In S110, the line segment 2 passing through the end points 3 and 4 is defined, and the reference point 5 is set as the midpoint between the end points 3 and 4. The reference point 5 is a reference adopted as a point indicating the boundary between the inner membrane and the outer membrane, and does not necessarily need to be present at the intermediate position of the line segment 2. If necessary, the user may set the reference point 5 at a desired position on the line segment 2 while viewing the ultrasonic image.

  In S120, the process moves to the next frame, and the myocardium moves to the position indicated by the intima surface 6 and the adventitia surface 11. In S130, the end point 3 and the end point 4 are respectively connected to the intima surface 6 and the adventitia surface 11 by using a pattern matching (pattern recognition) method of the B-mode image between the previous frame and the next frame. The position of the inner membrane side moving point 7 and the outer membrane side moving point 10 are determined. As a result, line segment 2 moves to line segment 8.

In S140, it reads the speed _{V 1} of the points of the reference point 5 from the tissue velocity data. That is, for example, the velocity data at the position of the reference point 5 is read from the velocity data at each position of the myocardium and blood flow that have already been acquired to form a color Doppler image. In S150, the angle theta ₁ between the ultrasonic beam to measure the line 2 and the speed V _1, performs angle correction of the velocity V _1, a direction of the velocity component of the line segment 2 of the reference point 5 V _{Find r1} . The velocity component V _r1 is obtained by V _r1 = V ₁ / cos θ ₁ . In S160, the distance d by which the reference point 5 has moved between frames is determined by the product of the velocity component V _r1 and the time difference Δt between frames.

In S170, the distance of the end points 4 and reference point 5 on the line 2 and _{d 45,} the movement point of the distance from the end point 10 of _{d 45} + d on line 8 (tentative point) 9 seeking, the tentative point 9 read the speed V ₂ from the tissue velocity data. In S180, the angle theta ₂ between the ultrasonic beam to measure the line 8 and the speed V _2, performs angle correction of the velocity V _2, a direction of the velocity component of the line segment 8 of the provisional point 9 V _{Find r2} . The velocity component V _r2 is obtained by V _r2 = V ₂ / cos θ ₂ .

Ｓ２００では、Ｓ１９０で算出された移動距離ｄｒが、現在の演算対象となっている二つのフレーム間で初めて求められた値か否かを確認する。そして、移動距離ｄｒが初めて求められた値であればＳ２２０（図４）へ進み、一方、移動距離ｄｒが初めて求められた値でなければＳ２１０（図４）へ進む。 In S190, an average speed V _r12 between Δt is obtained from the speed component V _r1 and the speed component V _r2, and a product of Δt is obtained to obtain the moving distance dr. The average speed V _r12 is obtained by V _r12 = 1/2 (V _r1 + V _r2 ). The moving distance dr may be calculated by the following equation.

In S200, it is confirmed whether or not the movement distance dr calculated in S190 is a value obtained for the first time between two frames that are the current calculation target. If the movement distance dr is a value obtained for the first time, the process proceeds to S220 (FIG. 4). On the other hand, if the movement distance dr is not a value obtained for the first time, the process proceeds to S210 (FIG. 4).

  In S210, it is confirmed whether or not the movement distance dr obtained this time is the same value as the movement distance dr obtained last time. If the values are the same, it is determined that the calculation for obtaining the movement distance dr has converged, and the process proceeds to S230. On the other hand, if it is not the same value, it is determined that the calculation for obtaining the movement distance dr has not converged, and the process proceeds to S220.

  In S220, it is confirmed whether or not the number of times of calculation of the movement distance dr has reached a preset number. If the set number of times has not been reached, the value of dr is set to d in S240, and the processing after S170 (FIG. 3) is executed to calculate the movement distance dr again. On the other hand, if the set number of times has been reached in S220, it is determined that the repetitive calculation of the movement distance dr has ended, and the process proceeds to S230.

In S230, the movement point of the reference point 5 is obtained using the movement distance dr obtained as a result of the repetitive calculation. That is, the moving point 9 to which the reference point 5 moves when moving from the line segment 2 to the line segment 8 is obtained as a point having a distance of d ₄₅ + dr from the end point 10.

  In S250, it is confirmed whether or not the current frame is the last frame. In the present embodiment, the movement destination of the reference point 5 is tracked over a plurality of frames. That is, if it is determined in S250 that it is not the last frame, in S260, the end point 7, the moving point 9, and the end point 10 of the line segment 8 are changed to the end point 3 and the reference point of the line segment 2 in the calculation of the next frame. 5. Considering the end point 4 to proceed to S120 (FIG. 3), the calculation of the movement distance dr in the next frame is executed. Thus, the position of the moving point 9 is obtained until it is determined in S250 that it is the last frame.

  In the present embodiment, for example, the tracking process is performed on a frame for one cycle of the heartbeat. For example, a plurality of frames from the time phase of the R wave obtained using the electrocardiographic waveform to the time phase of the next R wave are targeted. In this case, it is desirable that the end points and reference points set in S100 and S110 are set for the first frame (R-wave time phase frame). In the case where the set end point or reference point is not that of the first frame, the tracking principle described above is applied in a direction that goes back to the time frame of the R wave, and in the frame of the R wave time phase. The end point may be detected, and the reference point may be obtained again from the detected end point. It should be noted that only two end points may be tracked when tracing back in time.

  In the present embodiment, the movement destination of the reference point 5 is tracked over a plurality of frames according to the principle described above. The reference point 5 is not limited to one point. That is, for example, a plurality of reference points may be set on the line segment 2 in S110, and the tracking process may be executed for each reference point. As a result, it is possible to track any plurality of specific sites in the thickness direction of the heart wall. In the present embodiment, by using the tracking result of the reference point 5, various display image formations and calculations are executed in S270. Therefore, the apparatus configuration of the ultrasonic diagnostic apparatus according to the present embodiment will be described next.

  FIG. 5 is a functional block diagram of the ultrasonic diagnostic apparatus of the present embodiment. The probe 50 is a transducer that transmits and receives ultrasonic waves. In the present embodiment, an array transducer composed of a plurality of transducer elements is provided in the probe 50, and an ultrasonic beam is formed by the array transducer. In this embodiment, the ultrasonic beam is electronically scanned by an electronic sector scanning method, and a fan-shaped scanning surface is constructed. Incidentally, it is possible to apply a control for simultaneously forming a plurality of reception beams per transmission beam, and the probe 50 may be a so-called 3D probe. For example, when performing an ultrasonic diagnosis of the heart, the position and posture of the probe 50 abutted on the chest surface of the living body are appropriately adjusted. In that case, for example, a B-mode image displayed on the display is observed. In order to execute the tissue Doppler imaging method (TDI method), ultrasonic waves are transmitted and received a plurality of times for each beam address.

  The transmission / reception unit 52 is configured as a digital beam former. That is, the transmission / reception unit 52 has a transmission beam former and a reception beam former. A plurality of transmission signals are supplied to the array transducer by the transmission beam former, thereby forming a transmission beam. On the other hand, a plurality of reception signals output from the array transducer are subjected to phasing addition processing in the reception beamformer, whereby a reception signal after phasing addition is obtained. That is, a reception signal corresponding to the reception beam is obtained. The reception signal output from the transmission / reception unit 52 is output to the tissue echo processing unit 56 and the tissue velocity processing unit 58.

  The tissue echo processing unit 56 executes various signal processes for forming a tissue echo image. The process includes, for example, a logarithmic conversion process. The scan conversion unit 64 performs coordinate conversion processing, interpolation processing, and the like. That is, the scan conversion unit 64 has a so-called DSC (digital scan converter) function. Through processing by the tissue echo processing unit 56 and the scan conversion unit 64, the data of each frame is output, and the 2D echo image processing unit 70 forms image data of a two-dimensional B-mode image.

  A cine memory 60 is provided at the subsequent stage of the tissue echo processing unit 56, and data of each frame before coordinate conversion is stored in the cine memory 60 in chronological order. A memory for storing the data of each frame after coordinate conversion processed in the scan conversion unit 64 may be provided.

  The tissue velocity processing unit 58 functions as a Doppler processing unit, and performs complex signal conversion processing, autocorrelation calculation processing, and the like on the reception signal output from the transmission / reception unit 52, thereby obtaining tissue velocity information. Arithmetic. Then, the scan conversion unit 62 performs coordinate conversion processing, interpolation processing, and the like, and the 2D velocity image processing unit 72 performs color image (color color) in which the speed is positive and negative and the color corresponding to the value is applied to each tissue site. Doppler image) image data is formed. Note that a cine memory 60 is provided at the subsequent stage of the tissue velocity processing unit 58, and data of each frame output from the tissue velocity processing unit 58 is stored in chronological order.

  In the present embodiment, the cine memory 60 stores the tissue echo data processed by the tissue echo processing unit 56 and the tissue velocity data processed by the tissue velocity processing unit 58. In these two types of data, a plurality of data in time series order within a certain time range are stored in association with each other. The cine memory 60 has a ring buffer structure, and has a function of storing a frame sequence over a time range from the latest frame to a frame of a past fixed time. By using the cine memory 60, it is possible to read out the frame sequence stored in the cine memory 60 later for loop reproduction.

  By storing the data temporarily stored in the cine memory 60 also in the external recording medium 54, it becomes possible to store the frame data for a long time exceeding the capacity of the cine memory 60. In this embodiment, various processes are performed on a plurality of frame data in time series within a certain time range stored in the cine memory 60 or the external recording medium 54.

  The end point tracking unit 66 is based on the tissue echo data (data for the B-mode image) of each frame output through the processing by the tissue echo processing unit 56 and the scan conversion unit 64, and the end point inside and outside the myocardium. To track. In other words, the end point tracking unit 66 uses the pattern matching technique based on the principle described above (see FIGS. 3 and 4) to convert the inner end point and the outer end point that move with the movement of the myocardium into a plurality of frames. Track across.

  The reference point tracking unit 68 generates a reference point on a line segment that passes through the inner end point and the outer end point of the myocardium from the tissue velocity data of each frame output through the processing by the tissue velocity processing unit 58 and the scan conversion unit 62. To track. That is, the reference point tracking unit 68 uses the reference point velocity information (tissue velocity data) based on the principle described above (see FIGS. 3 and 4) to set a plurality of reference points that move with the movement of the myocardium. Track across frames.

  The tracking line forming unit 74 includes a line segment connecting two end points tracked by the end point tracking unit 66 (reference numerals 2 and 8 in FIG. 2), end points (reference numerals 3, 4, 7, and 10 in FIG. 2), and a reference. A display image showing reference points (reference numerals 5 and 9 in FIG. 2) tracked by the point tracking unit 68 is formed. By displaying an image such as a line segment formed by the tracking line forming unit 74 so as to be superimposed on the B-mode image, for example, a display image having the form shown in FIG. 2 is formed.

  In FIG. 5, the end point tracking result by the end point tracking unit 66 and the reference point tracking result by the reference point tracking unit 68 are supplied to the trace line forming unit 80 via the tracking line forming unit 74 to form a trace line. Is done. In addition, the strain calculation unit 82 calculates the strain.

Therefore, the trace line forming process and the strain calculation will be described with reference to FIG. FIG. 6 shows line segments Q ₁ , Q ₂ , Q ₃ ,..., Q _{n of} a plurality of frames arranged in the time axis t direction. That is, FIG. 6 shows a line segment passing through the inner end point and the outer end point of the myocardium, which is tracked by the method described above (see FIGS. 3 and 4) and arranged in the time axis t direction.

  In FIG. 6, three tracking points R, S, and T are shown on each line segment. Point R indicates an end point inside the myocardium, point T indicates an end point outside the myocardium, and point S indicates a reference point. Each of the three tracking points R, S, and T has a suffix (1 to n) corresponding to the line segment.

In the line segment Q ₁ of the frame F _{1 that is} the starting point, the distance between the points R and T is L. When the reference point S is set as an intermediate point between the points R and T, the distance L is divided into two equal sections, and their lengths are L ₀ (= L / 2), respectively. is there. Incidentally, the length L ₀ is used as information for normalization for calculating the strain.

  The three tracking points R, S, and T are tracked by the method described above (see FIGS. 3 and 4). When attention is paid to the upper tracking point R, it is possible to draw a single trace line by interconnecting a plurality of tracking points R1 to Rn arranged on the time axis. If this process is applied to each of the points R, S, and T, a plurality of necessary trace lines can be drawn.

Next, the strain calculation will be described with reference to FIG. A strain ε (t) indicating a change in the thickness of the myocardium is defined by ε (t) = (L (t) −L ₀ ) / L ₀ . Here, L (t) is the section length of the section currently focused on, and L ₀ is the reference section length for normalization. Therefore, in FIG. 6, if two sections L _RS2 and L _ST2 defined on the line segment Q ₂ of the frame F ₂ are respectively substituted into L (t) in the above formula, the strain ε (t ). The same applies to the two section lengths L _RS3 and L _ST3 on the segment Q ₃ of the frame F ₃ , and the same applies to the subsequent frames. Furthermore, in the present embodiment, a display image using a trace line or a strain calculation result can be formed.

FIG. 7 is a diagram for explaining a display image formed by the ultrasonic diagnostic apparatus according to the present embodiment. The M-mode tissue velocity image shown in (A) is the tissue velocity data on the line segments (Q ₁ , Q ₂ , Q ₃ ,..., Q _n in FIG. 6) obtained for each time phase, that is, for each frame. Are images arranged in chronological order. That is, the vertical axis corresponds to the position on the line segment, and the horizontal axis corresponds to the time axis. Each tissue velocity data is composed of a plurality of tissue velocity data arranged on a line segment of each time phase. In mapping these tissue velocity data, an interpolation process or a thinning process is applied as necessary. The M-mode tissue velocity image shown in (A) is displayed as a color image. That is, a predetermined hue and luminance are assigned according to the sign and magnitude of the tissue velocity data.

  In the present embodiment, trace lines (reference numerals 22, 24, and 26) can be drawn on the M-mode tissue velocity image. In the example shown in FIG. 7, trace lines corresponding to each of the three tracking points R, S, and T are drawn. That is, the trace line 22 of the point R which is the inner end point of the myocardium, the trace line 24 of the point S which is the reference point (boundary between the intima and outer membrane) in the myocardium, and the trace of the point T which is the end point outside the myocardium. Line 26 is shown. Thus, by drawing a trace line on the M-mode tissue velocity image, it is possible to easily observe the motion trajectory of the myocardium.

  In the present embodiment, an M-mode strain image as shown in (B) can be formed by using a strain calculation result. The horizontal axis in the M-mode strain image is the time axis as in the M-mode tissue velocity image, and the vertical axis also corresponds to the position on the line segment as in the M-mode tissue velocity image. This M-mode strain image is an image in which the strain calculated for each section in each time phase is expressed in color. That is, it is an image that is displayed by associating the sign and size of the strain calculated for each section in each frame with the hue or the like.

  When forming an M-mode strain image, the trace lines 22, 24, and 26 may be displayed as in the case of FIG. 7A, or may not be displayed. In any case, the strain is calculated for two sections of each time phase divided by the trace lines 22, 24, 26, that is, a section corresponding to the intima and a section corresponding to the outer membrane, The time change of the strain is represented by the color. For example, when attention is paid to a certain time phase, a one-dimensional pixel value sequence exists between the trace lines 22 and 26, and a partial pixel sequence 28 (internal) existing between the trace lines 22 and 24 is included therein. The pixel column on the film side) is colored corresponding to the strain defined for it, and this is applied to the partial pixel column 30 (pixel column on the outer film side) divided by the trace lines 24 and 26. Is the same. Strain is defined as a one-dimensional strain of tissue. In addition, the disease diagnosis accuracy can be further improved by setting the reference point on the line segment to a desired position as required and displaying the strain for each depth section or each layer in the heart wall. There is an advantage.

  In the present embodiment, by further designating a predetermined time phase on the M-mode strain image by the user, that is, by performing time phase designation using the cursor 31, for example, the strain graph 32 in the time phase is separately displayed on the screen. It can also be displayed. The strain graph 32 is a graph in which the horizontal axis represents the positive and negative values of the strain and the size thereof, and the vertical axis represents the position on the line segment.

  Incidentally, instead of the strain, the length of each section and the rate of change thereof can be expressed in color as an evaluation value. It is also possible to display a list of strains of each section in each time phase by numerical values, and it is also possible to display strains in designated time phases by numerical values. Further,% Wall Thickness, which is an index of the thickness of the myocardium, may be obtained from the trace result of the inner end point and the outer end point of the myocardium.

  In this embodiment, by setting a reference point at an intermediate position between the inner end point and the outer end point at the end diastole of the heart, this reference point is set as the boundary between the intima and the epicardium, and the intima side and the epicardium side of the myocardium Changes in thickness and the like can be obtained independently.

  Returning to FIG. 5, the trace line forming unit 80 forms a trace line by connecting the tracking points tracked for each frame on the time axis. That is, the trace line at the end point inside the myocardium, the trace line at the end point outside the myocardium, and the trace line at the reference point are formed by the method described using FIG. The trace line forming unit 80 may perform a smoothing process or the like in addition to the tracking point interconnection process.

  The strain calculation unit 82 calculates a strain for each section in each time phase in accordance with the principle of the strain calculation described with reference to FIG. The calculation result is subjected to a coloring process in the strain image forming unit 84, and an M-mode strain image (see FIG. 7) after the coloring process is formed. When a predetermined time phase is designated, the strain graph creation unit 86 creates a strain graph by referring to the strain of each section in the time phase.

The M image forming unit 78 forms an M mode image based on the image data of the B mode image formed by the 2D echo image processing unit 70. That is, for example, an M-mode image is formed in which tissue echo data on line segments (Q ₁ , Q ₂ , Q ₃ ,..., Q _n in FIG. 6) obtained for each frame are arranged in chronological order. . Further, the M image forming unit 78 forms an M mode tissue velocity image (see FIG. 7) based on the image data (velocity data) of the color image formed in the 2D velocity image processing unit 72.

  For example, the profile generation unit 76 acquires velocity data in a time phase designated by the user from the M image forming unit 78 and creates a velocity profile (velocity distribution). Further, the profile generation unit 76 may create a strain profile by using the strain calculation result acquired from the strain calculation unit 82.

  The composition processing unit 88 is a module that composes a plurality of image data selected according to the display mode from a plurality of input image data to form one display image. The image data output from the synthesis processing unit 88 is output to the display device 90. On the display device 90, for example, the myocardial ultrasound image (B-mode image or color Doppler image) shown in FIG. The shown M-mode tissue velocity image, M-mode strain image, and the like are displayed. The display device 90 may be configured by, for example, a CRT or a liquid crystal display. Alternatively, two displays, a CRT and a liquid crystal display, may be connected to the subsequent stage of the composition processing unit 88, and one may be used as the main display and the other as the sub display.

  The control unit 92 performs operation control of each component included in the ultrasonic diagnostic apparatus. The control unit 92 includes a CPU and an operation program. In FIG. 5, the display processing unit indicated by reference numeral 100 is shown as a module different from the control unit 92 in the present embodiment, but the display processing unit 100 may be configured by a CPU and a processing program. Alternatively, the display processing unit 100 may be configured by dedicated hardware. Alternatively, only some of the functions of the display processing unit 100 may be realized by software processing, and the rest may be realized by hardware.

  The controller 92 controls the operation of the cine memory 60 in this embodiment. The cine memory 60 is constituted by a semiconductor memory or the like, in which a frame sequence is stored. Under the control of the control unit 92, loop reproduction or the like is performed on the frame sequence stored in them. For example, when a loop reproduction instruction is issued to the cine memory 60, the time-series frame sequence stored in the cine memory 60 is sequentially called and displayed as a moving image on the display 90.

  The input unit 94 is configured by an operation panel or the like, and by using the input unit 94, the user can set an end point, a reference point, a time phase, a display mode, and the like. In addition to being output to the control unit 92, the electrocardiographic signal output from the electrocardiograph 96 is output to the synthesis processing unit 88. The electrocardiogram signal is used as a synchronizing signal in the loop reproduction described above, and an electrocardiogram waveform is displayed on the display 90.

  The tracking process and the image forming process in this embodiment can be performed in real time. Further, the image data after freezing or the image data stored in the apparatus or on the external recording medium 54 may be processed.

  As described above, the preferred embodiment of the present invention has been described. By using the ultrasonic diagnostic apparatus according to the present embodiment, the Doppler information can be used in combination with the point inside the tissue that has been difficult to track only by the conventional pattern matching method. Can be tracked with higher accuracy. As a result, not only the myocardium but also the local motion of the tissue can be accurately measured.

It is a figure which shows the ultrasonic image containing the myocardium which is an object structure | tissue. It is a figure for demonstrating the change of the thickness of a myocardium. It is a flowchart which shows the tracking procedure of the reference point in this embodiment. It is a flowchart which shows the tracking procedure of the reference point in this embodiment. 1 is a functional block diagram of an ultrasonic diagnostic apparatus according to the present invention. It is a figure for demonstrating the formation process and strain calculation of a trace line. It is a figure for demonstrating the display image formed in this embodiment.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 1 Myocardium, 2 line segment, 3, 4 end point, 5 reference point, 66 end point tracking part, 68 reference point tracking part, 74 tracking line formation part.

Claims (8)

A wave transmitting / receiving means for obtaining an echo signal by forming an ultrasonic beam in a space including the target tissue;
In a data space composed of data obtained from echo signals, line segment setting means for setting a line segment for the target tissue for each frame by following the movement of the target tissue;
A specific part tracking means for tracking a specific part of a target tissue corresponding to a reference point set on a line segment of the reference frame over a plurality of frames;
Have
The hood tracking means, based on the speed of the ultrasonic beam direction at the reference points obtained from the echo signal of the reference frame, set the temporary movement point of the specific site on the segment of the frame of interest, the frame of interest on the basis of the ultrasound beam direction velocity at the reference point and the ultrasound beam direction of the velocity in said temporary mobile points obtained from the echo signal, sets the movement point of the specific site on the segment of the frame of interest,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
The specific part tracking means includes
In addition to the velocity of the ultrasonic beam direction at the reference point, the angle of the ultrasonic beam direction with respect to the line segment where the reference point is set ,
In addition to the velocity of the ultrasonic beam direction at the temporary moving point , using the angle of the ultrasonic beam direction with respect to the line segment where the temporary moving point is set ,
Set the moving point of the specific part on the line segment of the frame of interest;
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 2,
The specific part tracking means includes
Based on the speed of the ultrasonic beam direction at the reference point and the angle of the ultrasonic beam direction with respect to the line segment where the reference point is set, calculate the speed of the line segment direction at the reference point,
Based on the velocity in the ultrasonic beam direction at the temporary movement point and the angle in the ultrasonic beam direction with respect to the line segment where the temporary movement point is set, the velocity in the line segment direction at the temporary movement point is calculated. ,
And a line segment direction of the velocity at the reference point, and calculates a movement amount of the specific part based the on the average value of the two speeds of the line segment direction consisting of a line segment direction of the velocity, in the temporary moving point, the wherein setting the moving point of the specific portion on a line of the frame of interest based on the movement amount,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 2,
The hood tracking means, for line segments and the average value of the two speeds consisting of the ultrasonic beam direction of the velocity in the temporary moving point and the ultrasonic beam direction of the velocity at the reference point, the reference point is set the average value of the two angles made of an ultrasonic beam direction angle in the temporary moving point relative to the line segment angle with the temporary movement point of the ultrasound beam direction is set at the reference point, the movement of the specific part based on the calculates the amount of the set the moving point of the specific portion on a line of the frame of interest based on the movement amount,
An ultrasonic diagnostic apparatus. A wave transmitting / receiving means for obtaining an echo signal by forming an ultrasonic beam in a space including the myocardium;
In the data space composed of data obtained from echo signals, a segment connecting the myocardial intima specific part and the epicardial specific part is set, and the intima specific part and the epicardium that move with the movement of the myocardium are specified. Line segment setting means for tracking a part and setting a line segment for each frame;
A specific part tracking means for tracking a specific part in the myocardial tissue specified by a reference point set on a line segment of the reference frame over a plurality of frames;
Have
The hood tracking means, based on the speed of the ultrasonic beam direction at the reference points obtained from the echo signal of the reference frame, set the temporary movement point of the specific site on the segment of the frame of interest, the frame of interest on the basis of the ultrasound beam direction velocity at the reference point and the ultrasound beam direction of the velocity in said temporary mobile points obtained from the echo signal, sets the movement point of the specific site on the segment of the frame of interest,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 5,
The specific part tracking means uses the set moving point as a new temporary moving point, and the velocity of the ultrasonic beam direction at the new temporary moving point obtained from the echo signal of the frame of interest and the ultrasonic beam direction at the reference point Based on the speed of the above, reset the moving point of the specific part on the line segment of the frame of interest,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 6,
The line segment setting means tracks the intima specific part and the epicardial specific part by pattern matching processing for image data obtained from the echo signal,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 7,
The hood tracking means tracks across the inner membrane and the specific site plurality of frames corresponding to the boundary of the outer membrane of the myocardium identified by the reference point,
An ultrasonic diagnostic apparatus.

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