JP2014008226A - Ultrasound diagnostic apparatus, image processing device, and image processing program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To simply display a marker showing a time phase even when a biological reference signal corresponding to a part of ultrasonic image data is not acquired.SOLUTION: An ultrasound diagnostic apparatus according to an embodiment is provided with a determination unit and an adjustment unit. The determination unit determines whether or not the number of signal frames to be the number of frames calculated according to a collection period of biological reference signals of an object to be detected that have been collected when generating a group of ultrasonic image data stored for reproduction and a scanning time per unit frame of the group of ultrasonic image data is smaller than the number of image frames to be the number of frames of the group of ultrasonic image data. The adjustment unit adjusts a position of a marker showing a time phase of each of the ultrasonic image data reproduced which is a marker displayed to be superimposed on a waveform displaying the biological reference signal in accordance with the scanning time per unit frame when the number of signal frames is smaller than the number of image frames.

Description

  Embodiments described herein relate generally to an ultrasonic diagnostic apparatus, an image processing apparatus, and an image processing program.

  In the ultrasonic diagnostic apparatus, ultrasonic image data is collected, a biological reference signal is collected, and the ultrasonic image data and the biological reference signal are simultaneously displayed in real time. In the ultrasonic diagnostic apparatus, the stored ultrasonic image data group and the biological reference signal are simultaneously reproduced and displayed after freezing. Examples of the biological reference signal include an electrocardiograph (ECG), a phonocardiography (PCG), and a respiration signal.

  The ultrasonic diagnostic apparatus displays, for example, a marker (for example, a linear marker) indicating in which phase of the biological reference signal the displayed ultrasonic image data is superimposed on the biological reference signal. ing. Here, in order to accurately match the time phases of the ultrasound image data and the biometric reference signal at the time of image reproduction after freezing, the biometric reference signal for the same time phase as the ultrasound image data needs to be captured. There is.

  However, collection of biological reference signals and generation of ultrasonic image data are performed through different paths. For this reason, a synchronization circuit for accurately matching the time phases of the ultrasound image data and the biological reference signal is mounted on the ultrasound diagnostic apparatus. However, in an inexpensive and simple synchronization circuit, the synchronization accuracy is poor. For example, the collection of ECG images is completed before the scan for one frame of ultrasonic data is completed after being frozen, and some ultrasonic image data In some cases, an ECG image corresponding to the above cannot be acquired.

  For this reason, in order to display a marker indicating the time phase on the biological reference signal, at present, an expensive and complicated synchronization circuit with high synchronization accuracy is mounted, or the same as ultrasound image data. It was necessary to photograph until the biometric reference signal for the time phase was captured.

JP 2006-197969 A

  The problem to be solved by the present invention is an ultrasonic diagnostic apparatus capable of easily displaying a marker indicating a time phase even when a biological reference signal corresponding to some ultrasonic image data is not acquired. An image processing apparatus and an image processing program are provided.

  The ultrasonic diagnostic apparatus according to the embodiment includes a determination unit and an adjustment unit. The determination unit is a frame calculated from the collection period of the biological reference signal of the subject collected at the time of generating the ultrasound image data group stored for reproduction and the scanning time per unit frame of the ultrasound image data group It is determined whether the number of signal frames, which is a number, is less than the number of image frames, which is the number of frames of the ultrasound image data group. When the number of signal frames is less than the number of image frames, the adjustment unit is a marker that is superimposed on a waveform that displays the biological reference signal, and is a marker that indicates a time phase of each ultrasonic image data to be reproduced The position is adjusted according to the scanning time per unit frame.

FIG. 1 is a diagram illustrating a configuration example of an ultrasonic diagnostic apparatus according to the present embodiment. FIG. 2 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the first algorithm. FIG. 3 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the second algorithm. FIG. 4 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the third algorithm. FIG. 5 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the fourth algorithm. FIG. 6 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the fifth algorithm. FIG. 7 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the sixth algorithm. FIG. 8 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the seventh algorithm. FIG. 9 is a flowchart illustrating an example of adjustment processing performed by the ultrasonic diagnostic apparatus according to the present embodiment.

  Hereinafter, embodiments of an ultrasonic diagnostic apparatus will be described in detail with reference to the accompanying drawings.

(Embodiment)
First, the configuration of the ultrasonic diagnostic apparatus according to the present embodiment will be described. FIG. 1 is a diagram illustrating a configuration example of an ultrasonic diagnostic apparatus according to the present embodiment. As shown in FIG. 1, the ultrasonic diagnostic apparatus according to the present embodiment includes an ultrasonic probe 1, a monitor 2, an input device 3, an electrocardiograph 4, and a device main body 10.

  The ultrasonic probe 1 includes a plurality of piezoelectric vibrators, and the plurality of piezoelectric vibrators generate ultrasonic waves based on a drive signal supplied from a transmission / reception unit 11 included in the apparatus main body 10 described later. The ultrasonic probe 1 receives a reflected wave from the subject P and converts it into an electrical signal. The ultrasonic probe 1 includes a matching layer and an acoustic lens provided in the piezoelectric vibrator, a backing material that prevents propagation of ultrasonic waves from the piezoelectric vibrator to the rear, and the like. The ultrasonic probe 1 is detachably connected to the apparatus main body 10.

  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 piezoelectric vibrators. 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 by the moving blood flow or the surface of the heart wall depends on the velocity component of the moving object in the ultrasonic transmission direction due to the Doppler effect. And undergoes a frequency shift (Doppler shift).

  In this embodiment, even when the subject P is scanned two-dimensionally by the ultrasonic probe 1 that is a one-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged in a row, the one-dimensional ultrasonic wave is used. An object P is obtained by an ultrasonic probe 1 that mechanically swings a plurality of piezoelectric vibrators of the probe or an ultrasonic probe 1 that is a two-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged in a two-dimensional grid. Even when scanning in three dimensions, it is applicable.

  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, when the operator presses the freeze button of the input device 3, the ultrasonic diagnostic apparatus according to the present embodiment enters a temporary stop state in which transmission / reception of ultrasonic waves is stopped, and shifts from the real-time display mode to the playback mode. .

  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, various images generated in the apparatus main body 10, and the apparatus main body 10 or the like.

  The electrocardiograph 4 is connected to the apparatus body 10 and measures an electrocardiograph (ECG) as a biological reference signal of the subject P to be subjected to ultrasonic scanning. The electrocardiograph 4 transmits the measured electrocardiogram to the apparatus main body 10. In addition, this embodiment is applicable even when the apparatus which measures a phonocardiogram (PCG: phonocardiography) and a respiration (respiration) signal is attached to the subject P as a biological reference signal.

  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 apparatus body 10 includes a transmission / reception unit 11, a B-mode processing unit 12, a Doppler processing unit 13, a collection unit 14, an image generation unit 15, an image memory 16, and an internal storage unit 17. A display data processing unit 18 and a control unit 19.

  The transmission / reception unit 11 includes a trigger generation circuit, a transmission delay circuit, a pulser circuit, and the like, and supplies a drive signal to the ultrasonic probe 1. The pulser circuit repeatedly generates a rate pulse for forming a transmission ultrasonic wave having a predetermined repetition frequency (PRF: Pulse Repetition Frequency). The PRF is also called a rate frequency. Each transmission delay circuit generates a transmission delay time for each piezoelectric vibrator necessary for determining transmission directivity by focusing ultrasonic waves generated from the ultrasonic probe 1 into a beam shape. Give to rate pulse. The trigger generation circuit applies a drive signal (drive pulse) to the ultrasonic probe 1 at a timing based on the rate pulse. That is, the transmission delay circuit arbitrarily adjusts the transmission direction from the piezoelectric vibrator surface by changing the transmission delay time given to each rate pulse.

  The transmission / reception unit 11 has a function capable of instantaneously changing the transmission frequency, the transmission drive voltage, and the like in order to execute a predetermined scan sequence based on an instruction from the control unit 19 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, a reception delay circuit, 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. To do. The amplifier circuit amplifies the reflected wave signal for each channel and performs gain correction processing. The A / D converter A / D converts the reflected wave signal whose gain is corrected. The reception delay circuit gives a reception delay time necessary for determining the reception directivity to the digital data. The adder performs the addition process of the reflected wave signal given the reception delay time by the reception delay circuit to generate the 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.

  Here, the transmission delay time and the reception delay time are determined by the position (depth) from the acoustic lens of the transmission focus and reception focus of the ultrasonic beam. The transmission / reception unit 11 controls transmission directivity and reception directivity in ultrasonic transmission / reception according to transmission / reception conditions such as transmission delay time and reception delay time. In addition, the transmission / reception unit 11 can change the piezoelectric vibrator (transmission aperture and reception aperture) used for transmission / reception of the ultrasonic probe 1 according to transmission / reception conditions.

  The B-mode processing unit 12 receives the reflected wave data from the transmission / reception unit 11, performs logarithmic amplification, envelope detection processing, and the like, and generates data (B-mode data) in which the signal intensity is expressed by brightness. .

  The Doppler processing unit 13 extracts the Doppler shift by performing frequency analysis of the velocity information from the reflected wave data received from the transmission / reception unit 11, and uses the Doppler shift to thereby obtain a blood flow, tissue, and contrast agent echo due to the Doppler effect. A component is extracted, and data (Doppler data) in which moving body information such as average speed, variance, and power is extracted at multiple points is generated.

  The B-mode processing unit 12 and the Doppler processing unit 13 according to the present embodiment may be capable of processing both two-dimensional reflected wave data and three-dimensional reflected wave data.

  The collection unit 14 acquires an ECG from the electrocardiograph 4 and collects an electrocardiogram during a period in which the subject P is ultrasonically scanned. Then, the collection unit 14 stores the acquired ECG in the image memory 16 described later.

  The image generation unit 15 generates ultrasonic image data from the data generated by the B mode processing unit 12 and the Doppler processing unit 13. That is, the image generation unit 15 generates B-mode image data 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. In addition, the image generation unit 15 can calculate average velocity image data, distributed image data, power image data, or the like representing moving body information (blood flow information or tissue movement information) from the Doppler data generated by the Doppler processing unit 13. Color Doppler image data as a combined image is generated.

  Here, the image generation unit 15 generally converts (scan converts) a scanning line signal sequence of ultrasonic scanning into a scanning line signal sequence of a video format typified by a television or the like, and serves as a display image. Generate an ultrasound image. Specifically, the image generation unit 15 generates an ultrasonic image as a display image by performing coordinate conversion in accordance with the ultrasonic scanning mode by the ultrasonic probe 1. In addition to the scan conversion, the image generation unit 15 performs various image processing, such as image processing (smoothing processing) for regenerating an average luminance image using a plurality of image frames after scan conversion, Image processing (edge enhancement processing) using a differential filter is performed in the image.

  Further, the image generation unit 15 generates a Doppler waveform in which blood flow velocity information is plotted in time series from the Doppler data generated by the Doppler processing unit 13.

  The image generation unit 15 can also generate a composite image in which character information, scales, body marks, and the like of various parameters are combined with an ultrasonic image (B-mode image, color Doppler image, Doppler waveform, etc.). In the present embodiment, the image generation unit 15 generates ultrasonic image data for display along time series, and also displays ultrasonic image data for display and “a waveform for displaying the ECG collected by the collection unit 14. "Is generated at the same time. In the present embodiment, the image generation unit 15 generates composite image data in which a marker corresponding to the time phase of the ultrasonic image data is superimposed on the ECG waveform. The image generation unit 15 performs the above generation processing in both the real-time display mode and the playback mode.

  The image memory 16 is a memory that stores various images generated by the image generation unit 15. The image memory 16 is a memory for storing the biological reference signal (ECG) collected by the collection unit 14. The image memory 16 stores, together with the B-mode image data generated by the image generation unit 15, time information of ultrasonic scanning performed to generate the B-mode image data. The image memory 16 stores the ECG wave height collected by the collecting unit 14 together with time information. The image memory 16 can also store data generated by the B-mode processing unit 12 and the Doppler processing unit 13.

  The internal storage unit 17 stores various data such as a control program for performing ultrasonic transmission / reception, image processing and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), diagnostic protocol, and various body marks. To do. The internal storage unit 17 is also used for storing image data and the like stored in the image memory 16 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 display data processing unit 18 is a processing unit for controlling display image data generation processing performed by the image generation unit 15. Specifically, the display data processing unit 18 controls image generation processing performed by the image generation unit 15 when the reproduction mode is executed. In order to perform such control, the display data processing unit 18 includes a determination unit 181 and an adjustment unit 182. The processing performed by the determination unit 181 and the adjustment unit 182 will be described in detail later.

  The control unit 19 controls the entire processing of the ultrasonic diagnostic apparatus. Specifically, the control unit 19 is 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. The processing of the processing unit 12, the Doppler processing unit 13, the image generation unit 15, and the display data processing unit 18 is controlled. The control unit 19 also controls the monitor 2 to display on the monitor 2 image data stored in the image memory 16 and a GUI for the operator to perform various setting processes via the input device 3.

  The overall configuration example of the ultrasonic diagnostic apparatus according to this embodiment has been described above. Under such a configuration, the ultrasonic diagnostic apparatus according to the present embodiment shifts to the reproduction mode when the freeze button is pressed, and the ultrasonic image data group (for example, the B-mode image data group) stored in the image memory 16 for reproduction. ) And the biological reference signal are reproduced and displayed at the same time. At this time, the ultrasonic diagnostic apparatus according to the present embodiment superimposes and displays a marker indicating the time phase of each ultrasonic image data to be reproduced on a waveform for displaying the biological reference signal. An example of such a marker is a display time phase marker indicating the time phase of the reproduced and displayed ultrasonic image data. Examples of such markers include a playback start marker that indicates the time phase of a playback start frame and a playback end marker that indicates the time phase of a playback end frame when the ultrasound image data group is played back as a moving image or frame-by-frame.

  Here, in order to accurately match the time phases of the ultrasound image data and the biological reference signal when reproducing the ultrasound image data group, the biological reference signal for the same time phase as the ultrasound image data is captured. Need to be.

  For example, it is assumed that the scanning time (scanning time per unit frame) of ultrasonic scanning performed for generating ultrasonic image data for one frame is “t”. Further, for example, it is assumed that the number of frames (hereinafter referred to as the number of image frames) of the ultrasound image data group stored for reproduction is “N”. In such a case, the time required from the scan start time of the first frame to the scan end time of the last frame is “N × t”. In addition, in order to accurately match the time phases of the ultrasound image data and the biological reference signal, the collection period of the biological reference signal needs to be “N × t”.

  However, the collection of the biometric reference signal is executed by the biometric reference signal collecting hardware such as the electrocardiograph 4 and the collection unit 14 shown in FIG. On the other hand, the generation and collection of ultrasonic image data are executed by the transmission / reception unit 11, the B-mode processing unit 12 (or the Doppler processing unit 13), and the image generation unit 15 under the control of the control unit 19. The generation and collection of ultrasound image data may be performed entirely by hardware or software, or may be performed by hardware and software. As described above, the collection of the biological reference signal and the generation of the ultrasonic image data are performed through different paths.

  For this reason, conventionally, a synchronization circuit for accurately matching the time phases of the ultrasound image data and the biological reference signal is mounted on the ultrasound diagnostic apparatus. However, in an inexpensive and simple synchronization circuit, the synchronization accuracy is poor. For example, ECG collection is completed before the scan for one frame of ultrasonic data is completed after freezing, and some ultrasonic image data is converted into a part of ultrasonic image data. There is a case where the corresponding ECG cannot be acquired. In this case, “partial ultrasound image data” is the last frame of the ultrasound image data group stored for reproduction.

  In addition, in an inexpensive and simple synchronization circuit, for example, a part of ultrasonic image data is acquired by starting collection of ECG images after the start of scanning for one frame of ultrasonic data immediately after the start of imaging. In some cases, an ECG image corresponding to the above cannot be acquired. The “partial ultrasonic image data” in this case is the first frame of the ultrasonic image data group stored for reproduction.

  Here, “calculated from the collection period of the biological reference signal of the subject collected when generating the ultrasound image data group stored for reproduction and the“ scanning time per unit frame ”of the ultrasound image data group. Defined as the number of signal frames. For example, if the collection period is “T”, the signal frame number “M” is an integer obtained by rounding down the first decimal place of the value of “T / t”. To explain using this definition, the number of signal frames is one less than the number of image frames because an inexpensive and simple synchronization circuit cannot obtain a biometric reference signal frame (hereinafter referred to as a signal frame) corresponding to the final frame. In addition, since the signal frames corresponding to the first frame and the final frame cannot be acquired, the number of signal frames may be two less than the number of image frames.

  For this reason, in order to display a marker indicating the time phase on the biological reference signal, it is currently necessary to mount an expensive and complicated synchronization circuit with high synchronization accuracy. Alternatively, in order to perform imaging until biometric reference signals for the same time phase as the ultrasound image data are captured, for example, a mechanism is provided to detect that the number of signal frames is less than the number of image frames and display an error. There was a need.

  Therefore, the ultrasonic diagnostic apparatus according to the present embodiment is described below in order to easily display a marker indicating a time phase even when a biological reference signal corresponding to some ultrasonic image data is not acquired. The process of the determination part 181 and the adjustment part 182 which are demonstrated to is performed.

  First, the determination unit 181 determines whether the number of signal frames of the biological reference signal of the subject collected when generating the ultrasound image data group stored for reproduction is less than the number of image frames of the ultrasound image data group. Determine whether. The determination unit 181 acquires the number of image frames with reference to the image memory 16 that stores the ultrasound image data group to be reproduced. Further, the determination unit 181 acquires the transmission / reception conditions of the ultrasound image data group stored for reproduction from the control unit 19, and acquires the collection period of the biological reference signal stored in the image memory 16, thereby obtaining a signal frame. Calculate the number. The present embodiment may be a case where the collection unit 14 calculates the number of signal frames and notifies the determination unit 181 of the calculated number of signal frames.

  When the number of signal frames is smaller than the number of image frames, the adjustment unit 182 is a marker that is superimposed and displayed on the waveform for displaying the biological reference signal, and is a marker that indicates the time phase of each reproduced ultrasound image data. The position is adjusted according to the scanning time per unit frame. Specifically, the adjustment unit 182 adjusts the positions of the “display time phase marker”, “reproduction start marker”, and “reproduction end marker” described above. More specifically, the adjustment unit 182 notifies the image generation unit 15 of the result of adjusting the positions of the “display time phase marker”, “reproduction start marker”, and “reproduction end marker”. Based on the position of each marker determined by the adjustment unit 182, the image generation unit 15 superimposes each marker on a waveform for displaying a biological reference signal.

  Hereinafter, the adjustment process performed by the adjustment unit 182 will be specifically described. Hereinafter, a case where the ultrasound image data group stored for reproduction is a two-dimensional (2D) B-mode image data group will be described. However, in the present embodiment, the ultrasound image data group stored for reproduction is a two-dimensional color Doppler image data group, a three-dimensional B-mode image data group, or a three-dimensional color Doppler image data group. Even so, it is applicable. Hereinafter, the display time phase marker may be referred to as a straight line marker. In the following description, the playback start marker is sometimes referred to as a left end (Left Point) marker, and the playback end marker is sometimes referred to as a right end (Right Point) marker. Usually, the biological reference signal such as ECG has the latest time phase from left to right, so that the reproduction start marker is on the left side and the reproduction end marker is on the right side.

  First, when the number of signal frames and the number of image frames are the same, the adjustment unit 182 adjusts the display time phase marker based on the first algorithm, and the “reproduction start marker” that the adjustment unit 182 performs based on the second algorithm. The adjustment process for “and reproduction end marker” will be described with reference to FIGS. 2 and 3 respectively. FIG. 2 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the first algorithm, and FIG. 3 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the second algorithm.

  The example shown in FIGS. 2 and 3 shows a case where the number of image frames and the number of signal frames are both “6”. Further, in the following description, when the number of acquired image frames is “6”, the ID (image ID) of each image frame is set to “image ID (1) in time series as shown in FIG. , Image ID (2),..., Image ID (6) ”. Further, in the following description, when the number of acquired signal frames is “6”, as shown in FIG. 2, the ID (signal ID) of each signal frame is expressed as “signal ID (1) along the time series. , Signal ID (2),..., Signal ID (6) ”.

  First, the adjustment unit 182 displays one signal frame from the number of image frames and the horizontal length of the region for displaying the ECG waveform on the monitor 2 regardless of the magnitude relationship between the number of signal frames and the number of image frames. The unit length to be calculated is calculated (see “L” shown in FIG. 2).

  Then, when the number of signal frames is the same as the number of image frames, the adjustment unit 182 sets the position near the center of the scanning period of each frame as the position of the display time phase marker (linear marker) based on the first algorithm ( (See the hatched numbers shown in Figure 2). Thereby, for example, as shown in FIG. 2, the image generation unit 15 corresponds to the vicinity of the center of the signal frame of the signal ID (1) when displaying the frame (first frame) of the image ID (1). A linear marker is superimposed on the position of the ECG waveform to be performed. For example, as shown in FIG. 2, the image generation unit 15 displays an ECG corresponding to the vicinity of the center of the signal frame of the signal ID (6) when displaying the frame (final frame) of the image ID (6). A linear marker is superimposed on the waveform position.

  When the number of signal frames is the same as the number of image frames, the position of the linear marker on the ECG waveform is changed to the first algorithm as the image ID of the image frame displayed on the monitor 2 changes from (1) to (6). Move based on. Thus, the operator can grasp which phase of the image data is displayed on the monitor 2.

  Further, when the number of signal frames and the number of image frames are the same, the adjustment unit 182 scans the position of the reproduction start marker (left end marker) for the frame set as the reproduction start frame based on the second algorithm. Let it be the time phase at the start (see the position of the hatched numbers in the “Left Point” column of FIG. 3). Further, when the number of signal frames and the number of image frames are the same, the adjustment unit 182 scans the position of the reproduction end marker (right end marker) for the frame set as the reproduction end frame based on the second algorithm. The time phase at the end is set (see the position of the hatched number shown in the column “Right Point” in FIG. 3).

  Thereby, for example, as illustrated in FIG. 3, when the frame (first frame) of the image ID (1) is set as the reproduction start frame, the image generation unit 15 performs the signal frame of the signal ID (1). A left end marker is superimposed on the left end of the ECG waveform. Further, for example, as shown in FIG. 3, when the frame (final frame) of the image ID (6) is set as the reproduction end frame, the image generation unit 15 sets the right end of the signal frame of the signal ID (6). That is, the right end marker is superimposed on the end of the ECG waveform. As shown in FIG. 3, the left end marker includes a line segment that is perpendicular to the time axis and a “left arrowhead in the left direction” that touches the upper left side of the line segment. As shown in FIG. 3, the right end marker is composed of a line segment that is perpendicular to the time axis and a “white arrowhead in the right direction” that is in contact with the upper right side of the line segment.

  As the operator moves the position of the left end marker adjusted based on the second algorithm to “1-6” using a mouse or the like, the image frames displayed on the monitor 2 are image ID (1) to image ID. Change to (6). Thereby, the operator can designate a desired image frame to start reproduction. Further, as the operator moves the position of the right end marker adjusted based on the second algorithm to “1 to 6” using a mouse or the like, the image frame displayed on the monitor 2 is image ID (1) to ID1. It changes to image ID (6). As a result, the operator can designate a desired image frame to end reproduction.

  Subsequently, when the number of signal frames is one frame less than the number of image frames, the adjustment unit 182 adjusts the display time phase marker based on the third algorithm, and the adjustment unit 182 performs based on the fourth algorithm. The adjustment processing of “reproduction start marker and reproduction end marker” will be described with reference to FIGS. 4 and 5 respectively. FIG. 4 is a diagram illustrating an example of the adjustment process performed by the adjustment unit based on the third algorithm, and FIG. 5 is a diagram illustrating an example of the adjustment process performed by the adjustment unit based on the fourth algorithm.

  In the example shown in FIGS. 4 and 5, the number of image frames is “6” and the number of signal frames is “5”. That is, in the example shown in FIGS. 4 and 5, “image ID (1), image ID (2),..., Image ID (6)” is acquired, and “signal ID (1), signal ID (2)” is acquired. ,..., Signal ID (5) ”has been acquired. In other words, in the example shown in FIGS. 4 and 5, the signal of the ECG waveform of “signal ID (1) to signal ID (5)” corresponding to the image frame of “image ID (1) to image ID (5)”. Although the frame is acquired, the signal frame of the ECG waveform corresponding to the final frame of the image ID (6) is not acquired.

  First, as described above, the adjustment unit 182 calculates the unit length for displaying one signal frame from the number of image frames and the horizontal length of the region for displaying the ECG waveform on the monitor 2 (FIG. 4). See “L”).

  Then, when the number of signal frames is one frame less than the number of image frames, the adjustment unit 182 adjusts the position of the display time phase marker (straight line marker) based on the third algorithm. That is, for the frames other than the final frame of the ultrasound image data group, the adjustment unit 182 sets the position of the time phase at the start of scanning of the frame as the position of the linear marker (the hatched numbers “1 to 1” shown in FIG. 4). See position 5)). Thereby, for example, as shown in FIG. 4, when the image frame with the image ID (1) is displayed, the image generation unit 15 displays the ECG waveform corresponding to the left end of the signal frame with the signal ID (1). A linear marker is superimposed on the position. Similarly, for example, when the image frame with the image ID (2) is displayed, the image generation unit 15 superimposes the linear marker on the position of the ECG waveform corresponding to the left end of the signal frame with the signal ID (2). .

  On the other hand, for the last frame, the adjustment unit 182 sets the position of the time phase at the end of scanning of the immediately preceding frame as the position of the linear marker (see the position of the hatched number “6” shown in FIG. 4). Thereby, for example, as illustrated in FIG. 4, when the last frame of the image ID (6) is displayed, the image generation unit 15 displays the ECG waveform corresponding to the right end of the signal frame of the signal ID (5). A linear marker is superimposed on the position.

  As the image ID of the image frame displayed on the monitor 2 changes from (1) to (5), the position of the linear marker on the ECG waveform is determined by the third algorithm as “the left end of the signal frame of signal ID (1)”. ,..., The left end of the signal frame of the signal ID (5) ”. When the image ID of the image frame displayed on the monitor 2 is (6), the position of the linear marker on the ECG waveform is the right end of the signal frame of the signal ID (5) by the third algorithm. By applying the third algorithm, even when the number of image frames is “6”, the time phases of all the image frames can be displayed on the waveform of the biometric reference signal having the number of signal frames “5”.

  Further, when the number of signal frames is one frame less than the number of image frames, the adjustment unit 182 adjusts the positions of the “reproduction start marker (left end marker) and reproduction end marker (right end marker)” based on the fourth algorithm. . That is, when the last frame of the ultrasound image data group is set as the reproduction start frame, the adjustment unit 182 sets the position of the time phase at the end of scanning of the immediately preceding frame as the position of the left end marker (FIG. 5). (See the position of the hatched number “6” shown in the column “Left Point” in (A)).

  Thereby, for example, when the last frame of the image ID (6) is set as the reproduction start frame, the image generation unit 15 sets the left end at the position of the ECG waveform corresponding to the right end of the signal frame of the signal ID (5). Overlay markers.

  Further, when the final frame is set as the playback end frame, the adjustment unit 182 uses the outside near the end of the waveform as the position of the playback end marker (in the column “Right Point” in FIG. 5A). (See the location of the hatched number “6” shown). Thereby, for example, as shown in FIG. 5B, the image generation unit 15 uses the vertical pixel group that passes through the pixel located on the right side of the pixel constituting the end of the ECG waveform, and uses the image ID. The right end marker when the last frame of (6) is set as the reproduction end frame is generated.

  When a frame other than the last frame of the ultrasound image data group is set as the reproduction start frame, the fourth algorithm, like the second algorithm, sets the position of the time phase at the start of scanning of the frame to the left end. The marker position (see the positions of the hatched numbers “1-5” shown in the column “Left Point” in FIG. 5A). When a frame other than the last frame of the ultrasound image data group is set as the reproduction end frame, the fourth algorithm sets the position of the time phase at the end of scanning of the frame to the right end as in the second algorithm. The marker position (see the position of the hatched numbers “1-5” shown in the column “Right Point” in FIG. 5A).

  FIG. 5A illustrates the left end marker when the first frame of the image ID (1) is a reproduction start frame. As shown in FIG. 5A, the left end marker overlaps with the start end of the ECG waveform. That is, the left end marker shown in FIG. 5A is generated by a pixel group in the vertical direction passing through the pixels constituting the start end of the ECG waveform. 5A illustrates the right end marker when the last frame of the image ID (6) is a reproduction end frame. The right end marker is in contact with the end of the ECG waveform as shown in FIG.

  As the image ID of the designated playback start frame changes to (1) to (5) by the fourth algorithm, the position of the left end marker on the ECG waveform is “the left end of the signal frame of signal ID (1), ... “Left end of signal frame of signal ID (5)”. Then, when the image ID of the designated reproduction start frame is (6) by the fourth algorithm, the position of the left end marker on the ECG waveform is the right end of the signal frame of signal ID (5).

  Further, as the image ID of the designated playback end frame changes from (1) to (5) by the fourth algorithm, the position of the right end marker on the ECG waveform is “the right end of the signal frame of signal ID (1)”. ,..., The right end of the signal frame of the signal ID (5) ”. Then, when the image ID of the designated reproduction end frame becomes (6) by the fourth algorithm, the position of the right end marker on the ECG waveform becomes a position outside the right end of the signal frame of the signal ID (5). By applying the fourth algorithm, even when the number of image frames is “6”, the reproduction range can be specified on the waveform of the biometric reference signal having the number of signal frames “5”.

  Subsequently, when the number of signal frames is two frames less than the number of image frames, the adjustment unit 182 adjusts the display time phase marker based on the fifth algorithm, and the adjustment unit 182 performs based on the sixth algorithm. The adjustment process of “reproduction start marker and reproduction end marker” will be described with reference to FIGS. 6 and 7 respectively. FIG. 6 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the fifth algorithm, and FIG. 7 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the sixth algorithm.

  In the example shown in FIGS. 6 and 7, the number of image frames is “7” and the number of signal frames is “5”. That is, in the example shown in FIGS. 6 and 7, “image ID (1), image ID (2),..., Image ID (7)” is acquired, and “signal ID (1), signal ID (2)” is acquired. ,..., Signal ID (5) ”has been acquired. In other words, in the example shown in FIGS. 6 and 7, “signal ID (1) to signal ID (5)” corresponding to “image ID (2) to image ID (6)” is acquired. This shows a case where the signal frame of the ECG waveform corresponding to the first frame of ID (1) is not acquired and the signal frame of the ECG waveform corresponding to the last frame of image ID (7) is not acquired.

  First, as described above, the adjustment unit 182 calculates a unit length for displaying one signal frame from the number of image frames and the horizontal length of the region for displaying the ECG waveform on the monitor 2.

  Then, when the number of signal frames is two frames less than the number of image frames, the adjustment unit 182 adjusts the position of the display time phase marker (linear marker) based on the fifth algorithm. That is, for the frames other than the first frame and the last frame of the ultrasonic image data group, the adjustment unit 182 sets the position near the center of the scanning period of the frame as the position of the linear marker (shown in FIG. 6A). (See the position of the hatched numbers "2-6"). Thereby, for example, when the image frame with the image ID (2) is displayed, the image generation unit 15 superimposes the linear marker at the position of the ECG waveform corresponding to the vicinity of the center of the signal frame with the signal ID (2). To do.

  On the other hand, for each of the first frame and the final frame, the adjustment unit 182 uses the outsides near the both ends of the waveform as the positions of the straight line markers (the hatched numbers “1” and “7” shown in FIG. 6A). See location). As a result, when the first frame of the image ID (1) is displayed, the image generation unit 15, for example, as shown in FIG. A straight line marker is generated using a group of pixels in the vertical direction passing through the pixels located at.

  FIG. 6A illustrates a linear marker when the first frame of the image ID (1) is displayed. Such a linear marker is in contact with the start of the ECG waveform as shown in FIG. When the last frame of the image ID (7) is displayed, the image generation unit 15 is adjacent to the right side of the pixel constituting the end of the ECG waveform as described with reference to (B) of FIG. A straight line marker is generated by using a group of pixels in the vertical direction passing through the located pixels. FIG. 6A illustrates a linear marker when the last frame of the image ID (7) is displayed. Such a linear marker is in contact with the end of the ECG waveform as shown in FIG.

  When the image ID of the image frame displayed on the monitor 2 is (1), the position of the linear marker on the ECG waveform becomes a position outside the left end of the signal frame of the signal ID (1) by the fifth algorithm. Then, as the image ID of the image frame displayed on the monitor 2 changes from (2) to (6), the position of the linear marker on the ECG waveform is changed to “signal frame of signal ID (2) by the fifth algorithm. ,..., The center of the signal frame of the signal ID (5) ”. When the image ID of the image frame displayed on the monitor 2 becomes (7), the position of the linear marker on the ECG waveform is set to the position outside the right end of the signal frame of the signal ID (5) by the fifth algorithm. Become. By applying the fifth algorithm, even when the number of image frames is “7”, the time phases of all the image frames can be displayed on the waveform of the biometric reference signal having the number of signal frames “5”.

  Further, when the number of signal frames is two frames less than the number of image frames, the adjustment unit 182 adjusts the positions of the “reproduction start marker (left end marker) and reproduction end marker (right end marker)” based on the sixth algorithm. . In other words, when the first frame of the ultrasound image data group is set as the reproduction start frame, the adjustment unit 182 sets the outside of the vicinity of the start end of the waveform as the position of the left end marker (see “Left Point” in FIG. 7). (See the location of the hatched number “1” in the column). In addition, the adjustment unit 182 uses the outside near the start end of the waveform as the position of the right end marker even when the first frame of the ultrasound image data group is set as the playback start frame (the “Right Point” in FIG. 7). (See the location of the hatched number “1” in the column).

  Thereby, for example, as described with reference to FIG. 6B, the image generation unit 15 uses a vertical pixel group passing through a pixel located on the left side of the pixel constituting the start end of the ECG waveform. The left end marker when the first frame of the image ID (1) is set as the reproduction start frame is generated. The image generation unit 15 also generates the right end marker when the first frame of the image ID (1) is set as the reproduction end frame by the same process.

  Similarly to the fourth algorithm, the adjustment unit 182 that performs the sixth algorithm, when the last frame is set as the reproduction start frame, determines the position of the time phase at the end of scanning of the immediately preceding frame as the position of the left end marker. (See the position of the hatched number “7” shown in the column “Left Point” in FIG. 7). Similarly to the fourth algorithm, the adjustment unit 182 that performs the sixth algorithm sets the outside of the vicinity of the end of the waveform as the position of the right end marker when the last frame is set as the reproduction end frame (FIG. 7). (See the location of the hatched number "7" in the "Right Point" column).

  When a frame other than the first frame and the last frame of the ultrasonic image data group is set as the reproduction start frame, the sixth algorithm is similar to the second algorithm in the time phase at the start of scanning of the frame. Is the position of the left end marker (see the positions of the hatched numbers “2-6” shown in the column “Left Point” in FIG. 7). When a frame other than the first frame and the last frame is set as the playback end frame, the sixth algorithm, like the second algorithm, sets the position of the time phase at the end of scanning of the frame to the right end marker. Position (see the positions of the hatched numbers “2-5” shown in the column “Right Point” in FIG. 7).

  FIG. 7 illustrates the left end marker when the first frame of the image ID (1) is the reproduction start frame. The left end marker is in contact with the start end of the ECG waveform as shown in FIG. FIG. 7 illustrates the right end marker when the last frame of the image ID (7) is a reproduction end frame. The right end marker is in contact with the end of the ECG waveform as shown in FIG.

  When the image ID of the reproduction start frame is (1), the position of the left end marker on the ECG waveform is outside the left end of the signal frame of the signal ID (1) by the sixth algorithm. Then, as the image ID of the reproduction start frame changes from (2) to (6), the position of the left end marker on the ECG waveform is determined according to the sixth algorithm as “the left end of the signal frame of signal ID (1),. “, The left end of the signal frame of the signal ID (5)”. Then, when the image ID of the reproduction start frame becomes (7), the position of the left end marker on the ECG waveform becomes the right end of the signal frame of the signal ID (5) by the sixth algorithm.

  When the image ID of the reproduction end frame is (1), the position of the left end marker on the ECG waveform is outside the left end of the signal frame of the signal ID (1) by the sixth algorithm. Then, as the image ID of the reproduction end frame changes from (2) to (6), the position of the right end marker on the ECG waveform is determined by the sixth algorithm as “the right end of the signal frame of signal ID (1),. “The right end of the signal frame of the signal ID (5)”. Then, according to the sixth algorithm, when the image ID of the reproduction end frame becomes (7), the position of the right end marker on the ECG waveform becomes a position outside the right end of the signal frame of the signal ID (5). By applying the sixth algorithm, even when the number of image frames is “7”, the reproduction range can be specified on the waveform of the biometric reference signal having the number of signal frames “5”.

  Here, the adjustment unit 182 according to the present embodiment may further execute a seventh algorithm described below when performing the above-described first to sixth algorithms. The seventh algorithm is an algorithm for adjusting the width of the marker superimposed on the biological reference signal.

  In the seventh algorithm, the adjustment unit 182 adjusts the width of the marker in the time axis direction according to the scanning time per unit frame, the display width of the waveform in the time axis direction, and the size of the unit pixel. Here, the scanning time per unit frame corresponds to the number of image frames per unit time, that is, the frame rate. The display width of the waveform in the time axis direction corresponds to the horizontal length of the region where the waveform of the biological reference signal is displayed on the monitor 2 described above. Further, the size of the unit pixel is the size of one pixel displayed on the monitor 2. FIG. 8 is a diagram illustrating an example of adjustment processing performed by the adjustment unit based on the seventh algorithm.

  For example, if the display width of the marker is fixed to 1 pixel and an ultrasound image data group collected at a low frame rate is played back as a moving image, the linear marker remains stationary at the same position for each frame for each frame. Give the person a sense of incongruity Also, when the operator moves the left end marker or right end marker by operating the mouse to set the playback section of the ultrasound image data group collected at a low frame rate, the marker moves smoothly in conjunction with the mouse operation. In order to prevent the operator from feeling uncomfortable. From this, as illustrated in FIG. 8, the adjustment unit 182 performs adjustment to increase the marker width as the frame rate decreases, so that the operator does not feel uncomfortable even at a low frame rate. A marker having a width is displayed.

  However, when such adjustment is performed, the width of the marker becomes narrower as the frame rate increases, and at a certain frame rate, the width of the marker becomes one pixel at the display limit as illustrated in FIG. However, a marker having a display width of 1 pixel has poor visibility for the operator. Therefore, the adjustment unit 182 increases the marker width as shown in FIG. 8 when the marker width is 1 pixel which is the display limit. Thereby, the adjustment part 182 can display the marker with which visibility was ensured, even in the case of a high frame rate.

  Next, an example of adjustment processing of the adjustment unit 182 included in the ultrasonic diagnostic apparatus according to the present embodiment will be described with reference to FIG. FIG. 9 is a flowchart illustrating an example of adjustment processing performed by the ultrasonic diagnostic apparatus according to the present embodiment.

  As illustrated in FIG. 9, the control unit 19 of the ultrasonic diagnostic apparatus according to the present embodiment determines whether or not the freeze button has been pressed (step S101). If the freeze button is not pressed (No at Step S101), the control unit 19 waits until the freeze button is pressed.

  On the other hand, when the freeze button is pressed (Yes at Step S101), the control unit 19 notifies the display data processing unit 18 that the ultrasound image data group and the biometric reference signal are stored in the image memory 16 for reproduction. To do. Then, the determination unit 181 determines whether or not the number of image frames is greater than the number of signal frames (step S102).

  Here, when the number of image frames is the same as the number of signal frames (No in step S102), the adjustment unit 182 calculates a unit length for displaying one signal frame. Then, the adjusting unit 182 determines to adjust the position of the linear marker with the first algorithm and adjust the positions of the left end marker and the right end marker with the second algorithm (step S104).

  On the other hand, when the number of signal frames is smaller than the number of image frames (Yes at Step S102), the determination unit 181 determines whether or not the difference in the number of frames is one frame (Step S103). Here, when the difference in the number of frames is one frame (Yes in step S103), the adjustment unit 182 calculates a unit length for displaying one signal frame. Then, the adjustment unit 182 determines to adjust the position of the linear marker with the third algorithm and adjust the positions of the left end marker and the right end marker with the fourth algorithm (step S105).

  On the other hand, since the difference in the number of frames is two frames, when it is not one frame (No at Step S103), the adjustment unit 182 calculates a unit length for displaying one signal frame. Then, the adjustment unit 182 determines to adjust the position of the linear marker with the fifth algorithm and adjust the positions of the left end marker and the right end marker with the sixth algorithm (step S106).

  After performing any of the determinations in steps S104 to S106, the adjustment unit 182 determines the marker width using the seventh algorithm (step S107). Then, the adjustment unit 182 notifies the adjustment result to the image generation unit 15 (step S108), and ends the process.

  As described above, in the present embodiment, the biological reference signal corresponding to a part of the ultrasound image data is not acquired by performing the adjustment process using the third to sixth algorithms together with the first and second algorithms. Even if it exists, the marker which shows a time phase can be displayed easily. That is, in this embodiment, it is possible to avoid performing re-imaging until a biological reference signal for the same time phase as the ultrasound image data is captured. Further, in the present embodiment, even when a biological reference signal corresponding to some ultrasonic image data is not acquired, a marker indicating the time phase can be reliably displayed with a simple and inexpensive system configuration. it can.

  In the present embodiment, visibility can be ensured by adjusting the width of the marker indicating the time phase to an appropriate width by performing the adjustment process using the seventh algorithm.

  Note that the image processing method described in the present embodiment may be performed by an image processing apparatus installed independently of the ultrasonic diagnostic apparatus. Such an image processing apparatus can perform the image processing method described in the present embodiment by acquiring an ultrasound image data group and a biological reference signal stored for reproduction.

  Further, each component of each illustrated apparatus is functionally conceptual, and does not necessarily need to be physically configured as illustrated. In other words, the specific form of distribution / integration of each device is not limited to the one shown in the figure, and all or a part of the distribution / integration is functionally or physically distributed in arbitrary units according to various loads or usage conditions. Can be integrated and configured. For example, the determination unit 181 and the adjustment unit 182 may be integrated into the control unit 19. Furthermore, all or a part of each processing function performed in each device can be realized by a CPU and a program that is analyzed and executed by the CPU, or can be realized as hardware by wired logic.

  The image processing method described in the present embodiment can be realized by executing an image processing program prepared in advance on a computer such as a personal computer or a workstation. This image processing program can be distributed via a network such as the Internet. The control program is recorded on a computer-readable non-transitory recording medium such as a flash memory such as a hard disk, a flexible disk (FD), a CD-ROM, an MO, a DVD, a USB memory, and an SD card memory. It can also be executed by being read from a non-transitory recording medium by a computer.

  As described above, according to the present embodiment, it is possible to easily display a marker indicating a time phase even when a biological reference signal corresponding to a part of ultrasonic image data is not acquired.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 1 Ultrasonic probe 2 Monitor 3 Input device 4 Electrocardiograph 10 Apparatus main body 11 Transmission / reception part 12 B mode processing part 13 Doppler processing part 14 Collection part 15 Image generation part 16 Image memory 17 Internal storage part 18 Display data processing part 181 Determination part 182 Adjustment unit 19 Control unit

Claims (8)

A signal that is the number of frames calculated from the collection period of the biological reference signal of the subject collected at the time of generating the ultrasound image data group stored for reproduction and the scanning time per unit frame of the ultrasound image data group A determination unit that determines whether the number of frames is less than the number of image frames that is the number of frames of the ultrasound image data group;
When the number of signal frames is less than the number of image frames, the marker is superimposed on the waveform displaying the biological reference signal, and the marker position indicating the time phase of each ultrasonic image data to be reproduced is An adjustment unit that adjusts according to the scanning time per unit frame;
An ultrasonic diagnostic apparatus comprising:   The adjustment unit adjusts the position of a display time phase marker indicating the time phase of the reproduced and displayed ultrasonic image data as the marker, and if the number of signal frames is one frame less than the number of image frames For example, for a frame other than the last frame of the ultrasonic image data group, the position of the time phase at the start of scanning of the frame is set as the position of the display time phase marker, and the last frame is scanned at the end of scanning of the immediately preceding frame. The ultrasonic diagnostic apparatus according to claim 1, wherein a time phase position is set as the position of the display time phase marker.   The adjustment unit further adjusts a position of a reproduction start marker indicating a time phase of a reproduction start frame and a reproduction end marker indicating a time phase of a reproduction end frame as the marker, when reproducing the ultrasonic image data group. In this case, when the last frame is set as the playback start frame, the position of the time phase at the end of scanning of the immediately preceding frame is set as the position of the playback start marker, and the last frame is set as the playback end frame. The ultrasonic diagnostic apparatus according to claim 2, wherein the position near the end of the waveform is the position of the reproduction end marker.   When the position of the display time phase marker indicating the time phase of the ultrasonic image data being reproduced and displayed is adjusted as the marker, the adjustment unit is less than the number of the image frames by 2 frames. For example, for the frames other than the first frame and the last frame of the ultrasonic image data group, the position near the center of the scanning period of the frame is set as the position of the display time phase marker, and each of the first frame and the last frame. The ultrasonic diagnostic apparatus according to claim 1, wherein each of the outsides near both ends of the waveform is set as the position of the display time phase marker.   The adjustment unit further adjusts a position of a reproduction start marker indicating a time phase of a reproduction start frame and a reproduction end marker indicating a time phase of a reproduction end frame as the marker, when reproducing the ultrasonic image data group. In this case, when the first frame of the ultrasonic image data group is set as a reproduction start frame or a reproduction end frame, the outside near the start end of the waveform is set as the position of the reproduction start marker or the reproduction end marker. When the last frame is set as the playback start frame, the time phase position at the end of scanning of the immediately preceding frame is set as the position of the playback start marker, and when the last frame is set as the playback end frame. The ultrasonic diagnostic apparatus according to claim 4, wherein an outer side near a terminal end of the waveform is set as a position of the reproduction end marker.   The adjustment unit adjusts the width of the marker in the time axis direction according to the scanning time per unit frame, the display width of the waveform in the time axis direction, and the size of the unit pixel. The ultrasonic diagnostic apparatus as described in any one of Claims 1-5. A signal that is the number of frames calculated from the collection period of the biological reference signal of the subject collected at the time of generating the ultrasound image data group stored for reproduction and the scanning time per unit frame of the ultrasound image data group A determination unit that determines whether the number of frames is less than the number of image frames that is the number of frames of the ultrasound image data group;
When the number of signal frames is less than the number of image frames, the marker is superimposed on the waveform displaying the biological reference signal, and the marker position indicating the time phase of each ultrasonic image data to be reproduced is An adjustment unit that adjusts according to the scanning time per unit frame;
An image processing apparatus comprising: A signal that is the number of frames calculated from the collection period of the biological reference signal of the subject collected at the time of generating the ultrasound image data group stored for reproduction and the scanning time per unit frame of the ultrasound image data group A determination procedure for determining whether the number of frames is less than the number of image frames that is the number of frames of the ultrasound image data group;
When the number of signal frames is less than the number of image frames, the marker is superimposed on the waveform displaying the biological reference signal, and the marker position indicating the time phase of each ultrasonic image data to be reproduced is Adjustment procedure to adjust according to the scanning time per unit frame;
An image processing program for causing a computer to execute.

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