JP2011244931A - Ultrasonograph - Google Patents

Abstract

PROBLEM TO BE SOLVED: To reduce the load of an operator when scanning ultrasound in three dimensions.SOLUTION: In an ultrasonograph of one embodiment, a display controller 18a controls so as to display images (an MPR image and a volume image of perpendicular three cross-sections) generated from ultrasonic volume data in a monitor 2. A moving vector calculator 18b calculates a moving vector of three dimensional area of interest between the ultrasonic volume data generated in time series. Further, a moving amount calculator 18c calculates the moving amount of the three dimensional area of interest in the ultrasonic volume data newly generated based on the moving vector calculated by the moving vector calculator 18b. Furthermore, a controller 18d adjusts such that the positions of the areas of interest in the volume image displayed in a monitor 2 are substantially the same based on the moving amount calculated by the moving amount calculator 18c.

Description

  Embodiments described herein relate generally to an ultrasonic diagnostic apparatus.

  2. Description of the Related Art Conventionally, in an ultrasonic diagnostic apparatus, a two-dimensional ultrasonic image is taken by electronically delaying transmission / reception of ultrasonic waves in an ultrasonic probe in which a plurality of ultrasonic transducers are arranged in a line. In recent years, a mechanical scan probe that mechanically swings an ultrasonic probe in which a plurality of ultrasonic transducers are arranged in a row, or an ultrasonic probe in which a plurality of ultrasonic transducers are arranged in a matrix (lattice) shape. Therefore, an ultrasonic diagnostic apparatus that generates a three-dimensional ultrasonic image (volume image) in time series in substantially real time has been put into practical use (see, for example, Patent Document 1).

  Such an ultrasonic diagnostic apparatus can provide a volume image of a fetus in real time, for example, in a fetal growth diagnosis. Hereinafter, an example of a procedure for observing a fetal volume image will be described. For example, the operator applies a mechanical scan probe to a subject (pregnant woman), performs a two-dimensional scan, and identifies a position where the fetus can be seen well with a two-dimensional ultrasonic image. After specifying the position of the fetus, the operator fixes the position of the probe and adjusts the position and size of the three-dimensional region of interest for displaying the volume image. Specifically, the operator sets a two-dimensional region of interest in a two-dimensional ultrasound image, and further sets the swing angle of the mechanical scan probe, thereby setting the position and size of the three-dimensional region of interest. Adjust.

  Then, the operator turns on a 4D function for continuously performing three-dimensional imaging in time series. Thereby, the ultrasonic diagnostic apparatus generates and displays a volume image in a three-dimensional region of interest at a constant volume rate (for example, 1 to 10 volumes per second). In addition, the operator can view a volume image so that an object to be observed, such as a fetal face, can be seen from the front by a rotation axis set in a three-dimensional region of interest (for example, three axes orthogonal to the X, Y, and Z axes) Can be rotated. Here, the observation target may be difficult to observe due to artifacts caused by other tissues. For example, when observing the fetal face, artifacts caused by substances in the amniotic fluid prevent the fetal face from being displayed. For this reason, the operator adjusts various parameters such as the setting of the three-dimensional region of interest and the rotation position by the rotation axis so that only the observation target is displayed in a desired direction.

JP 2000-132664 A

  However, since an observation target such as a fetus always moves, after a while after adjustment, the observation target may deviate from the range of the displayed volume image, or the direction of the observation target may change. In such a case, the operator needs to adjust the parameters described above again, and the operation is complicated.

  The ultrasonic diagnostic apparatus according to the embodiment includes a display control unit, a movement vector calculation unit, a movement amount calculation unit, and an adjustment unit. The display control unit controls to display an image generated from the ultrasonic volume data on a predetermined display unit. The movement vector calculation unit calculates a movement vector of the region of interest between the ultrasonic volume data generated along the time series. The movement amount calculation unit calculates a movement amount of the region of interest in the newly generated ultrasonic volume data based on the movement vector calculated by the movement vector calculation unit. The adjustment unit adjusts the position of the region of interest in the image displayed on the predetermined display unit to be substantially the same based on the movement amount calculated by the movement amount calculation unit.

FIG. 1 is a diagram for explaining the configuration of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a diagram for explaining the configuration of the control unit and the internal storage unit according to the first embodiment. FIG. 3 is a diagram for explaining adjustment of a three-dimensional region of interest. FIG. 4 is a diagram for explaining an image generated from ultrasonic volume data. FIG. 5 is a diagram for explaining an example of a display form of an image generated from ultrasonic volume data. FIG. 6 is a diagram for explaining an example of the motion correction switch. FIG. 7 is a diagram for explaining the movement vector calculation unit and the movement amount calculation unit. FIG. 8 is a diagram (1) for explaining processing by the adjustment unit. FIG. 9 is a diagram (2) for explaining the processing by the adjustment unit. FIG. 10 is a diagram (3) for explaining processing by the adjustment unit. FIG. 11 is a flowchart for explaining processing of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 12 is a diagram for explaining an adjustment unit according to a modification. FIG. 13 is a diagram for explaining the configuration of the control unit and the internal storage unit according to the second embodiment. FIG. 14 is a flowchart for explaining processing of the ultrasonic diagnostic apparatus according to the second embodiment.

  Exemplary embodiments of an ultrasonic diagnostic apparatus disclosed in the present application will be described below in detail with reference to the accompanying drawings.

  First, the configuration of the ultrasonic diagnostic apparatus according to the first embodiment will be described. FIG. 1 is a diagram for explaining the configuration of the ultrasonic diagnostic apparatus according to the first embodiment. As shown in FIG. 1, the ultrasonic diagnostic apparatus according to the first embodiment includes an ultrasonic probe 1, a monitor 2, an input device 3, and an apparatus main body 10.

  The ultrasonic probe 1 contains a plurality of ultrasonic transducers in which a plurality of transducer cells are integrated. Each ultrasonic transducer generates an ultrasonic wave based on a drive signal supplied from a transmission / reception unit 11 included in the apparatus main body 10 to be described later, and receives a reflected wave from the subject P and converts it into an electric signal. The ultrasonic probe 1 includes a matching layer provided on the piezoelectric vibrator, a backing material that prevents propagation of ultrasonic waves from the piezoelectric vibrator to the rear, and the like.

  When ultrasonic waves are transmitted from the ultrasonic probe 1 to the subject P, the transmitted ultrasonic waves are reflected one after another at the discontinuous surface of the acoustic impedance in the body tissue of the subject P, and the ultrasonic probe is used as a reflected wave signal. 1 is received by a plurality of ultrasonic transducers. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance at the discontinuous surface where the ultrasonic wave is reflected. Note that the reflected wave signal when the transmitted ultrasonic pulse is reflected on the moving blood flow or the surface of the heart wall depends on the velocity component of the moving body in the ultrasonic transmission direction due to the Doppler effect. And undergoes a frequency shift.

  Here, the ultrasonic probe 1 according to the first embodiment is an ultrasonic probe capable of scanning the subject P in two dimensions with ultrasonic waves and scanning the subject P in three dimensions. Specifically, the ultrasonic probe 1 according to the first embodiment swings a plurality of ultrasonic transducers that scan the subject P two-dimensionally at a predetermined angle (swing angle), so that the subject It is a mechanical scan probe that scans P in three dimensions.

  In the first embodiment, the ultrasonic probe 1 is a two-dimensional ultrasonic probe capable of ultrasonically scanning the subject P in three dimensions by arranging a plurality of ultrasonic transducers in a matrix. Even if it is, it is applicable. The two-dimensional ultrasonic probe can scan the subject P in two dimensions by focusing and transmitting ultrasonic waves.

  The input device 3 includes a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, and the like, accepts various setting requests from an operator of the ultrasonic diagnostic apparatus, and accepts it to the apparatus main body 10. Transfer various setting requests. For example, the input device 3 according to the first embodiment includes a “motion correction switch” for turning ON / OFF a correction process described later.

  The monitor 2 displays a GUI (Graphical User Interface) for an operator of the ultrasonic diagnostic apparatus to input various setting requests using the input device 3, or displays an ultrasonic image generated in the apparatus main body 10. To do.

  The apparatus main body 10 is an apparatus that generates an ultrasonic image based on the reflected wave received by the ultrasonic probe 1. As shown in FIG. 1, the transmission / reception unit 11, the B-mode processing unit 12, and the Doppler processing unit 13. An image generation unit 14, an image memory 15, an image composition unit 16, an internal storage unit 17, and a control unit 18.

  The transmission / reception unit 11 includes a trigger generation circuit, a delay circuit, a pulsar circuit, and the like, and supplies a drive signal to the ultrasonic probe 1. The pulsar circuit repeatedly generates rate pulses for forming transmission ultrasonic waves at a predetermined rate frequency. The delay circuit also sets the delay time for each piezoelectric vibrator necessary for determining the transmission directivity by focusing the ultrasonic wave generated from the ultrasonic probe 1 into a beam shape, and for each rate pulse generated by the pulser circuit. Give to. The trigger generation circuit applies a drive signal (drive pulse) to the ultrasonic probe 1 at a timing based on the rate pulse. In other words, the delay circuit arbitrarily adjusts the transmission direction from the piezoelectric vibrator surface by changing the delay time given to each rate pulse.

  The transmission / reception unit 11 has a function capable of instantaneously changing a transmission frequency, a transmission drive voltage, and the like in order to execute a predetermined scan sequence based on an instruction from the control unit 18 described later. In particular, the change of the transmission drive voltage is realized by a linear amplifier type transmission circuit capable of instantaneously switching its value or a mechanism for electrically switching a plurality of power supply units.

  The transmission / reception unit 11 includes an amplifier circuit, an A / D converter, an adder, and the like, and performs various processes on the reflected wave signal received by the ultrasonic probe 1 to generate reflected wave data. The amplifier circuit amplifies the reflected wave signal for each channel and performs gain correction processing. The A / D converter performs A / D conversion on the gain-corrected reflected wave signal and gives a delay time necessary for determining reception directivity to the digital data. The adder performs an addition process of the reflected wave signal processed by the A / D converter to generate reflected wave data. By the addition processing of the adder, the reflection component from the direction corresponding to the reception directivity of the reflected wave signal is emphasized.

  As described above, the transmission / reception unit 11 controls transmission directivity and reception directivity in ultrasonic transmission / reception.

  The B-mode processing unit 12 receives reflected wave data that is a processed reflected wave signal that has been subjected to gain correction processing, A / D conversion processing, and addition processing from the transmission / reception unit 11, and performs logarithmic amplification, envelope detection processing, and the like. As a result, data (B mode data) in which the signal intensity is expressed by brightness is generated.

  The Doppler processing unit 13 performs frequency analysis on velocity information from the reflected wave data received from the transmission / reception unit 11, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and mobile body information such as average velocity, dispersion, and power. Is generated for multiple points (Doppler data).

  The B-mode processing unit 12 and the Doppler processing unit 13 according to the first embodiment can process both two-dimensional reflected wave data and three-dimensional reflected wave data. That is, the B-mode processing unit 12 according to the first embodiment generates two-dimensional B-mode data from the two-dimensional reflected wave data, and generates three-dimensional B-mode data from the three-dimensional reflected wave data. Further, the Doppler processing unit 13 according to the first embodiment generates two-dimensional Doppler data from the two-dimensional reflected wave data, and generates three-dimensional Doppler data from the three-dimensional reflected wave data. Hereinafter, the three-dimensional B-mode data and the three-dimensional Doppler data are referred to as “ultrasonic volume data”.

  The image generation unit 14 generates a B-mode image in which the intensity of the reflected wave is expressed by luminance from the B-mode data generated by the B-mode processing unit 12. Further, the image generation unit 14 generates an average velocity image, a dispersion image, a power image, or a Doppler image as a combination image representing the moving body information from the Doppler data generated by the Doppler processing unit 13 as an ultrasonic image. .

  Specifically, the image generation unit 14 generates a B-mode image that is a cross-sectional image from two-dimensional B-mode data, and generates a Doppler image that is a cross-sectional image from two-dimensional Doppler data. Further, the image generation unit 14 generates a volume image, which is a two-dimensional image reflecting three-dimensional information, from the ultrasonic volume data by rendering processing (for example, volume rendering processing or surface rendering processing). For example, the image generation unit 14 generates a volume image by setting a viewpoint at the position of the ultrasonic probe 1. The image generation unit 14 can generate an MPR (Multi Planar Reconstructions) image obtained by cutting the ultrasonic volume data along a predetermined cross section.

  The image generation unit 14 converts (scan converts) the scanning line signal sequence of the ultrasonic scan into a scanning line signal sequence of a video format typified by a television or the like, and generates an ultrasonic image as a display image. .

  The image composition unit 16 generates a composite image in which character information, scales, body marks, and the like of various parameters are combined with the ultrasonic image generated by the image generation unit 14 and outputs the composite image to the monitor 2 as a video signal.

  The image memory 15 is a memory that stores the ultrasonic image generated by the image generation unit 14 and the combined image generated by the image combining unit 16.

  The internal storage unit 17 stores a control program for performing ultrasonic transmission / reception, image processing, and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), various data such as a diagnostic protocol and various body marks. To do.

  The internal storage unit 17 is also used for storing images stored in the image memory 15 as necessary. The data stored in the internal storage unit 17 can be transferred to an external peripheral device via an interface (not shown).

  The control unit 18 controls the entire processing in the ultrasonic diagnostic apparatus. Specifically, the control unit 18 transmits and receives the transmission / reception unit 11 and the B mode based on various setting requests input from the operator via the input device 3 and various control programs and various data read from the internal storage unit 17. Control processing of the processing unit 12, Doppler processing unit 13, image generation unit 14, and image composition unit 16, and control to display the ultrasonic image and composite image stored in the image memory 15 on the monitor 2. .

  The overall configuration of the ultrasonic diagnostic apparatus according to the first embodiment has been described above. With this configuration, the ultrasonic diagnostic apparatus according to the first embodiment generates ultrasonic volume data along a time series, and generates a volume image and an MPR image from the ultrasonic volume data. Then, the ultrasonic diagnostic apparatus according to the first embodiment sequentially displays the rendering image and the MPR image that are sequentially generated along the time series on the monitor 2. Reduces the burden on the operator when scanning ultrasound in dimensions.

  In the following, in the fetal development diagnosis, a case will be described in which a volume image or an MPR image of a fetus in the uterus of a subject P to be observed is observed in real time. However, the first embodiment is applicable even when the observation target is an organ such as the liver or heart of the subject P.

  FIG. 2 is a diagram for explaining the configuration of the control unit and the internal storage unit according to the first embodiment. As illustrated in FIG. 2, the control unit 18 according to the first embodiment includes a display control unit 18a, a movement vector calculation unit 18b, a movement amount calculation unit 18c, and an adjustment unit 18d.

  The display control unit 18a controls the monitor 2 to display an image (for example, a two-dimensional B-mode image) generated from the two-dimensional reflected wave data. Further, the display control unit 18a performs control so that an image (volume image or MPR image) generated from the ultrasonic volume data is displayed on the monitor 2.

  In the first embodiment, in order to observe the fetal volume image and the MPR image in real time, the operator first scans the ultrasound in two dimensions by placing the ultrasound probe 1 on the subject P as in the prior art. . Thereby, the image generation unit 14 generates a two-dimensional ultrasonic image (two-dimensional B-mode image), and the display control unit 18a performs control so that the monitor 2 displays the two-dimensional ultrasonic image. .

  While referring to the image displayed on the monitor 2 under the control of the display control unit 18a, the operator moves the ultrasonic probe 1 so that the position of the ultrasonic probe 1 where the fetus can be seen well is displayed in a two-dimensional ultrasonic image. Identify. Then, after specifying the position of the fetus, the operator fixes the position of the ultrasonic probe 1 and adjusts the position and size of the three-dimensional region of interest for displaying the volume image.

  FIG. 3 is a diagram for explaining adjustment of a three-dimensional region of interest. First, the operator draws a region including the fetal head as shown in FIG. 3A in order to avoid, for example, artifacts caused by substances in amniotic fluid in the volume image. In the two-dimensional B-mode image, a region including the face of the fetus to be observed is set as a VOI (Volume Of Interest). Then, the operator sets the swing angle “α (alpha)” of the ultrasonic probe 1 as shown in FIG. As a result, a three-dimensional region of interest including the observation target is set. The swing angle is defined by the ultrasonic probe 1 such as 30 degrees, 60 degrees, and 90 degrees. For example, the operator sets “60 degrees” as the swing angle “α (alpha)”. Set.

  As a result, the parameters of the size and position of the VOI in the two-dimensional B-mode image, the swing angle, and the cross section (two-dimensional scan plane) that is the center of the swung scan plane are set. A three-dimensional region of interest is set. That is, the three-dimensional region of interest is a collection range of ultrasonic volume data. The parameters used for setting the three-dimensional region of interest are stored in the parameter data 17a of the internal storage unit 17 under the control of the display control unit 18a (see FIG. 2).

  Then, the operator inputs a request to start ultrasonic three-dimensional scanning (3D scanning) via the input device 3 in order to perform three-dimensional imaging continuously in time series. By such processing, for example, the B-mode processing unit 12 generates three-dimensional B-mode data in a three-dimensional region of interest at a constant volume rate (for example, 1 to 10 volumes per second). Then, the image generation unit 14 generates a volume image from the viewpoint set at the position of the ultrasonic probe 1 from the three-dimensional B-mode data. Further, the image generation unit 14 generates MPR images of three orthogonal cross sections (A plane, B plane, and C plane) from the three-dimensional B mode data. FIG. 4 is a diagram for explaining an image generated from ultrasonic volume data.

  First, as shown in FIG. 4, the A plane is a cross section constructed by the direction in which the ultrasonic transducers are arranged and the ultrasonic transmission direction in the mechanically oscillating ultrasonic probe 1. It is. The B surface is a cross section constructed in the direction in which the ultrasonic transducers are arranged and the swinging direction, as shown in FIG. The C plane is a cross section perpendicular to the ultrasonic transmission direction as shown in FIG. As a result, the image generation unit 14 generates an MPR image (A surface), an MPR image (B surface), and an MPR image (C surface) from the three-dimensional B-mode data, as shown in FIG. Note that the cross section for generating the MPR image is not limited to the A plane, the B plane, and the C plane, and can be arbitrarily set by the operator.

  Further, the image generation unit 14 generates a volume image from the three-dimensional B-mode data as shown in FIG. As described above, the volume image is generated from the viewpoint set at the position of the ultrasonic probe 1. Therefore, for example, when referring to a volume image in which the face of the fetus is viewed from the front as much as possible, the operator may want to rotate the volume image. In such a case, for example, the operator operates a toggle switch of the input device 3 and, as shown in FIG. 4, three axes orthogonal to the X, Y, and Z axes set in advance in a three-dimensional region of interest. Rotate the volume image to adjust the volume image from the desired position. For example, the three orthogonal axes of the X axis, the Y axis, and the Z axis are set such that the XY plane is the C plane, the YZ plane is the A plane, and the XZ plane is the B plane.

  FIG. 5 is a diagram for explaining an example of a display form of an image generated from ultrasonic volume data. For example, the display control unit 18a performs control so that the image composition unit 16 generates an image obtained by combining the MPR image (A surface), the MPR image (B surface), and the MPR image (C surface) with the volume image. Thereby, as shown in FIG. 5, the display control unit 18a displays the MPR image (A surface), the MPR image (B surface), the MPR image (C surface), and the volume image respectively at the upper left, upper right, lower left, and lower right. Is read from the image memory 15 and displayed on the monitor 2.

  As described above, the operator who refers to the composite image shown in FIG. 5 performs the rotation adjustment using the three orthogonal axes to adjust the rotation position. The determined rotational position is stored in the parameter data 17a shown in FIG. 2, for example, under the control of the display control unit 18a as a parameter for displaying the volume image.

  As a result, the parameter data 17a stores parameters for setting the collection range of the ultrasonic volume data and parameters for displaying the volume image.

  By performing the above setting, an image generated from the ultrasonic volume data is observed.

  Then, when the “motion correction switch” of the input device 3 is turned “ON”, the processing of the movement vector calculation unit 18b, the movement amount calculation unit 18c, and the adjustment unit 18d illustrated in FIG. 2 is started. FIG. 6 is a diagram for explaining an example of the motion correction switch.

  The motion correction switch is, for example, a touch panel, and as shown in FIG. 6, an ON switch for turning on the motion correction process, an OFF switch for turning off the motion correction process, and an interval for performing the motion correction process And an up / down arrow (spin button) for setting the update time. For example, the operator sets the update time to “1.0 sec” and then presses the ON switch.

  Here, when the ON switch is pressed, the control unit 18 stores information for the movement vector calculation unit 18b described later to perform processing in the image information data 17b of the internal storage unit 17. Specifically, the control unit 18 displays the MPR image (A surface), the MPR image (B surface), and the MPR image (C surface) displayed on the monitor 2 when the ON switch of the motion correction switch is pressed. Is stored in the image information data 17b as image information to be processed by the movement vector calculation unit 18b described later.

  Then, the movement vector calculation unit 18b shown in FIG. 2 calculates a movement vector of the three-dimensional region of interest between the ultrasonic volume data generated along the time series. Then, the movement amount calculation unit 18c illustrated in FIG. 2 calculates the movement amount of the three-dimensional region of interest in the newly generated ultrasonic volume data based on the movement vector calculated by the movement vector calculation unit 18b. . Hereinafter, the time when the ON switch of the motion correction switch is pressed is “t0”, and the time after the update time (for example, 1 second) from “t0” is “t1”. In addition, a time point after the update time from “t1” is set to “t2”. FIG. 7 is a diagram for explaining the movement vector calculation unit and the movement amount calculation unit.

  Specifically, the movement vector calculation unit 18b calculates a movement vector of a three-dimensional region of interest based on the image information of the image information data 17b. More specifically, the movement vector calculation unit 18b substantially matches the “MP0 image (A surface), MPR image (B surface), and MPR image (C surface) of“ t0 ”” stored in the image information data 17b. The positions of the three cross sections to be determined are determined by the ultrasonic volume data generated at “t1”. For example, the movement vector calculation unit 18b performs local cross-correlation processing to determine the position of three cross sections that substantially match the image information data 17b using the ultrasonic volume data of “t1”. Thereby, the movement vector calculation unit 18b calculates a movement vector of the three-dimensional region of interest between “t0” and “t1” as shown in FIG.

  That is, the movement vector calculation unit 18b calculates a movement vector by tracking processing using an MPR image. However, the first embodiment may be a case where the movement vector calculation unit 18b calculates a movement vector by cross-correlation processing between ultrasonic volume data. In such a case, the data stored in the image information data 17b is ultrasonic volume data generated at “t0”.

  When the calculation processing capability of the movement vector calculation unit 18b is low, the calculation amount can be reduced by thinning out the number of sample points per scanning line in the movement vector calculation process. On the other hand, when the calculation processing capability of the movement vector calculation unit 18b is high, a successive approximation method can be used for calculating the movement amount. The update time is set according to the level of calculation processing capability of the movement vector calculation unit 18b.

  Then, based on the movement vector between “t0” and “t1”, the movement amount calculation unit 18c performs 3 at “t2” on the three-dimensional region of interest at “t0” as shown in FIG. The amount of movement of the dimensional region of interest is calculated.

  By such processing of the movement vector calculation unit 18b and the movement amount calculation unit 18c, the movement amount of the three-dimensional region of interest in the sequentially generated ultrasonic volume data is sequentially calculated.

  Returning to FIG. 2, the adjustment unit 18 d makes the positions of the three-dimensional regions of interest in the volume image displayed on the monitor 2 substantially the same based on the movement amount calculated by the movement amount calculation unit 18 c. adjust. Specifically, the adjustment unit 18d changes the collection range of the newly generated ultrasonic volume data based on the movement amount calculated by the movement amount calculation unit 18c.

  More specifically, the adjustment unit 18d newly generates ultrasonic volume data by adjusting the position and size of the three-dimensional region of interest based on the movement amount calculated by the movement amount calculation unit 18c. Change the collection range. That is, the adjusting unit 18d updates the position and size of the VOI stored in the parameter data 17a and the cross section that is the center of the oscillated scanning plane based on the movement amount. Note that since the three-dimensional region of interest is a flexible living tissue, the region of interest may move with expansion, contraction, and twist as well as a parallel movement like a rigid body. In such a case, adjusting the size of the VOI is important in adjusting the collection area.

  Furthermore, the adjusting unit 18d adjusts the rotational position of the volume image with the rotation axis set in the three-dimensional region of interest based on the movement amount calculated by the movement amount calculating unit 18c. That is, the adjusting unit 18d updates the parameter (rotation position) for displaying the volume image stored at the time when the ON switch of the motion correction switch is pressed based on the movement amount.

  8-10 is a figure for demonstrating the process by an adjustment part. For example, when the fetus moves within the uterus of the subject P, as shown in FIG. 8, the face of the fetus in the volume image deviates from the position displayed at the time “t0”.

  However, since the movement amount of the three-dimensional region of interest in the newly generated ultrasonic volume data is estimated by the processing of the movement amount calculation unit 18c described above, the adjustment unit 18d is configured as shown in FIG. Adjust the position and size of the VOI. For example, in the example shown in FIG. 9, the adjusted VOI position is adjusted to rotate counterclockwise from the VOI position in FIG. The adjusting unit 18d adjusts the cross section that is the center of the oscillating scanning surface. Further, the adjusting unit 18d adjusts the collection range so that the volume image of the ultrasonic volume data newly generated substantially matches the direction of the volume image displayed at the time “t0”. Adjust the rotation position.

  By the adjustment process of the adjustment unit 18d, three-dimensional ultrasonic volume data in which the collection range is adjusted is generated, and a three-section MPR image and a volume image are generated. Then, as shown in FIG. 10, the volume image displayed under the control of the display control unit 18a substantially matches the state when the ON switch of the motion correction switch is pressed.

  When the OFF switch of the correction switch is pressed, the processing by the movement vector calculation unit 18b, the movement amount calculation unit 18c, and the adjustment unit 18d is stopped.

  Next, processing of the ultrasonic diagnostic apparatus according to the first embodiment will be described with reference to FIG. FIG. 11 is a flowchart for explaining processing of the ultrasonic diagnostic apparatus according to the first embodiment.

  As illustrated in FIG. 11, the ultrasonic diagnostic apparatus according to the first embodiment determines whether a request for starting a 2D scan (two-dimensional scan using ultrasonic waves) for performing an inspection has been received (step S <b> 101). Here, when the 2D scan start request is not accepted (No in step S101), the ultrasonic diagnostic apparatus enters a standby state.

  On the other hand, when a 2D scan start request is received (Yes in step S101), the 2D scan is executed under the control of the control unit 18 (step S102). Thereby, the image generation unit 14 generates a 2D ultrasonic image.

  Then, the display control unit 18a controls to display the 2D ultrasonic image generated by the 2D scan on the monitor 2 (step S103). Then, the display control unit 18a determines whether or not the setting of the collection range of ultrasonic volume data that is a three-dimensional region of interest has been received from the operator (step S104). That is, the display control unit 18a determines whether or not the parameters of the size and position of the VOI, the swing angle, and the cross section (two-dimensional scan plane) that is the center of the scanned scan plane are set. .

  Here, when the collection range is not set (No at Step S104), the display control unit 18a returns to Step S103 and continues the display control process of the 2D ultrasonic image.

  On the other hand, when the collection range is set (Yes at Step S104), the control unit 18 determines whether or not a start request for 3D scanning (three-dimensional scanning using ultrasonic waves) has been received (Step S105). Here, when the 3D scan start request is not accepted (No at Step S105), the ultrasonic diagnostic apparatus enters a standby state.

  On the other hand, when the 3D scan start request is received (Yes at Step S105), the control unit 18 starts the 3D scan within the collection range received at Step S105 (Step S106). Thereby, ultrasonic volume data is sequentially generated, and the image generation unit 14 sequentially generates MPR images and volume images of three orthogonal cross sections. Then, the display control unit 18a controls the monitor 2 to sequentially display a composite image of each image generated from the ultrasonic volume data.

  Then, the display control unit 18a determines whether or not an adjustment of the rotational position of the volume image by three orthogonal axes has been received from the operator (step S107). Here, when the adjustment of the rotational position is not accepted (No at Step S107), the ultrasonic diagnostic apparatus is in a standby state.

  On the other hand, when the adjustment of the rotation position is received (Yes at Step S107), the display control unit 18a sets the parameter for setting the collection range of the ultrasonic volume data and the parameter for the rotation position for displaying the volume image as the parameter data. 17a is stored (step S108). Note that the parameter for setting the collection range of the ultrasonic volume data may be stored in the parameter data 17a when step S104 is positive.

  Then, the display control unit 18a controls the monitor 2 to display a composite image of each image (MPR image and volume image having three orthogonal cross sections) generated from the ultrasonic volume data (step S109). Note that the processing from step S101 to step S109 is a procedure conventionally performed in observation by ultrasonic 3D scanning.

  After that, the control unit 18 determines whether or not a correction start request has been received by pressing the ON switch of the motion correction switch together with the setting of the update time (step S110). If a correction start request is received (Yes at step S110), the display control unit 18a stores the image information of the MPR image of the three orthogonal cross sections at the time when the correction start request is received in the image information data 17b (step S111). ).

  Then, the movement vector calculation unit 18b determines whether or not the update time has elapsed (step S112). If the update time has not elapsed (No at Step S112), the movement vector calculation unit 18b waits until the update time elapses.

  On the other hand, when the update time has elapsed (Yes at Step S112), the movement vector calculation unit 18b calculates a movement vector of the three-dimensional region of interest between the ultrasound volume data based on the image information data 17b, and moves The amount calculation unit 18c calculates the amount of movement of the three-dimensional region of interest in the newly generated ultrasonic volume data based on the movement vector (step S113).

  Then, the adjusting unit 18d adjusts the parameter stored in the parameter data 17a based on the movement amount (step S114). That is, the adjusting unit 18d adjusts the position and size of the VOI, the cross section that is the center of the oscillating scanning surface, and the rotational position.

  Then, the display control unit 18a performs control so that the composite image generated from the parameter-adjusted ultrasonic volume data is displayed on the monitor 2 (step S115).

  After step S115 or when a correction start request is not received (No at step S110), the control unit 18 determines whether an inspection end request is received (step S116). Here, when the inspection end request is received (Yes at Step S116), the control unit 18 ends the process.

  On the other hand, when the inspection end request is not accepted (No at Step S116), the control unit 18 determines whether correction is being performed (Step S117). Here, when the correction process is not in progress (No at Step S117), the control unit 18 returns to Step S110 and performs a determination process as to whether a correction start request has been accepted.

  On the other hand, when the correction process is being performed (Yes at Step S117), the process returns to Step S112, and the movement vector calculation unit 18b determines whether or not the update time has elapsed.

  Note that the image information stored in step S111 may be updated to the MPR image having three orthogonal cross sections displayed in step S115.

  As described above, in the first embodiment, the display control unit 18a controls the monitor 2 to display an image (MPR image and volume image of three orthogonal cross sections) generated from the ultrasonic volume data. The movement vector calculation unit 18b calculates a movement vector of the three-dimensional region of interest between the ultrasonic volume data generated along the time series. Then, the movement amount calculation unit 18c calculates the movement amount of the three-dimensional region of interest in the newly generated ultrasonic volume data based on the movement vector calculated by the movement vector calculation unit 18b. Then, the adjustment unit 18d adjusts the position of the region of interest in the volume image displayed on the monitor 2 to be substantially the same based on the movement amount calculated by the movement amount calculation unit 18c.

  Therefore, according to the first embodiment, even if the three-dimensional region of interest to be observed moves, it is not necessary to adjust the parameters again, so that the burden on the operator when scanning ultrasound in three dimensions is reduced. It becomes possible to do. Further, according to the first embodiment, it is not necessary to adjust the parameters again, so that the inspection time can be shortened and the inspection efficiency can be improved.

  In the first embodiment, the adjustment unit 18d changes the collection range of the newly generated ultrasonic volume data based on the movement amount calculated by the movement amount calculation unit 18c. Therefore, according to the first embodiment, it is possible to generate ultrasonic volume data that always includes a three-dimensional region of interest to be observed.

  In the first embodiment, the adjustment unit 18d adjusts the position and size of the three-dimensional region of interest based on the movement amount calculated by the movement amount calculation unit 18c. Change the data collection range. Furthermore, the adjusting unit 18d adjusts the rotational position of the volume image with the rotation axis set in the three-dimensional region of interest based on the movement amount calculated by the movement amount calculating unit 18c. Therefore, according to the first embodiment, the rotational position of the volume image can be automatically adjusted to a position desired by the operator, and the burden on the operator when scanning ultrasonic waves in three dimensions is further reduced. It becomes possible.

  In the first embodiment, the movement vector calculation unit 18b starts the movement vector calculation process when a correction request is received via the motion correction switch of the input device 3. Therefore, according to the first embodiment, it is possible to avoid the inadvertent correction process and to start the correction process at the operator's discretion.

  The adjustment process by the adjustment unit 18d is not limited to the above-described first embodiment, and may be executed by a modification described below. That is, when the adjustment unit 18d in the modification is determined that only the direction of the three-dimensional region of interest in the newly generated ultrasonic volume data is different based on the movement amount calculated by the movement amount calculation unit 18c. Then, the rotational position of the rotational axis set in the three-dimensional region of interest is adjusted. FIG. 12 is a diagram for explaining an adjustment unit according to a modification.

  For example, it is assumed that the direction of the volume image of the fetal face shown in FIG. 12A is a desired direction that the operator wants to refer to. Then, as shown in the left diagram of FIG. 12B, the adjusting unit 18d includes the three-dimensional region of interest in the newly generated ultrasonic volume data, but only the direction of the three-dimensional region of interest is included. When it is determined that they are different from each other by the movement amount, the adjusting unit 18d does not perform the collection range changing process. Then, as illustrated in the left diagram of FIG. 12B, the adjustment unit 18d rotates the volume image generated by the image generation unit 14 from the newly generated ultrasonic volume data about the Z axis. As a result of this processing, the volume image generated from the newly generated ultrasonic volume data substantially matches the direction of the volume image shown in FIG. 12A, as shown in the right diagram of FIG. Will be.

  Therefore, in this modification, the number of adjustment processes when there is no need to change the collection range can be reduced.

  In the second embodiment, a case where the correction process is stopped based on the movement amount will be described with reference to FIG. FIG. 13 is a diagram for explaining the configuration of the control unit and the internal storage unit according to the second embodiment.

  As shown in FIG. 13, the control unit 18 and the internal storage unit 17 according to the second embodiment are compared with the control unit 18 and the internal storage unit 17 according to the first embodiment described with reference to FIG. The point which further has the part 18e and threshold value data 17c differs. Hereinafter, these will be mainly described.

  The collection range of the ultrasonic volume data by the ultrasonic probe 1 is limited by the upper limit value of the swing angle. Therefore, when the movement amount becomes larger than the predetermined threshold value, ultrasonic volume data including a three-dimensional region of interest cannot be generated even if the collection range is adjusted. Therefore, the threshold value data 17c stores in advance a threshold value corresponding to the movement amount at which the collection range cannot be adjusted.

  Then, the determination unit 18e determines whether or not the movement amount calculated by the movement amount calculation unit 18c is larger than the threshold value stored in the threshold value data 17c.

  Here, when the determination unit 18e determines that the movement amount is equal to or less than the threshold value, the adjustment unit 18d performs the adjustment process described in the first embodiment. On the other hand, when the determination unit 18e determines that the movement amount is larger than the threshold value, the display control unit 18a controls the monitor 2 to display that the movement amount is larger than the predetermined threshold value. For example, the display control unit 18a controls to display a warning that “the upper limit of correction has been exceeded”. Further, the control unit 18 stops the 3D scan, and shifts to the 2D scan mode so that the operator again sets the collection range by the 2D scan.

  Next, processing of the ultrasonic diagnostic apparatus according to the second embodiment will be described with reference to FIG. FIG. 14 is a flowchart for explaining processing of the ultrasonic diagnostic apparatus according to the second embodiment.

  As illustrated in FIG. 14, the ultrasonic diagnostic apparatus according to the second embodiment determines whether or not a 2D scan start request for performing an inspection has been received (step S <b> 201). Here, when the 2D scan start request is not accepted (No in step S201), the ultrasonic diagnostic apparatus enters a standby state.

  On the other hand, when a 2D scan start request is received (Yes in step S201), the 2D scan is executed under the control of the control unit 18 (step S202).

  Then, the display control unit 18a controls to display the 2D ultrasonic image generated by the 2D scan on the monitor 2 (step S203). Then, the display control unit 18a determines whether or not the setting of the collection range of ultrasonic volume data that is a three-dimensional region of interest has been received from the operator (step S204).

  Here, when the collection range is not set (No at Step S204), the display control unit 18a returns to Step S203 and continues the display control process of the 2D ultrasonic image.

  On the other hand, when the collection range is set (Yes at Step S204), the control unit 18 determines whether or not a 3D scan start request is received (Step S205). If the 3D scan start request is not accepted (No at Step S205), the ultrasonic diagnostic apparatus is in a standby state.

  On the other hand, when the 3D scan start request is received (Yes at Step S205), the control unit 18 starts the 3D scan within the collection range received at Step S205 (Step S206).

  Then, the display control unit 18a determines whether or not an adjustment of the rotational position of the volume image by three orthogonal axes has been received from the operator (step S207). Here, when the adjustment of the rotational position is not accepted (No at Step S207), the ultrasonic diagnostic apparatus enters a standby state.

  On the other hand, when adjustment of the rotational position is accepted (Yes at Step S207), the display control unit 18a stores various parameters in the parameter data 17a (Step S208).

  Then, the display control unit 18a controls the monitor 2 to display a composite image of each image (MPR image and volume image having three orthogonal cross sections) generated from the ultrasonic volume data (step S209).

  After that, the control unit 18 determines whether or not a correction start request has been received (step S210). Here, when the correction start request is received (Yes at Step S210), the display control unit 18a stores the image information of the MPR image of the three orthogonal sections at the time when the correction start request is received in the image information data 17b (Step S211). ).

  Then, the movement vector calculation unit 18b determines whether or not the update time has elapsed (step S212). If the update time has not elapsed (No at Step S212), the movement vector calculation unit 18b waits until the update time elapses.

  On the other hand, when the update time has elapsed (Yes at Step S212), the movement vector calculation unit 18b calculates a movement vector of the three-dimensional region of interest between the ultrasound volume data based on the image information data 17b, and moves The amount calculation unit 18c calculates the amount of movement of the three-dimensional region of interest in the newly generated ultrasonic volume data based on the movement vector (step S213).

  Then, the determination unit 18e determines whether or not the movement amount calculated by the movement amount calculation unit 18c is larger than the threshold value stored in the threshold value data 17c (step S214). Here, when the determination unit 18e determines that the movement amount is larger than the threshold (Yes at Step S214), the display control unit 18a controls to display a warning on the monitor 2 (Step S219). 18 controls to stop the 3D scan, return to step S202, and execute the 2D scan.

  On the other hand, when the determination unit 18e determines that the movement amount is equal to or less than the threshold (No at Step S214), the adjustment unit 18d adjusts the parameter stored in the parameter data 17a based on the movement amount (Step S215).

  Then, the display control unit 18a performs control so that the composite image generated from the parameter-adjusted ultrasonic volume data is displayed on the monitor 2 (step S216).

  After step S216 or when a correction start request is not received (No at step S210), the control unit 18 determines whether an inspection end request has been received (step S217). Here, when the inspection end request is received (Yes at Step S217), the control unit 18 ends the process.

  On the other hand, when the inspection end request is not accepted (No at Step S217), the control unit 18 determines whether correction is being performed (Step S218). Here, when the correction process is not in progress (No at Step S218), the control unit 18 returns to Step S210 and performs a determination process as to whether or not a correction start request has been accepted.

  On the other hand, when the correction process is being performed (Yes at Step S218), the process returns to Step S212, and the movement vector calculation unit 18b determines whether or not the update time has elapsed.

  As described above, in the second embodiment, the operator can easily recognize that the correction process is impossible because the observation target has moved greatly, and the collection range can be set again. It is possible to avoid a decrease in inspection efficiency. In the second embodiment, when the correction process becomes impossible, the process can be automatically shifted to the 2D scan, so that the operator's process can be reduced.

  As described above, according to the first and second embodiments, it is possible to reduce the burden on the operator when scanning ultrasound in three dimensions.

DESCRIPTION OF SYMBOLS 1 Ultrasonic probe 2 Monitor 3 Input apparatus 10 Apparatus main body 11 Transmission / reception part 12 B mode process part 13 Doppler process part 14 Image generation part 15 Image memory 16 Image composition part 17 Internal storage part 17a Parameter data 17b Image information data 18 Control part 18a Display control unit 18b Movement vector calculation unit 18c Movement amount calculation unit 18d Adjustment unit

Claims (6)

A display control unit that controls to display an image generated from the ultrasonic volume data on a predetermined display unit;
A movement vector calculation unit for calculating a movement vector of a region of interest between ultrasonic volume data generated along a time series;
Based on the movement vector calculated by the movement vector calculation unit, a movement amount calculation unit that calculates a movement amount of a region of interest in newly generated ultrasound volume data;
An adjustment unit configured to adjust the position of the region of interest in the image displayed on the predetermined display unit to be substantially the same based on the movement amount calculated by the movement amount calculation unit;
An ultrasonic diagnostic apparatus comprising:   The ultrasonic wave according to claim 1, wherein the adjustment unit changes a collection range of the newly generated ultrasonic volume data based on the movement amount calculated by the movement amount calculation unit. Diagnostic device.   The adjustment unit changes the collection range of the newly generated ultrasonic volume data by adjusting the position and size of the region of interest based on the movement amount calculated by the movement amount calculation unit. The ultrasonic diagnostic apparatus according to claim 2, further comprising adjusting a rotation position of the image by a rotation axis set in the region of interest.   When the adjustment unit determines that only the direction of the region of interest in the newly generated ultrasonic volume data is different based on the amount of movement calculated by the amount of movement calculation unit, the adjustment unit is set to the region of interest. The ultrasonic diagnostic apparatus according to claim 1, wherein the rotational position of the rotating shaft is adjusted. A determination unit that determines whether the movement amount calculated by the movement amount calculation unit is greater than a predetermined threshold;
The display control unit controls the predetermined display unit to display that the moving amount is larger than the predetermined threshold when the determining unit determines that the moving amount is larger than the predetermined threshold. The ultrasonic diagnostic apparatus according to claim 1, wherein:   The said movement vector calculation part starts the calculation process of the said movement vector, when the start request | requirement of a calculation process is received via the predetermined | prescribed input part. The ultrasonic diagnostic apparatus as described.

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