JP2007014542A - Ultrasonic diagnostic apparatus, and image processing device and method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide ultrasonic diagnostic apparatus, and an image processing device and method which are capable of highly precisely extracting a stable contour by eliminating an influence such as noise when extracting the contour in image data obtained from the subject. <P>SOLUTION: When generating contour data of time-series image data, a standard profile data generating section 71 sets prestored standard profile data in the first image data, an operation point moving region setting section 73 sets a moving region in the normal direction of the standard profile data relative to a plurality of operation points disposed by an operation point setting section 72 on the standard profile data. A boundary detecting section 75 calculates a representative pixel value to the operation points based on pixel values of operation point pixels corresponding to the operation points and adjacent pixels adjoining to the operation point pixels and having a prescribed number of pixels, and generates the contour data based on variation of the representative pixel value caused by the moving of the operation points along the moving region. An adjacent pixel setting section 74 updates (optimizes) the number of the adjacent pixels based on the profile of the contour data and generates the contour data of the image data of respective time phases continuing to the image data based on the updated number of pixels. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus, an image processing apparatus, and an image processing method that enable contour extraction of image data obtained from a subject.

  The ultrasonic diagnostic apparatus radiates an ultrasonic wave generated from an ultrasonic transducer built in the ultrasonic probe into the subject, and receives a reflected wave caused by a difference in acoustic impedance of the subject tissue by the ultrasonic probe. It can be displayed on a monitor and real-time two-dimensional images can be easily observed with a simple operation by simply bringing an ultrasonic probe into contact with the body surface, making it widely used for functional tests such as the heart and morphological diagnosis of various organs. It is used.

  In ultrasound diagnosis in the heart region, objective and quantitative evaluation of cardiac function is extremely important, and the measurement items include heart tissue motion speed, blood flow speed and disturbance, There are area and volume.

  In particular, the cardiac ejection fraction calculated from the change in intracardiac volume at the end diastole and end systole provides extremely useful information for evaluating cardiac function. This measurement of the intracardiac volume is conventionally performed by a myocardium in B-mode image data (hereinafter referred to as image data) of the heart obtained by a doctor or laboratory technician (hereinafter referred to as an operator) using an ultrasonic diagnostic apparatus. This is done by manually setting a contour line at the boundary between the heart and the heart chamber (myocardial / cardiac chamber boundary), and then applying the Modified-Simpson method based on the long axis in the heart chamber surrounded by the contour line. I came.

  The setting of the contour line for the ultrasound image data described above has not only caused a great load on the operator but also a factor that significantly reduces the diagnostic efficiency. A so-called ACT (Automated-Contour-Tracking) method has been developed (see, for example, Patent Document 1).

  In the automatic extraction method of the myocardial / heart chamber boundary described in Patent Document 1, for example, a plurality of operation points are arranged at predetermined intervals on a closed curve line set at a predetermined position in the heart chamber of the image data by the operator, The pixel value of the image data corresponding to the position of the operation point is continuously measured while moving each of the operation points radially toward the myocardium. Then, a position where the pixel value changes abruptly is detected as a myocardial / cardiac cavity boundary, and contour data is generated by connecting a plurality of detected boundary positions.

According to this method, the operator designates the position of the heart chamber to be measured with respect to the time-series image data displayed on the display unit of the ultrasonic diagnostic apparatus, whereby the heart chamber in each time phase is specified. The internal volume is measured, and the cardiac ejection fraction is calculated based on the intracardiac volume at the end diastole and the end systole.
JP 2000-217818 A

  According to the contour extraction method described in Patent Document 1, the amount of change in the pixel value is measured by sequentially reading out the pixel value of the image data corresponding to the position of the operation point that moves radially in the heart chamber, and this change Based on the amount, the boundary (myocardial / cardiac cavity boundary) between the heart chamber where the reflection of ultrasonic waves is small and the myocardium where reflection is relatively large is detected.

  By the way, non-stationary noise such as speckle noise or external noise generated by interference of reflected waves from myocardial tissue or blood cells in the heart chamber is mixed in the image data generated by the ultrasonic diagnostic apparatus. is doing. If the influence of these noises is significant in the pixel of the image data corresponding to the position of the operation point, there is a possibility that the myocardium / heart chamber boundary is detected erroneously. There is a problem that an unacceptable error occurs in the intracardiac volume and cardiac ejection fraction measured based on the above.

  The present invention has been made in view of the above-described problems, and its object is to achieve high accuracy by eliminating the influence of noise and the like when performing contour extraction on image data obtained on a subject. An object of the present invention is to provide an ultrasonic diagnostic apparatus, an image processing apparatus, and an image processing method that enable stable contour extraction.

  In order to solve the above-described problem, an image processing apparatus according to a first aspect of the present invention includes a standard shape data setting unit that sets standard shape data for image data obtained from a subject, and the standard shape data. An operation point setting means for arranging a plurality of operation points, an operation point movement area setting means for setting a movement area of the operation point, an operation point pixel of the image data corresponding to the operation point, and the operation point pixel A representative pixel value for the operation point is calculated based on pixel values of one or a plurality of adjacent pixels adjacent to each other, and the change amount of the representative pixel value accompanying the movement of the operation point along the movement region is calculated. Boundary detection means for detecting a tissue boundary in image data, and contour data generation means for generating contour data based on boundary information obtained by the boundary detection means .

  According to a second aspect of the present invention, there is provided an image processing apparatus of the present invention, comprising: an image data storage means for storing a plurality of time-series image data obtained for a subject; and the plurality of image data. Standard shape data setting means for setting standard shape data for the selected reference image data, operation point setting means for arranging a plurality of operation points for the standard shape data, and an operation for setting a movement area of the operation points A representative pixel value for the operation point based on a point movement area setting means, an operation point pixel of the reference image data corresponding to the operation point, and a pixel value of one or a plurality of adjacent pixels adjacent to the operation point pixel; Boundary detection means for detecting a tissue boundary in the reference image data from the amount of change of the representative pixel value accompanying the movement of the operation point along the movement area, and the boundary detection means Based on the obtained boundary information it is characterized by comprising a contour data generation means for generating outline data.

  On the other hand, an ultrasonic diagnostic apparatus of the present invention according to claim 13 includes an ultrasonic probe having an ultrasonic transducer that transmits and receives ultrasonic waves to and from a subject, and a transmission means for driving the ultrasonic transducer. A receiving unit that receives an ultrasonic wave reflected from the subject obtained by the ultrasonic transducer, and an image data generating unit that generates image data based on a reception signal obtained by the receiving unit. The ultrasonic diagnostic apparatus includes the image processing apparatus according to any one of claims 1 to 12 as a means for generating contour data in the image data.

  Furthermore, in the image processing method of the present invention according to claim 16, the standard shape data setting means sets the standard shape data for the desired image data, and the operation point setting means sets the standard shape data to the standard shape data. A step of arranging a plurality of operation points at a predetermined interval; a step of setting an operation point movement area setting unit; and a step of setting a movement area of the operation point; and a boundary detection unit setting the operation point at a predetermined position of the movement area. Calculating a representative pixel value for the operation point based on the corresponding operation point pixel of the image data and a pixel value of one or more adjacent pixels adjacent to the operation point pixel; and A step of detecting a tissue boundary in the image data from the amount of change in the representative pixel value accompanying the movement of the operation point along the movement region; It is characterized by having a step of generating outline data based on the boundary information obtained by the serial boundary detection means.

  According to the present invention, when performing contour extraction on image data obtained for a subject, highly accurate and stable contour extraction can be performed by eliminating the influence of noise and the like.

  Embodiments of the present invention will be described below with reference to the drawings.

  In the embodiment described below, when measuring the intracardiac volume and cardiac ejection rate for the subject based on the contour data of the myocardial / cardiac cavity boundary in the time-series image data obtained from the subject, Standard shape data of the myocardial / cardiac chamber boundary is set in the image data in the first time phase as image data, and further, linear operation point movement is performed with respect to a plurality of operation points arranged at predetermined intervals on the standard shape data. The region is set in a direction orthogonal to the standard shape data. Next, the representative pixel value corresponding to the operation point from the pixel values of the pixel corresponding to the operation point (operation point pixel) and a predetermined number of pixels (adjacent pixels) adjacent to the operation point pixel in the direction orthogonal to the operation point moving area. The contour data is generated based on the myocardial / cardiac cavity boundary detected from the change amount of the representative pixel value accompanying the movement of the operation point along the operation point moving region.

  Then, the operator optimizes the number of adjacent pixels while observing the influence (for example, continuity) of noise in the contour data superimposed and displayed on the image data, so that the operation point pixel and the optimized adjacent pixel Based on the representative pixel value calculated from the pixel value, contour data is generated for the reference image data and the image data of each time phase following the reference image data.

  In this embodiment, the contour extraction method for measuring the intracardiac volume and cardiac ejection fraction of the subject using time-series B-mode image data obtained by the ultrasonic diagnostic apparatus. However, the target image diagnostic apparatus, image data, measurement target, measurement purpose, and the like are not limited to these.

(Device configuration)
The configuration of the ultrasonic diagnostic apparatus according to this embodiment will be described with reference to FIGS. FIG. 1 is a block diagram showing the overall configuration of the ultrasonic diagnostic apparatus, and FIG. 2 is a block diagram of a transmission / reception unit and a received signal processing unit included in the ultrasonic diagnostic apparatus.

  The ultrasonic diagnostic apparatus 100 of the present embodiment illustrated in FIG. 1 transmits ultrasonic pulses to a subject and converts ultrasonic reflected waves (received ultrasonic waves) into electrical signals (received signals). The ultrasonic probe 3 having a child and a drive signal for transmitting an ultrasonic pulse in a predetermined direction of the subject are supplied to the ultrasonic transducer of the ultrasonic probe 3 and obtained from the ultrasonic transducer Transmission / reception unit 2 for phasing and adding reception signals of a plurality of channels, reception signal processing unit 4 for generating B mode data based on the reception signal after phasing addition, and B mode data obtained in units of scanning directions are sequentially stored. Thus, an image data storage unit 5 for generating two-dimensional image data (B-mode image data) is provided.

  In addition, the ultrasonic diagnostic apparatus 100 includes an image data selection unit 6 that selects time-series image data obtained in a predetermined period T0 from the image data of the subject stored in the image data storage unit 5; A contour tracing unit 7 that detects a myocardial / cardiac chamber boundary for each piece of selected image data and generates contour data based on positional information of the myocardial / cardiac chamber boundary, and a predetermined value based on the obtained contour data. A volume measuring unit 8 that measures the intracardiac volume in the time phase and an ejection rate calculating unit 9 that calculates the cardiac ejection rate based on the measured intracardiac volume at the end systole and end diastole are provided.

  Furthermore, the ultrasonic diagnostic apparatus 100 includes time-series image data stored in the image data storage unit 5, time-series image data for a predetermined period T 0 selected by the image data selection unit 6, and a contour trace unit 7. The display unit 10 for displaying the generated standard shape data and contour data of the myocardial / cardiac cavity boundary, the numerical value of the cardiac ejection rate calculated by the ejection rate calculation unit 9, and a selection instruction signal for image data The input unit 11 for specifying the position of the feature amount in the image data, and for temporarily setting or updating the number of adjacent pixels for calculating the representative pixel value of the operation point, which will be described later, and the above units. The system control part 12 which controls automatically is provided.

  The ultrasonic probe 3 has a plurality of ultrasonic transducers (not shown) arranged at the tip portion, and transmits and receives ultrasonic waves by bringing the tip portion into contact with the subject. Each of the ultrasonic transducers of the ultrasonic probe 3 is connected to the transmission / reception unit 2 via an Nx channel multi-core cable (not shown). The ultrasonic transducer is an electroacoustic transducer, which converts an electric pulse (driving signal) into an ultrasonic pulse (transmitting ultrasonic wave) at the time of transmission, and electrically converts an ultrasonic reflected wave (received ultrasonic wave) at the time of reception. It has a function of converting to a received signal.

  The ultrasonic probe 3 has a sector scan support, a linear scan support, a convex scan support, and the like, and the operator can arbitrarily select according to the diagnosis part. In the present embodiment, a case where an ultrasonic probe for sector scanning in which Nx ultrasonic transducers are arranged one-dimensionally is described, but the present invention is not limited to this.

  The transmitting / receiving unit 2 illustrated in FIG. 2 is configured to transmit a driving signal to the ultrasonic transducer of the ultrasonic probe 3 and to phase-tune the Nx channel received signal obtained from the ultrasonic transducer. A receiving unit 22 for performing addition is provided. The transmission unit 21 includes a rate pulse generator 211, a transmission delay circuit 212, and a drive circuit 213. The rate pulse generator 211 generates a rate pulse that determines the repetition period of the transmission ultrasonic wave. This is supplied to the transmission delay circuit 212.

  The transmission delay circuit 212 is composed of Nx-channel independent delay circuits equal in number to the ultrasonic transducers used for transmission, a focusing delay time for focusing the transmission ultrasonic waves to a predetermined depth, A deflection delay time for transmitting a sound wave in a predetermined direction is given to the rate pulse, and the rate pulse is supplied to the drive circuit 213. The drive circuit 213 has the same number of Nx-channel independent drive circuits as the transmission delay circuit 212, drives Nx ultrasonic transducers built in the ultrasonic probe 3, and enters the subject. Transmits ultrasonic waves.

  On the other hand, the receiving unit 22 includes an A / D converter 221 configured with Nx channels, a reception delay circuit 222, and an adder 223. An Nx channel received signal supplied from the ultrasonic transducer is A The digital signal is converted by the / D converter 221 and sent to the reception delay circuit 222. The reception delay circuit 222 determines a focusing delay time for focusing a received ultrasonic wave from a predetermined depth and a deflection delay time for setting a reception directivity with respect to a predetermined direction. The adder 223 adds the reception signals from the reception delay circuit 222 to each of the reception signals of the Nx channel output from. That is, the reception delay circuit 222 and the adder 223 perform phasing addition on the reception signal obtained from a predetermined direction.

  Next, the received signal processing unit 4 includes an envelope detector 411 and a logarithmic converter 412, and the envelope detector 411 envelopes the received signal after phasing addition supplied from the adder 223 of the receiving unit 22. Line detection is performed, and the amplitude of the envelope detection signal is logarithmically converted by a logarithmic converter 412 to generate B-mode data.

  Returning to FIG. 1, the image data storage unit 5 is a storage circuit for storing a plurality of pieces of image data obtained in time series by ultrasonic scanning on the subject. The B-mode data in the scanning direction unit generated by the reception signal processing unit 4 based on the reception signal obtained by the acoustic wave scanning is sequentially stored in the image data storage unit 5 to generate one piece of image data. Image data is generated and stored in a similar manner for a plurality of time phases following the phase. Further, image data collection conditions, time phase information, and the like are added to these image data as supplementary information.

  The image data selection unit 6 selects M images corresponding to the desired period T0 from the time-series image data stored in the image data storage unit 5 based on the selection instruction signal supplied from the input unit 11. Data P1 to PM are selected and stored in its own storage circuit (not shown). In this case, the operator sequentially displays the image data stored in the image data storage unit 5 on the monitor of the display unit 10, and among these image data, the first image data P1 and the last image data in a predetermined cycle T0. By specifying the PM using the input device of the input unit 11, the time-series image data P1 to PM can be easily selected, but may be selected by other methods.

  On the other hand, the contour trace unit 7 is formed of a closed curve based on the position information of the myocardial feature amount in the image data P1 (reference image data) among the time-series image data P1 to PM selected by the image data selection unit 6. A standard shape data generation unit 71 that generates standard shape data, an operation point setting unit 72 that arranges a plurality of operation points at predetermined intervals in the standard shape data or contour data described later, and a closed curve of the standard shape data or contour data An operation point moving region setting unit 73 that sets an operation point moving region in a direction perpendicular to the normal direction (normal direction), and an adjacent pixel setting unit 74 that sets adjacent pixels used to calculate a representative pixel value corresponding to each operation point. Furthermore, the representative pixel value is calculated based on the pixel value of the operation point pixel of the image data corresponding to the position of the operation point and the adjacent pixel set adjacent to the operation point pixel. A boundary detection unit 75 for detecting a myocardial / cardiac cavity boundary based on a change amount of the representative pixel value accompanying the movement of the operation point; and a myocardial / cardiac cavity boundary detected by the movement of the plurality of operation points. An outline data generation unit 76 that generates outline data based on the position information is provided.

  The standard shape data generation unit 71 includes a standard shape database 711 and a CPU 712. The standard shape database 711 includes image data collection conditions (for example, an ultrasonic scanning method, a scanning direction, or a scanning section for a diagnosis target organ (heart)). ) As a parameter, standard shape data of the myocardial / cardiac cavity boundary in the atrium or ventricle is stored in advance.

  On the other hand, the CPU 712 reads suitable standard shape data from the standard shape database 711 based on the image data collection condition added to the image data P1, and the input unit 11 further receives the image data P1 displayed on the display unit 10. The standard shape data is corrected for enlargement / reduction or rotation based on the positional information of the set myocardial feature quantities (ie, the annulus V1 and V2 and the apex V3).

  The corrected standard shape pattern is supplied to the display unit 10 via the system control unit 12 as necessary, and is superimposed on the image data P1 supplied from the image data selection unit 6.

  Next, the operation point setting unit 72 arranges operation points R1 to RN at predetermined intervals in the corrected standard shape data generated by the standard shape data generation unit 71 with respect to the image data P1. On the other hand, in the image data P2 to PM, operation points R1 to RN at predetermined intervals are set in the contour data generated by the boundary detection unit 75 described later for the image data P1 to P (M-1).

  Further, the operation point setting unit 72 sequentially moves the operation points R1 to RN along the linear operation point movement regions C1 to CN set by the operation point movement region setting unit 73. The operation points R1 to RN are preferably moved from the heart chamber in the myocardial direction along the operation point movement areas C1 to CN set in the image data P1 or the image data P2 to PM.

  On the other hand, the operating point moving area setting unit 73 sets the linear operating point moving areas C1 to CN with respect to the operating points R1 to RN in the normal direction of the closed curve forming the standard shape data or the contour data.

  FIG. 3 shows image data P1 of the left ventricle LV obtained by placing the tip of the ultrasound probe 3 in the vicinity of the apex of the subject. The operator uses the input device of the input unit 11 to set the image data P1. The standard shape data B1 generated by the standard shape data generating unit 71 based on the positional information of the annulus valve annulus V1, V2 and apex V3 and the placement information of the ultrasonic probe 3 is the myocardial / cardiac cavity in the left ventricle LV. Set near the boundary.

  On the other hand, FIG. 4 shows standard shape data B1 generated by the standard shape data generation unit 71 for the image data P1, and operation points R1 to RN arranged by the operation point setting unit 72 at predetermined intervals for the standard shape data B1. , Line segments C1 to CN indicating the operation point movement areas of the operation points R1 to RN set by the operation point movement area setting unit 73 are schematically shown.

  Next, the adjacent pixel setting unit 74 sets adjacent pixels centered on the operation point pixel corresponding to each of the operation points R1 to RN set (moved) at predetermined positions in the operation point movement regions C1 to CN. In this case, one or a plurality of adjacent pixels adjacent to the operation point pixel are set in a direction substantially perpendicular to the linear operation point moving areas C1 to CN. Further, the adjacent pixel setting unit 74 updates the number of adjacent pixels as needed based on the adjacent pixel increase / decrease instruction signal supplied from the input unit 11.

  The boundary detection unit 75 calculates the pixel values of the operation point pixel corresponding to the operation point set at a predetermined position in the operation point moving areas C1 to CN and the adjacent pixel adjacent to the operation point pixel set by the adjacent pixel setting unit 74. To calculate the representative pixel value. Then, representative pixel values are sequentially calculated corresponding to the operation points R1 to RN moving along the operation point movement regions C1 to CN, and the myocardial / cardiac cavity boundary is detected based on the change amount.

  Next, setting of adjacent pixels and calculation of representative pixel values performed by the above-described adjacent pixel setting unit 74 and boundary detection unit 75, and detection of a myocardial / cardiac cavity boundary will be described with reference to FIGS.

  FIG. 5 shows an adjacent pixel setting method based on the operation point pixel and a representative pixel value calculation method corresponding to the operation point pixel. However, here, in order to simplify the description, a case where the standard shape data B1 is set along the pixel arrangement direction of the image data P1 is shown. That is, in FIG. 5, the standard shape data B1 is set to the pixels a13 to ax3 arranged in the column direction (vertical direction) of the image data P1, and the operation points R1 and R2 in the standard shape data B1 are the pixels a33 and a83. Furthermore, the operation point moving areas C1 and C2 with respect to the operation points R1 and R2 are set in the pixels a31 to a35 and the pixels a81 to a85 arranged in the row direction (lateral direction) of the image data P1, respectively.

  For example, the operation point R1 moves from the pixel a31 to the pixel a35 in the operation point movement area C1, and the representative pixel value is sequentially calculated along with this movement. That is, when the operation point R1 is set to the first pixel a31, the adjacent pixel setting unit 74 is adjacent to the operation point moving region C1 in the direction perpendicular to the operation point moving region C1, for example, the pixels a11, a21, and a41. And a51 are set as adjacent pixels.

  Next, the boundary detection unit 75 uses the pixel value A31 of the operation point pixel a31 and the pixel values A11, A21, A41, and A51 of the adjacent pixels a11, a21, a41, and a51 set by the adjacent pixel setting unit 74 to set the pixel 31. The representative pixel value D31 corresponding to is calculated. In this case, the boundary detection unit 75 desirably calculates the representative pixel value D31 from the average of the pixel values A11 to A51. However, the boundary detection unit 75 is not particularly limited, and is, for example, the maximum value among the pixel values A11 to A51. May be used as the representative pixel value D31.

  Next, when the operation point R1 is set at the position of the pixel a32 by the operation point setting unit 72, the adjacent pixel setting unit 74 sets the pixels a12, a22, a42, and a45 as adjacent pixels, and the boundary detection unit 75 The representative pixel value D32 corresponding to the pixel 32 is calculated using the pixel values A12 to A52 of the pixels a12 to a52.

  Even when the operation point R1 is set at the positions of the pixels a33, a34, and a35, the representative pixel values D33, D34, and D35 corresponding to the pixels a33, a34, and a35 are calculated by the same procedure.

  Next, the boundary detection unit 75 detects the myocardial / cardiac cavity boundary based on the amount of change in the representative pixel values D31 to D35 obtained with the movement of the operation point R1 in the operation point movement region C1. FIG. 6 shows a specific example of a myocardial / cardiac chamber boundary detection method based on the amount of change in the representative pixel values D31 to D35. For example, the pixels a31 to a34 correspond to the heart chamber having a low reflection intensity. When the pixel a35 corresponds to a myocardial tissue having a relatively large reflection intensity, the representative pixel value in each of the pixels a31 to a35 exhibits change characteristics as shown in FIG. Then, the position showing the maximum amount of change in this change characteristic, that is, the boundary between the pixel 34 and the pixel 35 is detected as the myocardial / cardiac cavity boundary.

  Similarly, a representative pixel value is calculated by the same procedure for each of the operation points R2 to RN that move in the operation point movement areas C2 to CN, and the myocardium / heart chamber is based on the amount of change in the representative pixel value. A boundary is detected.

  In the above description, the operation point, the operation point moving region and the adjacent pixel are set and the myocardial / cardiac cavity boundary is detected based on the standard shape data B1 generated for the image data P1. As described above, with respect to the image data P2 to PM, each of the above settings and the myocardium / heart chamber are based on the contour data generated by the contour data generation unit 76 described later for the image data P1 to P (M-1). Boundary detection is performed.

  Returning to FIG. 1, the contour data generation unit 76 of the contour trace unit 7 detects the myocardium / heart chamber detected by the boundary detection unit 75 for each of the image data P1 to PM selected by the image data selection unit 6. The contour data is generated based on the boundary position information. Then, the generated contour data is supplied to the display unit 10 via the system control unit 12 so as to be superimposed on the image data P1 to PM.

  Next, the volume measuring unit 8 includes an arithmetic circuit and a storage circuit (not shown), and the arithmetic circuit measures the intracardiac volume based on the contour data in the image data P1 to PM generated by the contour data generating unit 76. To do.

  FIG. 7 shows a specific example of the intracardiac volume measurement performed by the volume measuring unit 8. In the volume measuring unit 8, the contour data generating unit 76 of the contour tracing unit 7 first sets the image data P1 to PM. The annulus is detected from the contour data E generated for each of the two, and the long axis FL of the heart is set based on the position of the annulus. Furthermore, a perpendicular line is drawn with respect to the long axis FL from a dividing point hj (j = 1 to J) obtained by dividing the long axis FL by an interval Δh, and between the two intersections f1j and f2j where the perpendicular intersects the contour data E. The length Xj (j = 1 to J) is calculated (see FIG. 7A).

  Next, the contents of the heart chamber in each time phase are applied by applying the so-called Modified-Simpson method, in which the volume is approximated by the sum of microcylinders with the lengths X1 to Xj obtained by the above procedure as the diameter and the preset Δh as the height. The product is measured (see FIG. 7B).

  The intracardiac volume of each time phase measured by the arithmetic circuit is stored in the storage circuit with the time phase as supplementary information.

On the other hand, the ejection fraction calculating unit 9 reads the intracardiac volume Vxs at the end systole and the intracardiac volume Vxd at the end diastole from the intracardiac volume data stored in the storage circuit of the volume measuring unit 8, Based on the formula (1), the cardiac ejection fraction Zx is calculated.
Zx = (Vxd−Vxs) / Vxd × 100 (%) (1)
Next, the display unit 10 displays time-series image data stored in the image data storage unit 5 or image data of a predetermined period T0 selected by the image data selection unit 6, and further, a contour trace unit 7, the standard shape data and contour data of the myocardial / cardiac cavity boundary generated in 7, and the numerical value of the cardiac ejection rate Zx calculated by the ejection rate calculation unit 9 are superimposed and displayed on the image data.

  The display unit 10 includes a display image data generation circuit, a conversion circuit, and a monitor (not shown). The display image data generation circuit is an image stored in the storage circuit of the image data storage unit 5 or the image data selection unit 6. After the data is subjected to processing such as scan conversion corresponding to a predetermined display form, additional information such as standard shape data and contour data is synthesized to generate display image data. The conversion circuit performs D / A conversion and television format conversion on the display image data generated by the display image data generation circuit and displays the display image data on the monitor.

  Then, the image data P1 to PM are selected based on the image data of the image data storage unit 5 displayed in time series on the monitor of the display unit 10, and further selected from these image data P1 to PM. Standard shape data is generated based on the image data P1. Further, the number of adjacent pixels is optimized based on the contour data superimposed and displayed on the image data P1.

  On the other hand, the input unit 11 includes an input device such as a liquid crystal display panel, a keyboard, a trackball, a mouse, and a lever on the operation panel, and inputs object information, initial setting of image data collection conditions and display conditions, and operation points. Initial setting of the arrangement interval and movement range, input of a selection instruction signal for the image data P1 to PM, setting of a feature amount position for the reference image data, provisional setting and updating of the number of adjacent pixels, and further generation of image data and various Inputs command signals for measurement.

(Image data generation procedure)
Next, the image data generation procedure in this embodiment will be described with reference to the flowchart of FIG.

  Prior to the generation of image data, the operator of the ultrasonic diagnostic apparatus 100 inputs subject information at the input unit 11 and further sets collection conditions and display conditions for image data (B-mode image data). Then, these input information and initial setting information are stored in the storage circuit of the system control unit 12 (step S1 in FIG. 8).

  When the above initial setting is completed, the operator inputs an image data generation start command at the input unit 11 (step S2 in FIG. 8), and this command signal is supplied to the system control unit 12, whereby Generation and storage of image data by the ultrasonic diagnostic apparatus 100 are started.

  When generating the image data, the rate pulse generator 211 of the transmission unit 21 shown in FIG. 2 determines the repetition period (rate period) of the transmission ultrasonic wave radiated into the subject according to the control signal from the system control unit 12. A rate pulse is generated and supplied to the transmission delay circuit 212. The transmission delay circuit 212 determines the delay time for focusing the ultrasonic wave to a predetermined depth in order to obtain a narrow beam width in transmission and the delay time for transmitting the ultrasonic wave in the first scanning direction θ1 as the rate pulse. The rate pulse is supplied to the Nx channel driving circuit 213.

  Next, the drive circuit 213 generates a drive signal based on the rate pulse supplied from the transmission delay circuit 212, supplies this drive signal to the Nx ultrasonic transducers in the ultrasonic probe 3, and supplies the drive signal inside the subject. Transmits ultrasonic waves in the θ1 direction.

  A part of the transmitted ultrasonic wave is reflected by the organ boundary surface or tissue of the subject with different acoustic impedance, and is received by the same ultrasonic transducer as that at the time of transmission and converted into an Nx channel electrical reception signal. Is done. Next, the received signal is converted into a digital signal by the A / D converter 221 of the receiving unit 22, and then the delay time for converging the received ultrasonic wave from a predetermined depth in the Nx channel reception delay circuit 222. And a delay time for setting a strong reception directivity with respect to the reception ultrasonic wave from the scanning direction θ1 is given and phased and added by the adder 223.

  Then, the envelope detector 411 and the logarithmic converter 412 of the reception signal processing unit 4 to which the reception signal after the phasing addition is supplied perform envelope detection and logarithmic conversion on the reception signal to obtain B-mode data. It is generated and stored in the image data storage unit 5 in FIG. 1 (step S3 in FIG. 8).

  When generation and storage of the B-mode data in the scanning direction θ1 is completed, the scanning direction θp (θp = θ1 + (p−1) Δθ (p = 2 to P) in which the transmission / reception direction of the ultrasonic wave is updated by Δθ in the θ direction. )), Ultrasonic waves are transmitted and received in the same procedure. At this time, the system control unit 12 updates the delay times of the transmission delay circuit 212 and the reception delay circuit 222 in accordance with the ultrasonic transmission / reception direction by the control signal.

  Then, B-mode data is generated by ultrasonic transmission / reception in the scanning directions θ2 to θP in the same manner as in the scanning direction θ1 (step S3 in FIG. 8), and these B-mode data are sequentially stored in the image data storage unit 5. Two-dimensional image data is generated (step S4 in FIG. 8).

  When the generation and storage of the image data in the first time phase are completed, the same procedure is repeated to generate the image data after the second time phase and store it in the image data storage unit 5. In this case, time-series two-dimensional image data to which image data collection conditions and time phase information are added is stored in the image data storage unit 5 (steps S3 and S4 in FIG. 8).

(Procedure for generating contour data and calculating cardiac ejection fraction)
Next, the procedure for generating contour data and the procedure for calculating the cardiac ejection rate calculated based on the contour data in this embodiment will be described with reference to the flowchart of FIG.

  The operator uses the input unit 11 to set an operation point arrangement interval and a moving range, and further to temporarily set the number of adjacent pixels (step S11 in FIG. 9), which are stored in the image data storage unit 5. A command signal for displaying the image data of the subject is input. The image data storage unit 5 that has received this command signal via the system control unit 12 supplies the image data stored in its own storage circuit to the display unit 10 and displays it as a moving image on the monitor.

  Next, the operator observes the image data displayed on the display unit 10, and generates an image data selection instruction signal by designating the first image data P1 and the last image data PM in the desired period T0. The data is supplied to the data selection unit 6. Then, the image data selection unit 6 reads out the time-series image data P1 to PM from the image data stored in the image data storage unit 5 based on the selection instruction signal, and temporarily stores them in its storage circuit. (Step S12 in FIG. 9).

  Next, the image data selection unit 6 reads the image data P1 stored in the storage circuit as reference image data, and displays it as a still image on the monitor of the display unit 10. Then, the operator who has observed the image data P1 displayed on the monitor of the display unit 10 inputs the positions of the annulus features V1 and V2 and the apex V3, which are myocardial feature amounts, with respect to the left ventricle of the image data P1. 11 is designated using the input device 11 (step S13 in FIG. 9).

  On the other hand, the standard shape data generation unit 71 reads out suitable standard shape data from the standard shape database 711 based on the image data collection condition added to the image data P1, and further adds the image data P1 displayed on the display unit 10 to the image data P1. On the other hand, correction processing such as enlargement / reduction or rotation is performed on the standard shape data based on the positional information of the myocardial feature amount (that is, the annulus V1 and V2 and the apex V3) designated by the input unit 11 (FIG. 9). Step S14).

  Then, the corrected standard shape data is supplied to the display unit 10 through the system control unit 12 as necessary, and is displayed on the monitor together with the image data P1 and the position information of the myocardial feature amount.

  Next, the operation point setting unit 72 arranges the operation points R1 to RN at predetermined intervals in the corrected standard shape data generated by the standard shape data generation unit 71 for the image data P1, and the operation point moving region setting unit. 73 sets the linear operation point movement areas C1 to CN with respect to the operation points R1 to RN in the normal direction of the standard shape data composed of closed curves based on the information of the initially set operation point movement range ( Step S15 in FIG. 9). Then, the operation point setting unit 72 sequentially moves the operation points R1 to RN from the inside of the heart chamber to the myocardial direction along the operation point movement regions C1 to CN set by the operation point movement region setting unit 73.

  That is, the operation point setting unit 72 first sets the operation points R1 to RN to the first operation point positions of the operation point movement areas C1 to CN (for example, positions corresponding to the pixels a31, a81,... In FIG. 5). Set. On the other hand, the adjacent pixel setting unit 74 sets the pixels of the image data P1 corresponding to the operation points R1 to RN set at the operation point positions in the operation point movement areas C1 to CN as operation point pixels, and further moves the operation point. One or a plurality of pixels adjacent to the operation point pixel in a direction substantially perpendicular to the regions C1 to CN are set as adjacent pixels (step S16 in FIG. 9). The above adjacent pixels are set based on the number of adjacent pixels temporarily set in the input unit 11.

  Then, the boundary detection unit 75 calculates a representative pixel value by using the operation point pixel corresponding to the first operation point position in each of the operation point movement regions C1 to CN and the pixel values of the adjacent pixels (FIG. 9). Step S17).

  Next, the operation point setting unit 72 moves the operation points R1 to RN to the second operation point positions (for example, positions corresponding to the pixels a32, a82,... In FIG. 5) in the operation point movement regions C1 to CN. Then, the adjacent pixel setting unit 74 sets the operation point pixels corresponding to the operation points R1 to RN moved to the operation point positions in the operation point movement areas C1 to CN and the adjacent pixels adjacent to the operation point pixels. Then, the boundary detection unit 75 calculates a representative pixel value using the operation point pixel corresponding to the second operation point position in each of the operation point movement areas C1 to CN and the pixel values of the adjacent pixels.

  Similarly, for the third and subsequent operation point positions, the representative pixel value is calculated based on the pixel values of the operation point pixel corresponding to this operation point position and its adjacent pixels (step S16 in FIG. 9). And S17).

  Next, the boundary detection unit 75 detects the position of the myocardial / heart chamber boundary based on the change amount of the representative pixel value calculated along with the movement of the operation points R1 to RN along the operation point movement regions C1 to CN (FIG. 9 step S18). On the other hand, the contour data generation unit 76 generates the contour data based on the position information of the myocardial / cardiac cavity boundary detected by the boundary detection unit 75 and supplies the contour data to the display unit 10 via the system control unit 12. Then, the display unit 10 superimposes the contour data on the image data P1 supplied from the image data selection unit 6 and displays it on the monitor (step S19 in FIG. 9).

  Next, the operator observes the contour data displayed on the monitor of the display unit 10 together with the image data P1. If the influence of noise or the like is recognized, the number of adjacent pixels is updated using a lever for increasing / decreasing the number of adjacent pixels provided on the operation panel of the input unit 11 (step S20 in FIG. 9). The pixel setting unit 74 updates the number of adjacent pixels for each operation point based on the updated number of adjacent pixels, and repeats the above-described steps S17 to S19. On the other hand, when the influence of noise or the like is not recognized in the contour data, the operator inputs a cardiac ejection ratio calculation start command from the input unit 11.

  The volume measuring unit 8 that has received the command signal via the system control unit 12 measures the intracardiac volume based on the contour data in the image data P1 generated by the contour data generating unit 76 (step of FIG. 9). S21).

  Next, the image data selection unit 6 reads the image data P2 stored in the storage circuit, and the operation point setting unit 72 has a predetermined interval in the contour data generated by the contour data generation unit 76 for the image data P1. Operation points R1 to RN are arranged. Then, the operating point moving area setting unit 73 sets linear operating point moving areas C1 to CN for the operating points R1 to RN, and the operating point setting unit 72 operates along the operating point moving areas C1 to CN. Points R1 to RN are sequentially moved from the heart chamber toward the myocardium (step S22 in FIG. 9).

  On the other hand, the adjacent pixel setting unit 74 sets the pixel of the image data P2 corresponding to the operation points R1 to RN moved along the operation point movement areas C1 to CN as the operation point pixel, and further to the image data P1. Set adjacent pixels with optimized number of pixels.

  In addition, the boundary detection unit 75 calculates a representative pixel value using the operation point pixel corresponding to each operation point position in the operation point moving areas C1 to CN and the pixel values of the adjacent pixels, and changes in the calculated representative pixel value Based on the quantity, the position of the myocardial / heart chamber boundary is detected. The contour data generation unit 76 generates the contour data based on the position information of the myocardial / cardiac cavity boundary detected by the boundary detection unit 75, and the volume measurement unit 8 generates the image generated by the contour data generation unit 76. The intracardiac volume is measured based on the contour data in the data P2 (steps S16 to S21 in FIG. 9).

  Thereafter, contour data of the myocardial / heart chamber boundary for the image data P3 to PM is generated by the same procedure, and the intracardiac volume is measured based on the contour data. Then, the measurement result of the intracardiac volume obtained from the image data P1 to PM is stored in its own storage circuit (steps S16 to S22 in FIG. 9).

  When the measurement of the intracardiac volume with respect to the image data P1 to PM is completed, the ejection fraction calculation unit 9 selects the intracardiac volume from the measurement results of the intracardiac volume stored in the storage circuit of the volume measurement unit 8 at the end diastole. The measurement result and the measurement result at the end systole are read out to calculate the cardiac ejection fraction (step S23 in FIG. 9). Then, the obtained cardiac ejection fraction data is supplied to the display unit 10 via the system control unit 12 and displayed on the monitor.

(Modification)
Next, a modification of the above embodiment will be described. In this modification, reference image data is used when measuring the intracardiac volume and the ejection fraction of the subject based on the contour data of the myocardial / cardiac cavity boundary in the time-series image data obtained from the subject. The standard shape data of the myocardial / cardiac cavity boundary is set in the image data in the first time phase as a linear operation point moving region with respect to a plurality of operation points arranged at predetermined intervals on the standard shape data. A direction perpendicular to the standard shape data is set.

  Next, pixel values of a predetermined number of pixels (adjacent pixels) adjacent to the operation point pixel in a direction orthogonal to the operation point moving area and a pixel corresponding to the operation point (operation point pixel) are read. Then, the number of adjacent pixels is updated so that a ratio of pixels having a pixel value larger than a preset threshold value among the read pixels is larger than a predetermined value, and the operation point pixel and the updated adjacent pixel are updated. A representative pixel value for the operation point is calculated from the pixel value. Then, contour data is generated based on the myocardial / cardiac cavity boundary detected from the amount of change in the representative pixel value accompanying the movement of the operation point.

  FIG. 10 shows the configuration of the ultrasonic diagnostic apparatus in this modification. The difference between the ultrasonic diagnostic apparatus 200 of this modification example and the ultrasonic diagnostic apparatus 100 of the above-described embodiment is that, in the former case, a pixel value comparison unit 77 and an adjacent pixel control unit 78 are provided instead of the adjacent pixel setting unit 74. It is that. In FIG. 10, units having substantially the same functions as the units of the ultrasonic diagnostic apparatus 100 shown in FIG.

  The ultrasonic diagnostic apparatus 200 of this modification shown in FIG. 10 includes an ultrasonic probe 3 including an ultrasonic transducer, a transmission / reception unit 2 that drives the ultrasonic transducer and performs phasing addition of a received signal, A reception signal processing unit 4 for generating mode data and an image data storage unit 5 for generating two-dimensional image data (B-mode image data) are provided. An image data selecting unit 6 for selecting image data, a contour tracing unit 7a for generating contour data of the myocardial / cardiac chamber boundary from these image data, and a volume for measuring the intracardiac volume based on the obtained contour data A measurement unit 8 and an ejection rate calculation unit 9 that calculates the cardiac ejection rate based on the intracardiac volume at the end systole and the end diastole are provided.

  In addition, the ultrasonic diagnostic apparatus 200 includes the image data stored in the image data storage unit 5, the image data selected by the image data selection unit 6, and the cardiac ejection rate calculated by the ejection rate calculation unit 9. A display unit 10 for displaying the numerical value of the image, an input unit 11 for inputting a selection instruction signal for image data, specifying a feature amount position in the image data, and the like, and a system control unit 12 for comprehensively controlling the above-described units. It has.

  The contour tracing unit 7a generates a standard shape data based on the position information of the feature amount in the image data P1 (reference image data) among the time-series image data P1 to PM selected by the image data selection unit 6. A shape data generation unit 71, an operation point setting unit 72 that arranges a plurality of operation points on the standard shape data at predetermined intervals, and an operation point movement region setting that sets an operation point movement region in the normal direction of the standard shape data Unit 73, the operation point pixel of the image data corresponding to the position of the operation point moving along the operation point moving region, and the pixel value and predetermined threshold value of a predetermined number of adjacent pixels set adjacent to the operation point pixel A pixel value comparison unit 77 that performs a comparison with the pixel value, and an adjacent pixel control that updates the number of pixels of the adjacent pixel so that a ratio of pixels having a pixel value larger than the threshold value is equal to or greater than a predetermined value 78, and further calculating a representative pixel value based on the operation point pixel of the image data corresponding to the position of the operation point and the pixel value of the adjacent pixel of the number of pixels updated by the adjacent pixel control unit 78, and A boundary detection unit 75 for detecting a myocardial / cardiac chamber boundary based on a change amount of the representative pixel value accompanying the movement, and a contour based on positional information of the myocardial / cardiac chamber boundary detected by the movement of the plurality of operation points. An outline data generation unit 76 for generating data is provided.

  The adjacent pixel control unit 78 sets the pixel of the image data P1 corresponding to the operation points R1 to RN set at the predetermined operation point positions in the operation point movement regions C1 to CN as the operation point pixel, and further moves the operation point. For example, two pixels adjacent to the operation point pixel in a direction substantially perpendicular to the regions C1 to CN are set as adjacent pixels. Next, the adjacent pixel control unit 78 sequentially increases the number of pixels of the adjacent pixels, reads out the pixel value of the adjacent pixels and the pixel value of the operation point pixel, and supplies them to the pixel value comparison unit 77.

  On the other hand, the pixel value comparison circuit 77 that has received the above-described pixel values from the adjacent pixel control unit 78 compares these pixel values with a preset threshold value, and the ratio of pixels having pixel values equal to or greater than the threshold value is determined. When the predetermined value is reached, the arrival signal is supplied to the adjacent pixel control unit 78. The adjacent pixel control unit 78 that has received the arrival signal performs optimization by stopping the increase in the number of adjacent pixels, and the boundary detection unit 75 performs a predetermined operation in each of the operation point moving regions C1 to CN. The representative pixel value is calculated using the operation point pixel corresponding to the point position and the pixel value of the adjacent pixel in which the number of pixels is optimized.

  Next, the representative pixel value is repeatedly calculated while moving the operation points R1 to RN along the operation point moving regions C1 to CN, and the boundary detection unit 75 performs the myocardial / increase based on the calculated change amount of the representative pixel value. The position of the heart chamber boundary is detected. The volume measuring unit 8 measures the intracardiac volume based on the contour data generated from the position information of the myocardial / cardiac boundary by the contour data generating unit 76, and the ejection rate calculating unit 9 calculates the intracardiac volume. The cardiac ejection fraction is calculated from the measured results using the measured results at the end diastole and the measured results at the end systole.

  According to the embodiment of the present invention described above, when the contour extraction of the myocardial / cardiac cavity boundary is performed by applying the ACT method to the B-mode image data obtained from the subject, the operation point position of the ACT method is set. A representative pixel value for the operation point is calculated from the corresponding operation point pixel and the pixel values of a plurality of adjacent pixels adjacent to the operation point pixel, and the myocardial / Since the heart chamber boundary is detected, the influence of the noise component included in each pixel is greatly reduced when the representative pixel value is calculated. Accordingly, the contour extraction accuracy of the myocardial / heart chamber boundary is improved, and the measurement accuracy for the intracardiac volume and the cardiac ejection fraction is further improved.

  In addition, since the influence of non-stationary noise is reduced, stable contour extraction is always possible, and diagnostic efficiency is improved.

  Furthermore, the contour data set at the myocardial / heart chamber boundary can be displayed superimposed on the image data, and the change in the contour data accompanying the increase or decrease in the number of adjacent pixels can be monitored. It is possible to easily set adjacent pixels.

  On the other hand, according to the above-described modification, the number of adjacent pixels is automatically optimized in consideration of the state of noise mixed in the image data, so that the load on the operator can be greatly reduced. The diagnostic efficiency is further improved. In particular, in the present modification, the number of adjacent pixels is optimized by statistically processing pixel values in a plurality of adjacent pixels, so that the contour is always highly accurate without depending on the experience and skill of the operator. Extraction is possible.

  As mentioned above, although the Example of this invention has been described, this invention is not limited to the above-mentioned Example, It can change and implement. For example, as described above, in this embodiment and its modification, time-series B-mode image data obtained by the ultrasonic diagnostic apparatus is used, and the volume of the heart chamber and the ejection fraction of the subject are measured. Although the contour extraction method for the purpose of measurement will be described, the target image diagnosis apparatus, image data, measurement target, measurement purpose, and the like are not limited to these.

  Moreover, although the case where the contour trace portion 7 in the above embodiment or the contour trace portion 7a in the above modification is provided in the ultrasonic diagnostic apparatus 100 or the ultrasonic diagnostic apparatus 200 has been described, for example, as shown in FIG. In addition, the image processing apparatus 300 for generating contour data may be configured together with the image data storage unit 5, the image data selection unit 6, the display unit 10, the input unit 11, and the system control unit 12.

  According to this method, since the image processing apparatus 300 is configured independently of the image diagnostic apparatus such as the ultrasonic diagnostic apparatus, the image processing apparatus 300 applies not only to the ultrasonic diagnostic apparatus but also to image data collected by other image diagnostic apparatuses. It is also possible to generate contour data. The image processing apparatus 300 may include a volume measuring unit 8 that measures the intracardiac volume and a ejection rate calculating unit 9 that calculates the cardiac ejection rate.

  On the other hand, in the above-described embodiment and its modification, the case where the adjacent pixel is set in the direction orthogonal to the operation point moving area has been described. However, the adjacent pixel may be set along the operation point moving area. . That is, by calculating the representative pixel value for the operation point using the pixel values of adjacent pixels that are two-dimensionally arranged around the operation point pixel, the representative pixel value is calculated based on many pixel values. Furthermore, stable contour data can be generated.

  In the above-described embodiment and its modification, the case where the first time phase image data P1 in the predetermined period T0 is used as the reference image data for setting the standard shape data has been described. However, the present invention is not limited to this. The image data may be any of image data P2 to PM. Furthermore, although the operation point moving region or the adjacent pixel is set in a straight line, it may be set along an arbitrary curve.

  On the other hand, when generating the contour data only for the purpose of calculating the cardiac ejection fraction, the image data selection unit 6 selects only the end-diastolic and end-systolic image data, and the contour data for these image data is selected. The processing efficiency can be improved by performing the generation and measurement of the intracardiac volume.

  Further, the standard shape data, the operation point, and the operation point moving area generated in the contour trace unit 7 or the contour trace unit 7a are not necessarily displayed on the display unit 10, but are displayed to confirm the processing process. Is also possible.

  When the update of the number of adjacent pixels in the above-described embodiment (step S20 in FIG. 9) is completed, the boundary detection unit 75 automatically calculates the representative pixel value based on the updated pixel value of the adjacent pixel. However, the calculation may be performed based on a calculation start instruction signal input by the operator through the input unit 11.

1 is a block diagram showing the overall configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention. The block diagram which shows the structure of the transmission / reception part and reception signal processing part with which the ultrasound diagnosing device of the Example is provided. The figure which shows the position of the feature-value designated in the reference | standard image data of the Example, and the standard shape data set based on this positional information. The figure which shows typically the standard shape data, the operation point, and the operation point movement area | region set to the reference | standard image data of the Example. The figure for demonstrating the setting method of the adjacent pixel on the basis of the operation point pixel in the Example, and the calculation method of the representative pixel value corresponding to this operation point pixel. The figure which shows the specific example of the detection method of the myocardial / cardiac cavity boundary based on the variation | change_quantity of the representative pixel value in the Example. The figure which shows the specific example of the volume measurement in the heart chamber in a present Example. 6 is a flowchart illustrating a procedure for generating image data according to the present exemplary embodiment. The flowchart which shows the outline data production | generation procedure and cardiac ejection fraction calculation procedure in a present Example. The block diagram which shows the whole structure of the ultrasound diagnosing device in the modification of a present Example. The block diagram of the image processing apparatus in the other modification of a present Example.

Explanation of symbols

DESCRIPTION OF SYMBOLS 2 ... Transmission / reception part 3 ... Ultrasonic probe 4 ... Reception signal processing part 5 ... Image data storage part 6 ... Image data selection part 7, 7a ... Contour trace part 8 ... Volume measurement part 9 ... Ejection rate calculation part 10 ... Display part DESCRIPTION OF SYMBOLS 11 ... Input part 12 ... System control part 21 ... Transmission part 22 ... Reception part 71 ... Standard shape data generation part 72 ... Operation point setting part 73 ... Operation point moving area setting part 74 ... Contour pixel setting part 75 ... Boundary detection part 76 ... Contour data generator 77 ... Pixel value comparator 78 ... Adjacent pixel controller 211 ... Rate pulse generator 212 ... Transmission delay circuit 213 ... Drive circuit 221 ... A / D converter 222 ... Reception delay circuit 223 ... Adder 411 ... Envelope detector 412 ... logarithmic converters 100 and 200 ... ultrasonic diagnostic apparatus 300 ... image processing apparatus

Claims (18)

Standard shape data setting means for setting standard shape data for image data obtained from a subject;
Operation point setting means for arranging a plurality of operation points for the standard shape data;
Operation point moving area setting means for setting a moving area of the operation point;
A representative pixel value for the operation point is calculated based on the operation point pixel of the image data corresponding to the operation point and the pixel value of one or a plurality of adjacent pixels adjacent to the operation point pixel, and along the moving region Boundary detecting means for detecting a tissue boundary in the image data from the amount of change in the representative pixel value accompanying the movement of the operation point;
An image processing apparatus comprising contour data generation means for generating contour data based on boundary information obtained by the boundary detection means. Image data storage means for storing a plurality of time-series image data obtained for a subject;
Standard shape data setting means for setting standard shape data for reference image data selected from the plurality of pieces of image data;
Operation point setting means for arranging a plurality of operation points for the standard shape data;
Operation point moving area setting means for setting a moving area of the operation point;
A representative pixel value for the operation point is calculated based on the operation point pixel of the reference image data corresponding to the operation point and the pixel value of one or more adjacent pixels adjacent to the operation point pixel, and Boundary detecting means for detecting a tissue boundary in the reference image data from the amount of change in the representative pixel value accompanying the movement of the operation point along;
An image processing apparatus comprising contour data generation means for generating contour data based on boundary information obtained by the boundary detection means.   Display means for displaying the contour data; input means for inputting a pixel number increase / decrease instruction signal for the adjacent pixels based on the shape of the displayed contour data; and the number of adjacent pixels based on the pixel number increase / decrease instruction signal. The image processing apparatus according to claim 1, further comprising an adjacent pixel setting unit for updating.   Pixel value comparison means for comparing the pixel values of the operation point pixel and the adjacent pixel with a predetermined threshold value, and the ratio of the pixel values of the operation point pixel and the adjacent pixel exceeding the threshold value is greater than or equal to a preset value The image processing apparatus according to claim 1, further comprising: an adjacent pixel control unit that updates the number of adjacent pixels.   The image processing apparatus according to claim 1, wherein the operation point moving area setting unit sets a linear moving area in a substantially normal direction of the standard shape data.   4. The image processing according to claim 3, wherein the adjacent pixel setting unit updates the number of pixels of the adjacent pixel at least in a direction substantially orthogonal to the movement region of the operation point based on the pixel number increase / decrease instruction signal. apparatus.   The adjacent pixel control unit updates the number of pixels of the adjacent pixel at least in a direction substantially orthogonal to the movement region of the operation point based on a comparison result between the operation point pixel and the pixel value of the adjacent pixel and the threshold value. The image processing apparatus according to claim 4.   The contour data generation means generates contour data for the image data or the reference image data based on the adjacent pixels updated by the adjacent pixel setting unit or the adjacent pixel control unit. The image processing apparatus according to claim 4.   The image processing apparatus according to claim 1, wherein the boundary detection unit calculates the representative pixel value by adding and averaging pixel values of the operation point pixel and the adjacent pixel.   3. The image processing according to claim 2, wherein the standard shape data setting means sets the standard shape data for first time phase image data among the plurality of time-series image data. apparatus.   The operation point setting means arranges the operation point with respect to the contour data of the reference image data generated by the contour data generation means when generating the contour data in the image data of a predetermined time phase. The image processing apparatus described.   The operation point setting means, when generating contour data in image data of a predetermined time phase, arranges the operation points with respect to the contour data of image data in the previous time phase generated by the contour data generation means. Item 12. The image processing apparatus according to Item 11. An ultrasonic probe having an ultrasonic transducer for transmitting and receiving ultrasonic waves to and from a subject;
An image based on a transmission means for driving the ultrasonic vibrator, a reception means for receiving an ultrasonic wave reflected from the subject obtained by the ultrasonic vibrator, and a reception signal obtained by the reception means In an ultrasonic diagnostic apparatus provided with image data generation means for generating data,
An ultrasonic diagnostic apparatus comprising the image processing apparatus according to any one of claims 1 to 12 as means for generating contour data in the image data.   14. The ultrasonic wave according to claim 13, further comprising a volume measuring unit, wherein the volume measuring unit measures an intracardiac volume based on contour data of a myocardial / cardiac cavity boundary generated by the contour data generating unit. Diagnostic device.   15. The ejection rate calculation unit is provided, and the ejection rate calculation unit calculates the cardiac ejection rate based on the intracardiac volume of a predetermined time phase measured by the volume measurement unit. Ultrasound diagnostic equipment. A standard shape data setting means for setting standard shape data for desired image data;
An operation point setting means for arranging a plurality of operation points at a predetermined interval with respect to the standard shape data;
An operation point moving region setting means for setting a moving region of the operation point;
Boundary detection means for the operation point based on the operation point pixel of the image data corresponding to the operation point at a predetermined position of the moving area and the pixel value of one or more adjacent pixels adjacent to the operation point pixel Calculating a representative pixel value;
The boundary detection means detecting a tissue boundary in the image data from the amount of change in the representative pixel value accompanying the movement of the operation point along the movement region;
An image processing method comprising: a step of generating contour data based on boundary information obtained by the boundary detection unit. Subsequent to the generation of the contour data, the display means displays the contour data superimposed on the image data;
An input means for inputting a pixel number increase / decrease instruction signal for the adjacent pixels based on the shape of the contour data displayed by the display means;
An adjacent pixel setting unit updating the number of adjacent pixels based on the pixel number increase / decrease instruction signal;
The image processing method according to claim 16, further comprising a step of updating the contour data for the image data based on the updated adjacent pixels. Subsequent to the generation of the contour data, a pixel value comparison unit compares the pixel values of the operation point pixel and the adjacent pixel of the image data with a predetermined threshold value;
An adjacent pixel control means updating the number of adjacent pixels so that a ratio at which the pixel value of the operation point pixel and the adjacent pixel exceeds the threshold is equal to or greater than a preset value;
18. The image processing method according to claim 17, further comprising a step of updating the contour data for the image data based on the updated adjacent pixels.

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