Ultrasonic diagnostic apparatus

Abstract

To enable a user to concentrate on drawing a two dimensional ultrasonic image while assisting the user's operation for transition to a Doppler mode.SOLUTION: An ultrasound diagnostic apparatus according to an embodiment includes an acquisition unit that acquires a two-dimensional ultrasound image generated based on a signal received by an ultrasound probe and first measurement position information related to a measurement position for measuring blood flow information set in the two-dimensional ultrasound image, a calculation unit that calculates a degree of coincidence between the two-dimensional ultrasound image and first measurement position information and a reference image in which a measurement position is set and second measurement position information related to the measurement position set in the reference image, and a transition control unit that controls transition to a Doppler mode for measuring blood flow information in a subject based on a calculation result of the calculation unit.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The embodiments disclosed in this specification and the drawings relate to an ultrasound diagnostic device. [Background technology]

[0002] Conventionally, in ultrasound diagnostic devices, Doppler information (Doppler signals) extracted from reflected ultrasound waves is used to display a Doppler spectrum (Doppler waveform), which is an example of blood flow information. The Doppler waveform is a waveform in which the blood flow velocity at a measurement position set by the user as an observation site is plotted in time series.

[0003] For example, in a PWD mode for measuring a Doppler waveform using the Pulsed Wave Doppler (PWD) method, a user manually places a marker indicating a measurement position at a specific location within a blood vessel in accordance with the course of the blood vessel depicted in a two-dimensional ultrasound image (a two-dimensional B-mode image or a two-dimensional color Doppler image), and then presses a PWD button to transition to the PWD mode, whereby a Doppler waveform, which is an example of blood flow information at the measurement position, is displayed live on the display of the ultrasound diagnostic device. When transitioning to the PWD mode in this way, the user needs to operate the ultrasound probe with one hand to visualize an appropriate two-dimensional ultrasound image on the display, and operate the input device with the other hand to place a marker at a specific location within the blood vessel on the visualized two-dimensional ultrasound image, and then press the PWD button to transition to the PWD mode. In other words, the user must simultaneously operate the ultrasound probe to generate a two-dimensional ultrasound image and place a marker at a specific location within the blood vessel on the two-dimensional ultrasound image while performing an input operation to transition to PWD mode, which makes the user's operations cumbersome.

[0004] This problem occurs not only in the PWD mode but also in other Doppler modes, such as the CWD mode for measuring Doppler waveforms using the CWD (Continuous Wave Doppler) method. Therefore, it is desirable to enable the user to concentrate on creating a two-dimensional ultrasound image while assisting the user in switching to the Doppler mode. [Prior art documents] [Patent documents]

[0005] [Patent Document 1] Japanese Patent Application Publication No. 2019-000152 [Patent Document 2] Japanese Patent Application Laid-Open No. 2000-166926 [Patent Document 3] Japanese Patent Application Laid-Open No. 2014-213030 Summary of the Invention [Problem to be solved by the invention]

[0006] One of the problems to be solved by the embodiments disclosed in this specification and the drawings is to enable a user to concentrate on rendering a two-dimensional ultrasound image while assisting the user in performing an operation to transition to Doppler mode. However, the problems to be solved by the embodiments disclosed in this specification and the drawings are not limited to the above problem. Problems corresponding to the effects of each configuration shown in the embodiments described below can also be positioned as other problems. [Means for solving the problem]

[0007] An ultrasound diagnostic apparatus according to an embodiment includes an acquisition unit that acquires a two-dimensional ultrasound image generated based on a signal received by an ultrasound probe and first measurement position information related to measurement positions for measuring blood flow information set in the two-dimensional ultrasound image; a calculation unit that calculates a degree of coincidence between the two-dimensional ultrasound image and the first measurement position information, and a reference image in which measurement positions are set and second measurement position information related to the measurement positions set in the reference image; and a transition control unit that controls a transition to a Doppler mode for measuring blood flow information in a subject based on a calculation result by the calculation unit. [Brief explanation of the drawings]

[0008] [Figure 1] 1 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus according to a first embodiment. [Figure 2] 5A and 5B are diagrams showing an example of a target image and second measurement position information according to the first embodiment. [Figure 3] 2 is a diagram showing an example of a two-dimensional ultrasound image and a Doppler waveform displayed on a display in the ultrasound diagnostic apparatus according to the first embodiment. FIG. [Figure 4] 4 is a flowchart for explaining mode transition processing executed in the ultrasound diagnostic apparatus according to the first embodiment. [Figure 5] FIG. 10 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus according to a third embodiment. [Figure 6] 10 is a flowchart for explaining mode transition processing executed in the ultrasound diagnostic apparatus according to the third embodiment. [Figure 7] FIG. 10 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus according to a fourth embodiment. [Figure 8] 10 is a flowchart for explaining mode transition processing executed in an ultrasound diagnostic apparatus according to a fourth embodiment. [Figure 9] FIG. 10 is a diagram showing an example of a two-dimensional ultrasound image and a Doppler waveform displayed on a display in an ultrasound diagnostic apparatus according to a fourth embodiment. [Figure 10]FIG. 10 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus according to a fifth embodiment. [Figure 11] 10 is a flowchart for explaining mode transition processing executed in an ultrasound diagnostic apparatus according to a fifth embodiment. [Figure 12] FIG. 13 is a diagram showing an example of a two-dimensional ultrasound image, a Doppler waveform, and a target image displayed on a display in an ultrasound diagnostic apparatus according to a sixth embodiment. [Figure 13] FIG. 13 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus according to the seventh embodiment. [Figure 14] 13 is a flowchart for explaining mode transition processing executed in the ultrasound diagnostic apparatus according to the seventh embodiment. [Figure 15] FIG. 13 is a diagram showing an example of a process in which the acquisition function acquires a two-dimensional B-mode image and a marker, which is an example of second identification information, in step S11 of the mode transition processing executed in the ultrasound diagnostic apparatus according to the eighth embodiment. [Figure 16] FIG. 13 is a diagram showing an example of a process in which the calculation function calculates the degree of coincidence between a two-dimensional ultrasound image and its measurement position, and a target image and its measurement position in step S13 of the mode transition processing executed in the ultrasound diagnostic apparatus according to the eighth embodiment. DETAILED DESCRIPTION OF THE INVENTION

[0009] Hereinafter, an embodiment of an ultrasound diagnostic device will be described with reference to the drawings. In the following description, components having substantially the same functions and configurations are designated by the same reference numerals, and redundant description will be given only when necessary.

[0010] [First embodiment] Fig. 1 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus according to the first embodiment. As shown in Fig. 1, the ultrasound diagnostic apparatus 1 includes an ultrasound probe 10, an apparatus main body 30, an input device 50, and a display 70.

[0011] The ultrasonic probe 10 has, for example, a plurality of piezoelectric vibrators. These plurality of piezoelectric vibrators generate ultrasonic waves based on drive signals supplied from a transmission circuit 31 included in the device main body 30, which will be described later. The ultrasonic probe 10 also receives reflected waves from the subject P and converts them into electrical signals. The ultrasonic probe 10 also has, for example, a matching layer provided on the piezoelectric vibrators and a backing material that prevents ultrasonic waves from propagating backward from the piezoelectric vibrators.

[0012] When ultrasonic waves are transmitted from the ultrasonic probe 10 to the subject P, the transmitted ultrasonic waves are reflected successively by discontinuous surfaces of acoustic impedance in the tissues of the subject P and are received as reflected wave signals by the multiple piezoelectric transducers of the ultrasonic probe 10. The amplitude of the received reflected wave signals depends on the difference in acoustic impedance at the discontinuous surfaces from which the ultrasonic waves are reflected. When the transmitted ultrasonic pulses are reflected by the surface of a moving blood flow or heart wall, the reflected wave signals undergo a frequency shift due to the Doppler effect, depending on the velocity component of the moving object in the direction of ultrasonic transmission.

[0013] The ultrasonic probe 10 is detachably connected to the device main body 30. When scanning a two-dimensional region inside the subject P (two-dimensional scanning), the user connects, for example, a 1D array probe in which multiple piezoelectric transducers are arranged in a row to the device main body 30 as the ultrasonic probe 10. The 1D array probe is a linear ultrasonic probe, a convex ultrasonic probe, a sector ultrasonic probe, etc. When scanning a three-dimensional region inside the subject P (three-dimensional scanning), the user connects, for example, a mechanical 4D probe or a 2D array probe to the device main body 30 as the ultrasonic probe 10. A mechanical 4D probe is capable of two-dimensional scanning using multiple piezoelectric transducers arranged in a row like a 1D array probe, and is also capable of three-dimensional scanning by oscillating the multiple piezoelectric transducers at a predetermined angle (oscillation angle). A 2D array probe is capable of three-dimensional scanning using multiple piezoelectric transducers arranged in a matrix, and is also capable of two-dimensional scanning by focusing and transmitting ultrasonic waves. The 2D array probe is also capable of simultaneously performing two-dimensional scanning of multiple cross sections.

[0014] Furthermore, the ultrasound diagnostic device 1 according to this embodiment measures Doppler waveforms using a pulsed wave Doppler (PWD) method or a continuous wave Doppler (CWD) method, as will be described later. Therefore, in this embodiment, the ultrasound probe 10 connected to the device main body 30 is an ultrasound probe that can transmit and receive ultrasound waves for capturing two-dimensional ultrasound images, as well as transmit and receive ultrasound waves for measuring Doppler waveforms using the PWD method or the CWD method.

[0015] The device main body 30 generates an ultrasound image based on a signal from the ultrasound probe 10. Specifically, the device main body 30 can generate a two-dimensional ultrasound image based on a reflected wave signal corresponding to a two-dimensional region of the subject P received by the ultrasound probe 10. The device main body 30 can also generate a three-dimensional ultrasound image based on a reflected wave signal corresponding to a three-dimensional region of the subject P received by the ultrasound probe 10. As shown in FIG. 1 , the device main body 30 has a transmission circuit 31, a reception circuit 32, a B-mode processing circuit 33, a Doppler processing circuit 34, an image generation circuit 35, an image memory 36, a storage circuit 37, and a processing circuit 38.

[0016] The transmission circuit 31 includes a pulse generator, a transmission delay unit, a pulser, etc., and supplies a drive signal to the ultrasonic probe 10. The pulse generator repeatedly generates rate pulses at a predetermined rate frequency to form transmitted ultrasonic waves. The transmission delay unit focuses the ultrasonic waves generated from the ultrasonic probe 10 into a beam and provides a delay time for each piezoelectric transducer required to determine the transmission directivity to each rate pulse generated by the pulse generator. The pulser applies a drive signal (drive pulse) to the ultrasonic probe 10 at a timing based on the rate pulse. In other words, the transmission delay unit changes the delay time provided to each rate pulse to arbitrarily adjust the transmission direction of the ultrasonic waves transmitted from the piezoelectric transducer surface.

[0017] The transmission circuit 31 has the function of instantaneously changing the transmission frequency, transmission drive voltage, etc. in order to execute a predetermined scan sequence based on instructions from the processing circuit 38, which will be described later. In particular, the change in transmission drive voltage is realized by a linear amplifier type oscillation circuit that can instantaneously switch its value, or a mechanism that electrically switches between multiple power supply units.

[0018] The receiving circuit 32 has a preamplifier, an A / D (Analog / Digital) converter, a reception delay unit, an adder, etc., and performs various processes on the reflected wave signals received by the ultrasound probe 10 to generate reflected wave data. The preamplifier amplifies the reflected wave signals for each channel and performs gain adjustment (gain correction). The A / D converter A / D converts the gain-corrected reflected wave signals to digital signals. The reception delay unit provides a delay time required to determine the reception directivity. The adder performs addition processing on the reflected wave signals processed by the reception delay unit to generate reflected wave data. The adder then outputs the generated reflected wave data to the B-mode processing circuit 33 and the Doppler processing circuit 34.

[0019] When performing two-dimensional scanning of the subject P, the transmission circuitry 31 causes the ultrasonic probe 10 to transmit two-dimensional ultrasonic beams. Then, the reception circuitry 32 generates two-dimensional reflected wave data from the two-dimensional reflected wave signals received by the ultrasonic probe 10. Furthermore, when performing three-dimensional scanning of the subject P, the transmission circuitry 31 according to this embodiment causes the ultrasonic probe 10 to transmit three-dimensional ultrasonic beams. Then, the reception circuitry 32 generates three-dimensional reflected wave data from the three-dimensional reflected wave signals received by the ultrasonic probe 10.

[0020] The B-mode processing circuit 33 receives the reflected wave data from the receiving circuit 32, and performs logarithmic amplification, envelope detection processing, etc. to generate data (B-mode data) in which the signal strength is expressed as brightness.

[0021] The Doppler processing circuit 34 performs frequency analysis on the velocity information from the reflected wave data received from the receiving circuit 32, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and generates data (Doppler data) in which moving object information such as velocity, dispersion, and power is extracted for multiple points. Here, the moving object refers to, for example, blood flow, tissue of an organ that moves periodically, such as the heart wall, or a contrast agent.

[0022] The B-mode processing circuit 33 and the Doppler processing circuit 34 can process both two-dimensional reflected wave data and three-dimensional reflected wave data. That is, the B-mode processing circuit 33 generates two-dimensional B-mode data from two-dimensional reflected wave data, and generates three-dimensional B-mode data from three-dimensional reflected wave data. Furthermore, the Doppler processing circuit 34 generates two-dimensional Doppler data from two-dimensional reflected wave data, and generates three-dimensional Doppler data from three-dimensional reflected wave data.

[0023] The image generation circuit 35 generates an ultrasound image expressed in a predetermined brightness range based on the signal received by the ultrasound probe 10. For example, the image generation circuit 35 generates, as the ultrasound image, a two-dimensional B-mode image in which the intensity of the reflected wave is expressed as brightness from the two-dimensional B-mode data generated by the B-mode processing circuit 33. The image generation circuit 35 also generates, as the ultrasound image, a mean velocity image, a variance image, a power image, or a two-dimensional color Doppler image as a combination of these images, which represents information about the moving object from the two-dimensional Doppler data generated by the Doppler processing circuit 34.

[0024] Here, the image generation circuit 35 generally converts (scan converts) a series of scan line signals of an ultrasonic scan into a series of scan line signals in a video format such as that of a television, and generates an ultrasonic image for display. For example, the image generation circuit 35 generates an ultrasonic image for display by performing coordinate conversion in accordance with the ultrasonic scanning form of the ultrasonic probe 10. In addition to scan conversion, the image generation circuit 35 also performs various image processing, such as image processing (smoothing processing) for regenerating an average brightness image using multiple image frames after scan conversion, and image processing (edge ​​enhancement processing) using a differential filter within the image.

[0025] That is, the B-mode data and Doppler data are data before scan conversion processing, and the data generated by the image generation circuitry 35 is an ultrasound image for display after scan conversion processing. Note that the B-mode data and Doppler data are also called raw data. The image generation circuitry 35 generates two-dimensional ultrasound images, such as a two-dimensional B-mode image or a two-dimensional color Doppler image, from the two-dimensional B-mode data or two-dimensional Doppler data, which are raw data. The image generation circuitry 35 can also generate a superimposed image, for example, by superimposing a color Doppler image on a two-dimensional B-mode image.

[0026] Furthermore, for example, the image generating circuitry 35 generates an M-mode image from time-series data of B-mode data on one scanning line generated by the B-mode processing circuitry 33. Furthermore, the image generating circuitry 35 generates a Doppler waveform in which velocity information of blood flow and tissue is plotted in time series from the Doppler data generated by the Doppler processing circuitry 34. This Doppler waveform is an example of blood flow information.

[0027] Furthermore, the image generation circuitry 35 can generate a three-dimensional B-mode image by performing coordinate transformation on the three-dimensional B-mode data generated by the B-mode processing circuitry 33. The image generation circuitry 35 can also generate a three-dimensional color Doppler image by performing coordinate transformation on the three-dimensional Doppler data generated by the Doppler processing circuitry 34.

[0028] The image memory 36 is a memory that stores various images generated by the image generation circuit 35. The image memory 36 also stores data generated by the B-mode processing circuit 33 and the Doppler processing circuit 34. The B-mode data and Doppler data stored in the image memory 36 can be called up by an operator after diagnosis, for example, and are converted into an ultrasound image for display via the image generation circuit 35. The image memory 36 also stores reflected wave data output by the receiving circuit 32. For example, the image memory 36 is realized by a semiconductor memory element such as a RAM (Random Access Memory), a flash memory, a hard disk, or an optical disk.

[0029] The memory circuitry 37 stores control programs for transmitting and receiving ultrasound, image processing, and display processing, as well as various data such as diagnostic information (e.g., patient ID, doctor's findings, etc.), diagnostic protocols, and various body marks. The memory circuitry 37 also stores thresholds related to the degree of match, which will be described later. The memory circuitry 37 is also used to store data stored in the image memory 36, as necessary. For example, the memory circuitry 37 is realized by a semiconductor memory element such as a flash memory, a hard disk, or an optical disk.

[0030] The memory circuitry 37 also stores a target image. This target image corresponds to a reference image according to this embodiment. Therefore, the memory circuitry 37 corresponds to a storage unit according to this embodiment. Here, the target image is an ultrasound image used for comparison with a two-dimensional ultrasound image. A measurement position for measuring blood flow information is set in this target image. Specifically, for example, a marker indicating a measurement position for measuring a Doppler waveform, which is an example of blood flow information, is set in the target image. This marker indicating the measurement position is also referred to as a sample volume or a sample gate. The marker indicating the measurement position in this target image is an example of second measurement position information, which is information related to the measurement position set in the reference image. The target image may be stored in the image memory 36. In this case, the image memory 36 corresponds to a storage unit according to this embodiment.

[0031] The target image according to this embodiment is, for example, an ultrasound image in which a measurement position is set in a frozen state of a live display of a 2D B-mode image. Specifically, this target image is an ultrasound image in which a measurement position is set by the user rendering a cross section (ultrasound image) in B-mode (described later) before measuring a Doppler waveform during an ultrasound examination of the subject P. When the user has rendered the intended cross section (ultrasound image), the user freezes the live display of the 2D B-mode image being displayed on the display 70, and sets a marker indicating a measurement position on the frozen 2D B-mode image displayed on the display 70. That is, the memory circuitry 37 stores, as the target image TA1, the frozen 2D B-mode image displayed on the display 70, which is an ultrasound image in which a measurement position is set. Furthermore, the memory circuitry 37 stores, together with the frozen 2D B-mode image displayed on the display 70, a marker indicating the measurement position set on the 2D B-mode image as second measurement position information.

[0032] 2 is a diagram showing an example of a target image and second measurement position information according to the first embodiment. As shown in FIG. 2, the target image TA1 is a two-dimensional B-mode image, and a marker MA1 indicating a measurement position in the target image TA1 is set on the target image TA1 as second measurement position information. In addition, in the example shown in FIG. 2, a region of interest R1 for synthesizing a two-dimensional color Doppler image is set on the target image TA1. Note that the region of interest R1 does not have to be set on the target image TA1.

[0033] The processing circuitry 38 executes various types of data processing. The processing circuitry 38 has a system control function 381, a display control function 382, ​​an acquisition function 383, a calculation function 384, and a transition control function 385. Here, for example, each of the processing functions of the processing circuitry 38 shown in FIG. 1 , i.e., the system control function 381, the display control function 382, ​​the acquisition function 383, the calculation function 384, and the transition control function 385, are recorded in the storage circuitry 37 in the form of a computer-executable program. The processing circuitry 38 reads each program from the storage circuitry 37 and executes the read program to realize the function corresponding to each program. In other words, the processing circuitry 38 in a state in which each program has been read has each function shown in the processing circuitry 38 of FIG. 1 . The processing circuitry 38 is realized by, for example, a processor. The system control function 381 is an example of a control unit. The display control function 382 is an example of a display control unit. The acquisition function 383 is an example of an acquisition unit. The calculation function 384 is an example of a calculation unit. The transition control function 385 is an example of a transition control unit.

[0034] The system control function 381 is a function that controls the overall operation of the ultrasound diagnostic apparatus 1. For example, the system control function 381 controls the transmission circuitry 31 and the reception circuitry 32 based on parameters related to transmission and reception of ultrasound waves corresponding to various modes. These various modes include, for example, B mode, color Doppler mode, PWD mode, and CWD mode. Note that the PWD mode is also referred to as the PW mode, and the CWD mode is also referred to as the CW mode. In the following description, the PWD mode and the CWD mode will be collectively referred to as the Doppler mode.

[0035] B-mode is a mode for generating a B-mode image by B-mode scanning. Color Doppler mode is a mode for generating a color Doppler image by color Doppler scanning, in which color is assigned to blood flow information measured using, for example, a pulse wave. Color Doppler mode scanning includes B-mode scanning. In color Doppler mode, for example, both a B-mode image and a color Doppler image are generated, and the color Doppler image is superimposed on the B-mode image.

[0036] PWD mode is a mode for measuring the Doppler waveform of a specific measurement site using a PWD mode scan (PWD-based scan) in which pulse waves are transmitted to a scanning line and reflected waves are received. In PWD mode, the ultrasound probe 10 generally performs a PWD mode scan on one scanning line, but it is also possible to perform a PWD mode scan on multiple scanning lines. In this case, the ultrasound probe 10 transmits pulse waves to the multiple scanning lines in sequence and receives reflected waves. In PWD mode, only the Doppler waveform is updated to observe blood flow with good image quality. In this case, B-mode scanning cannot be used in combination.

[0037] CWD mode is a mode for measuring the Doppler waveform on one scan line using a CWD mode scan (CWD method scan) that transmits a continuous wave while receiving a reflected wave. In CWD mode, the continuous wave must be continuously applied to the target, so B-mode scan cannot be used in combination. In the following, this embodiment will be described using as an example a case where the Doppler mode is PWD mode and the Doppler waveform is measured using the PWD method.

[0038] The display control function 382 is a function that controls the display 70 to display various ultrasound images, Doppler waveforms, and the like generated by the image generation circuit 35. For example, the display control function 382 controls the display 70 to display a B-mode image, a color Doppler image, or an image including both of these, and a Doppler waveform, generated by the image generation circuit 35. Specifically, the display control function 382 causes the display 70 to live-display a B-mode image, a color Doppler image, or an image including both of these, or causes the display 70 to live-display (in real time) a Doppler waveform. The display control function 382 also controls the display 70 to live-display a two-dimensional ultrasound image and freeze the live display of the Doppler waveform, or controls the display 70 to freeze the live display of the two-dimensional ultrasound image and live-display a Doppler waveform.

[0039] 3 is a diagram showing an example of a two-dimensional ultrasound image and a Doppler waveform displayed on the display 70 in the ultrasound diagnostic apparatus 1 according to the first embodiment. As shown in FIG. 3, the display control function 382 causes a two-dimensional B-mode image IM1 as a two-dimensional ultrasound image and a Doppler waveform WA1 to be displayed on the display 70. The display control function 382 also causes a marker MA2 indicating a measurement position for measuring blood flow information to be displayed on the two-dimensional B-mode image IM1 displayed on the display 70. The marker MA2 indicating the measurement position on the two-dimensional B-mode image IM1 is an example of first measurement position information, which is information related to the measurement position set on the two-dimensional ultrasound image.

[0040] In this embodiment, the user sets the marker MA2 on the two-dimensional B-mode image IM1 by manually moving the position of the marker MA2, which indicates the measurement position on the two-dimensional B-mode image IM1, via the input device 50. In the example shown in FIG. 3, a region of interest R2 for synthesizing a two-dimensional color Doppler image is set in the two-dimensional B-mode image IM1. The region of interest R2 does not have to be set in the two-dimensional B-mode image IM1. In the example shown in FIG. 3, a Doppler waveform WA1 is displayed on the display 70, but the Doppler waveform WA1 does not have to be displayed before the PWD mode is started. In addition, when the marker MA1 or the marker MA2 is a marker for measuring a Doppler waveform using the PWD method, the marker MA1 or the marker MA2 will also be referred to as a PWD marker hereinafter.

[0041] As described above, PWD mode scanning in PWD mode and B-mode scanning in B mode cannot be used together. Therefore, one of the two-dimensional B-mode image IM1 and the Doppler waveform WA1 displayed on the display 70 is displayed live (in real time), while the other is displayed frozen. Specifically, when B mode is selected, the Doppler waveform WA1 displayed immediately before B mode is started is displayed as a still image, i.e., the Doppler waveform WA1 is displayed frozen, and the two-dimensional B-mode image IM1 is displayed live. On the other hand, when PWD mode is selected, the two-dimensional B-mode image IM1 displayed immediately before PWD mode is started is displayed as a still image, i.e., the two-dimensional B-mode image IM1 is displayed frozen, and the Doppler waveform WA1 is displayed live.

[0042] The acquisition function 383 acquires a two-dimensional ultrasound image and first measurement position information. Specifically, for example, the acquisition function 383 acquires a two-dimensional B-mode image IM1 as the two-dimensional ultrasound image, and acquires a marker MA2 indicating the measurement position set on the two-dimensional B-mode image IM1 as the first measurement position information.

[0043] The calculation function 384 calculates the degree of coincidence between the two-dimensional ultrasonic image and the first measurement position information, and the target image TA1 and the second measurement position information.

[0044] The transition control function 385 controls the transition to the Doppler mode for measuring blood flow information in the subject P based on the calculation result of the calculation function 384. For example, the transition control function 385 controls the transition to the PWD mode as the Doppler mode.

[0045] The input device 50 includes a mouse, keyboard, buttons, panel switches, a touch command screen, a wheel, a dial, a foot switch, a trackball, a joystick, etc., and accepts various setting requests from the user of the ultrasound diagnostic device 1 and transfers the accepted setting requests to the device main body 30.

[0046] The display 70 displays a GUI (Graphical User Interface) that allows the user of the ultrasound diagnostic apparatus 1 to input various setting requests using the input device 50, and also displays ultrasound images and Doppler waveforms WA1 generated in the device main body 30. The display 70 also displays various messages to notify the user of the processing status of the device main body 30. The display 70 also has a speaker and can output sound. For example, the speaker of the display 70 outputs a predetermined sound such as a beep to notify the user of the processing status of the device main body 30. The display 70 corresponds to the display unit according to this embodiment.

[0047] 4 is a flowchart for explaining the mode transition process executed in the ultrasound diagnostic apparatus 1 according to the first embodiment. This mode transition process acquires a two-dimensional ultrasound image and measurement positions on the two-dimensional ultrasound image, calculates the degree of coincidence between the two-dimensional ultrasound image and its measurement positions and the target image TA1 and measurement positions on the target image TA1, determines whether the degree of coincidence is equal to or greater than a threshold, and transitions to the PWD mode. For example, the mode transition process is executed when the process of setting measurement positions on the two-dimensional ultrasound image is started in B mode.

[0048] 4, first, the acquisition function 383 in the processing circuitry 38 of the device main body 30 acquires a two-dimensional ultrasound image and a measurement position on the two-dimensional ultrasound image (step S11). Specifically, the acquisition function 383 acquires, from the image memory 36, a two-dimensional B-mode image IM1 displayed on the display 70 as the two-dimensional ultrasound image, and a marker MA2 set on the two-dimensional B-mode image IM1 as the measurement position.

[0049] 4, the calculation function 384 in the processing circuitry 38 of the apparatus main body 30 calculates the degree of coincidence between the two-dimensional ultrasound image and its measurement position, and the target image TA1 and the measurement position on the target image TA1 (step S13). Specifically, the calculation function 384 calculates the degree of coincidence between the two-dimensional B-mode image IM1 acquired by the acquisition function 383 in step S11 and the marker MA2 set on the two-dimensional B-mode image IM1, and the target image TA1 and the marker MA1 set on the target image TA1 stored in the memory circuitry 37. More specifically, the calculation function 384 calculates the degree of coincidence between the two-dimensional B-mode image IM1 and the target image TA1, and the degree of coincidence between the measurement positions of the marker MA2 set on the two-dimensional B-mode image IM1 and the marker MA1 set on the target image TA1.

[0050] 4, the transition control function 385 in the processing circuitry 38 of the device main body 30 determines whether the degree of match is equal to or greater than a threshold (step S15). Specifically, the transition control function 385 determines whether the degree of match of the image calculated in step S13 and the degree of match of the measurement position are each equal to or greater than a threshold. If the degree of match is not equal to or greater than the threshold in step S15 (step S15: No), the process returns to step S11 described above, and the process of acquiring the two-dimensional ultrasound image and the measurement position on the two-dimensional ultrasound image (step S11) and the process of calculating the degree of match (step S13) are repeated and waited.

[0051] On the other hand, if the degree of match is equal to or greater than the threshold value in step S15 (step S15: Yes), the transition control function 385 in the processing circuitry 38 of the apparatus main body 30 transitions to PWD mode (step S17). Specifically, the transition control function 385 transitions from B mode to PWD mode. Furthermore, when the transition control function 385 transitions to PWD mode, the display control function 382 freezes the live display of the two-dimensional B-mode image IM1 and controls the display 70 to live display a Doppler waveform WA1, which is an example of blood flow information.

[0052] In step S17, the mode transition is made to the PWD mode, and the mode transition process is completed.

[0053] As described above, the ultrasound diagnostic device 1 acquires a two-dimensional ultrasound image and measurement positions on the two-dimensional ultrasound image, calculates the degree of coincidence between the two-dimensional ultrasound image and its measurement positions and the target image TA1 and the measurement positions on the target image TA1, determines whether the degree of coincidence is equal to or greater than a threshold, and transitions to PWD mode if the degree of coincidence is equal to or greater than the threshold. Therefore, by assisting the user in performing an operation to transition to PWD mode, the user can concentrate on depicting the two-dimensional ultrasound image.

[0054] Second Embodiment In the ultrasound diagnostic apparatus 1 according to the first embodiment described above, the target image is, for example, an ultrasound image in which a measurement position is set in a frozen state of live display of the two-dimensional B-mode image IM1, but the target image is not limited to this.

[0055] The target image may be, for example, an ultrasound image on which a measurement position was set in a previous ultrasound examination. Specifically, this target image may be an ultrasound image on which a user set a marker indicating the measurement position when measuring the Doppler waveform WA1 in a previous ultrasound examination of the subject P. This target image differs from the target image in the first embodiment in that it is not a target image generated during the ultrasound examination of the subject P, but a target image generated in a previous ultrasound examination of the subject P. In other words, the storage circuitry 37 may store, as the target image, an ultrasound image on which a measurement position was set, on which a marker indicating the measurement position was set by the user when measuring the Doppler waveform WA1 in a previous ultrasound examination of the subject P. Furthermore, the storage circuitry 37 may store, as second measurement position information, the marker indicating the measurement position set on this ultrasound image, along with the ultrasound image on which a marker indicating the measurement position was set by the user when measuring the Doppler waveform WA1 in a previous ultrasound examination of the subject P.

[0056] By using such a target image and second measurement position information to calculate the degree of coincidence, when a user wants to measure the Doppler waveform WA1 at the same position where the Doppler waveform was measured in a previous ultrasound examination during multiple hospital visits, regular medical checkups, re-examinations, etc., an ultrasound image that highly coincides with the ultrasound image on which the user set a marker indicating the measurement position when the Doppler waveform WA1 was measured in the previous ultrasound examination, which is the target image TA1, can be rendered, and a marker can be set in the rendered ultrasound image at a position that highly coincides with the position of the marker indicating the measurement position when the Doppler waveform WA1 was measured in the previous ultrasound examination, thereby automatically transitioning to PWD mode. Therefore, ultrasound diagnostic device 1 assists the user in performing an operation to transition to PWD mode, allowing the user to concentrate on rendering a two-dimensional ultrasound image.

[0057] The target image may also be, for example, an ultrasound image on which a measurement position is set immediately before transition to the PWD mode. Specifically, for example, the target image may be an ultrasound image displayed on the display 70 immediately before transition to the PWD mode and on which a marker indicating a measurement position is set by the user. That is, the storage circuitry 37 may store, as the target image, an ultrasound image displayed on the display 70 immediately before transition to the PWD mode and on which a marker indicating a measurement position is set by the user. The storage circuitry 37 may also store, as second measurement position information, the marker indicating the measurement position set on this ultrasound image, together with the ultrasound image displayed on the display 70 immediately before transition to the PWD mode and on which a marker indicating a measurement position is set by the user.

[0058] By using such target image TA1 and second measurement position information to calculate the degree of coincidence, when the subject P moves during measurement of the Doppler waveform in PWD mode and the process of depicting the cross section intended by the user is started again, an ultrasound image that is highly consistent with the ultrasound image displayed on the display 70 immediately before transitioning to the PWD mode and on which a marker indicating the measurement position is set by the user immediately before transitioning to the PWD mode is depicted, and a marker indicating the measurement position is set in the depicted ultrasound image at a position that is highly consistent with the position of the marker indicating the measurement position set by the user immediately before transitioning to the PWD mode, thereby enabling automatic transition to the PWD mode. Therefore, the ultrasound diagnostic apparatus 1 assists the user in performing an operation to transition to the PWD mode, allowing the user to concentrate on depicting a two-dimensional ultrasound image.

[0059] Third Embodiment In the ultrasound diagnostic apparatus 1 according to the first embodiment described above, the position of the marker MA2 in the two-dimensional ultrasound image is set manually by the user, but this is not limiting. In the third embodiment, when the degree of coincidence between the images is equal to or greater than a threshold and the degree of coincidence between the measurement positions is equal to or less than a threshold, it is also possible to move the position of the marker MA2 set in the two-dimensional ultrasound image so that the degree of coincidence between the measurement positions increases (to be equal to or greater than the threshold). Below, a case where this modified example is applied to the first embodiment will be referred to as the third embodiment, and differences from the first embodiment will be described. Note that, although a case where this modified example is applied to the first embodiment will be described below, this modified example can also be applied to the second embodiment described above.

[0060] Fig. 5 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus 1 according to the third embodiment, and corresponds to Fig. 1. As shown in Fig. 5, the ultrasound diagnostic apparatus 1 according to this embodiment is configured by adding a position control function 386 to the processing circuitry 38 of the ultrasound diagnostic apparatus 1 according to the first embodiment. Note that the configuration and functions other than the position control function 386 are the same as those in Fig. 1 of the first embodiment described above, and therefore will not be described here.

[0061] The position control function 386 controls the position of a marker indicating a measurement position set on a two-dimensional ultrasonic image so that the degree of coincidence between the first measurement position information and the second measurement position information increases.

[0062] FIG. 6 is a flowchart illustrating mode transition processing executed in the ultrasound diagnostic apparatus 1 according to the third embodiment, and corresponds to FIG. 4. The mode transition processing according to the third embodiment calculates the degree of image coincidence, determines whether the degree of image coincidence is equal to or greater than a threshold, calculates the degree of measurement position coincidence, determines whether the degree of measurement position coincidence is equal to or greater than a threshold, controls the position of the PWD marker, and transitions to the PWD mode. For example, the mode transition processing is executed when processing to set a measurement position on a two-dimensional ultrasound image is started. Note that the processing of step S11 shown in FIG. 6 is the same as that in FIG. 4, and therefore description thereof will be omitted.

[0063] 6, the calculation function 384 in the processing circuitry 38 of the device body 30 calculates the degree of coincidence of the images (step S21). Specifically, the calculation function 384 calculates the degree of coincidence between the two-dimensional B-mode image IM1 acquired by the acquisition function 383 in step S11 and the target image TA1 stored in the memory circuitry 37.

[0064] 6, the transition control function 385 in the processing circuitry 38 of the device main body 30 determines whether the degree of coincidence of the images is equal to or greater than a threshold value (step S23). If the degree of coincidence of the images is not equal to or greater than the threshold value in step S23 (step S23: No), the process returns to step S11 described above, and the process of acquiring the two-dimensional ultrasound image and the measurement position on the two-dimensional ultrasound image (step S11) and the process of calculating the degree of coincidence of the images (step S23) are repeated and the process waits.

[0065] On the other hand, if the degree of coincidence of the images is equal to or greater than the threshold value in step S23 (step S23: Yes), the calculation function 384 in the processing circuitry 38 of the apparatus main body 30 calculates the degree of coincidence of the measurement positions (step S25). Specifically, the calculation function 384 calculates the degree of coincidence of the measurement positions between the position of the marker MA2 set on the two-dimensional B-mode image IM1 and the position of the marker MA1 set on the target image TA1.

[0066] 6, the transition control function 385 in the processing circuitry 38 of the device body 30 determines whether the degree of coincidence of the measurement positions is equal to or greater than a threshold value (step S27). If the degree of coincidence of the measurement positions is not equal to or greater than the threshold value in step S27 (step S27: No), the position control function 386 in the processing circuitry 38 of the device body 30 moves the position of the PWD marker (step S29). Specifically, the position control function 386 moves the position of the marker MA2 set on the two-dimensional B-mode image IM1 so that the degree of coincidence between the first measurement position information and the second measurement position information increases. More specifically, for example, the position control function 386 moves the position of the marker MA2 set on the two-dimensional B-mode image IM1 so that the position becomes the same as the position of the marker MA1 set on the target image TA1.

[0067] The process of step S17 after step S29 or when the degree of coincidence of the measurement positions is equal to or greater than the threshold value in step S27 (step S27: No) is the same as that in the first embodiment, and therefore will not be described again. Then, in step S17, the mode transition process is terminated by transitioning to the PWD mode.

[0068] As described above, the ultrasound diagnostic device 1 acquires a two-dimensional ultrasound image and a measurement position on the two-dimensional ultrasound image, calculates the degree of coincidence of the images, determines whether the degree of coincidence of the images is equal to or greater than a threshold, calculates the degree of coincidence of the measurement position if the degree of coincidence of the images is equal to or greater than the threshold, determines whether the degree of coincidence of the measurement position is equal to or greater than a threshold, and controls the position of the PWD marker and transitions to the PWD mode if the degree of coincidence of the measurement position is equal to or less than the threshold.Therefore, the ultrasound diagnostic device 1 assists the user in performing a user operation for setting a PWD marker on the two-dimensional ultrasound image and a user operation for transitioning to the PWD mode, allowing the user to concentrate on depicting the two-dimensional ultrasound image.

[0069] [Fourth embodiment] In the ultrasound diagnostic apparatus 1 according to the first embodiment described above, it is also possible to notify the user of the calculated degree of coincidence. Below, a case where this modification is applied to the first embodiment will be described as a fourth embodiment, and differences from the first embodiment described above will be explained. Note that although the following describes a case where this modification is applied to the first embodiment, this modification can also be applied to the second and third embodiments described above.

[0070] Fig. 7 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus 1 according to the fourth embodiment, and corresponds to Fig. 1. As shown in Fig. 7, the ultrasound diagnostic apparatus 1 according to this embodiment is configured by adding a notification function 387 to the processing circuitry 38 of the ultrasound diagnostic apparatus 1 according to the first embodiment. Note that the configuration and functions other than the notification function 387 are the same as those in Fig. 1 of the first embodiment described above, and therefore description thereof will be omitted.

[0071] The notification function 387 notifies the degree of match between the two-dimensional ultrasound image and its measurement position and the target image TA1 and the measurement position on the target image TA1. Specifically, the notification function 387 notifies the degree of match between the two-dimensional ultrasound image and its measurement position and the target image TA1 and the measurement position on the target image TA1 by one of color, number, and sound, or a combination of two or more of color, number, and sound.

[0072] FIG. 8 is a flowchart illustrating mode transition processing executed in the ultrasound diagnostic apparatus 1 according to the fourth embodiment, and corresponds to FIG. 4. The mode transition processing according to the fourth embodiment includes acquiring a two-dimensional ultrasound image and measurement positions, calculating the degree of coincidence between the two-dimensional ultrasound image and its measurement positions and the target image TA1 and the measurement positions on the target image TA1, determining whether the degree of coincidence is equal to or greater than a threshold, transitioning to PWD mode, and notifying the calculated degree of coincidence. For example, the mode transition processing is executed when processing to set measurement positions on a two-dimensional ultrasound image is started. Note that the processing from step S11 to step S17 shown in FIG. 8 is the same as that in FIG. 4, and therefore description thereof will be omitted.

[0073] 8, the notification function 387 in the processing circuit 38 of the device main body 30 notifies the user of the degree of match (step S31). Specifically, the notification function 387 notifies the user of the degree of match between the two-dimensional ultrasound image and its measurement position calculated by the calculation function 384 in step S13, and the target image TA1 and the measurement position on the target image TA1.

[0074] Fig. 9 is a diagram showing an example of a two-dimensional ultrasound image and a Doppler waveform displayed on the display 70 in the ultrasound diagnostic apparatus 1 according to the fourth embodiment, and corresponds to Fig. 3. In the example shown in Fig. 9, the display control function 382 causes the display 70 to display a two-dimensional B-mode image IM1 as a two-dimensional ultrasound image, a Doppler waveform WA1, and a marker MA2 indicating a measurement position on the two-dimensional B-mode image IM1, and the notification function 387 notifies the user by displaying "90%" near the Doppler waveform WA1, which is the number indicating the degree of coincidence between the two-dimensional B-mode image IM1 and its measurement position and the target image TA1 and the measurement position on the target image TA1.

[0075] In step S31, the degree of match is notified, and the mode transition process ends.

[0076] As described above, the ultrasound diagnostic device 1 acquires a two-dimensional ultrasound image and a measurement position on the two-dimensional ultrasound image, calculates the degree of coincidence between the two-dimensional ultrasound image and its measurement position and the target image TA1 and the measurement position on the target image TA1, determines whether the degree of coincidence is equal to or greater than a threshold, and if the degree of coincidence is equal to or greater than the threshold, transitions to PWD mode and notifies the user of the calculated degree of coincidence, allowing the user to determine whether or not the PWD marker was successfully set at the intended measurement position on the intended two-dimensional ultrasound image.

[0077] In the above-described fourth embodiment, the notification function 387 notifies the user of one degree of coincidence between the two-dimensional ultrasound image and its measurement position, and the target image TA1 and the measurement position on the target image TA1. However, if the degree of coincidence between the two-dimensional ultrasound image and the target image TA1, and the degree of coincidence between the measurement position on the two-dimensional ultrasound image and the measurement position on the target image TA1 are calculated, the notification function 387 may notify the user of each of the degree of coincidence of the image and the degree of coincidence of the measurement position.

[0078] Furthermore, in the fourth embodiment described above, the color and number indicating the degree of match notified by the notification function 387 may be stored together with the two-dimensional ultrasound image in the image memory 36 or the storage circuitry 37. By storing the color and number indicating the degree of match together with the two-dimensional ultrasound image in this way, the user can use the color and number as a guide to check whether or not the PWD marker was placed at the intended measurement position when reviewing the examination results later.

[0079] Furthermore, in the above-described fourth embodiment, when the notification function 387 notifies the user of the color related to the degree of match, the notification function 387 may notify the user of the color related to the degree of match, for example, by changing the color of the border of the two-dimensional B-mode image or the Doppler waveform according to the degree of match.

[0080] Fifth Embodiment In the ultrasound diagnostic device 1 according to each of the above-described embodiments, the calculation function calculates the degree of coincidence between the two-dimensional ultrasound image and the first measurement position information, and the target image TA1 and the second measurement position information, and is also capable of calculating the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10. Hereinafter, a case where this modified example is applied to the first embodiment will be referred to as the fifth embodiment, and differences from the first embodiment will be described. Note that, although a case where this modified example is applied to the first embodiment will be described below, this modified example can also be applied to the second to fourth embodiments.

[0081] FIG. 10 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus 1 according to the fifth embodiment, and corresponds to FIG. 1. As shown in FIG. 10, in the ultrasound diagnostic apparatus 1 according to this embodiment, the calculation function of the processing circuitry 38 is different from that of the first embodiment, and is therefore represented as a calculation function 384a. The ultrasound diagnostic apparatus 1 according to this embodiment is configured by adding a position sensor 111, a transmitter 113, and a position sensor output storage circuit 39 to the ultrasound diagnostic apparatus 1 according to the first embodiment. Note that the configurations and functions other than the calculation function 384a, the position sensor 111, the transmitter 113, and the position sensor output storage circuit 39 are the same as those in FIG. 1 of the first embodiment, and therefore will not be described again.

[0082] The position sensor 111 and the transmitter 113 are devices (position detection system) for acquiring position information of the ultrasonic probe 10. The position sensor 111 detects the position of the ultrasonic probe 10. Specifically, for example, the position sensor 111 is a magnetic sensor attached to the ultrasonic probe 10. Also, for example, the transmitter 113 is a device that is placed at an arbitrary position and forms a magnetic field from its own device as the center toward the outside.

[0083] The position sensor 111 detects the three-dimensional magnetic field formed by the transmitter 113. Then, based on the information of the detected magnetic field, the position sensor 111 calculates the position (coordinates) and direction (angle) of the device itself in a space with the transmitter 113 as the origin, and outputs the calculated position and direction to the position sensor output storage circuit 39.

[0084] In this embodiment, the position information of the ultrasound probe 10 is acquired by the position detection system described above. However, the configuration of the position detection system is not limited to this. In other words, the configuration of the position detection system is arbitrary, and the system may be configured with, for example, a gyro sensor, an acceleration sensor, or the like.

[0085] The position sensor output storage circuit 39 stores the position of the ultrasonic probe 10 output from the position sensor 111. For example, the position sensor output storage circuit 39 stores the position of the ultrasonic probe 10 output from the position sensor 111 in chronological order, or stores the position of the ultrasonic probe 10 when the target image TA1 detected by the position sensor 111 is generated. The position of the ultrasonic probe 10 when the target image TA1 is generated is, for example, the position of the ultrasonic probe 10 when the live display of the two-dimensional B-mode image displayed live on the display 70 is frozen.

[0086] The calculation function 384a calculates the degree of coincidence between the two-dimensional ultrasonic image and the first measurement position information, and the target image TA1 and the second measurement position information, as well as the degree of coincidence between the position of the ultrasonic probe 10 when the target image TA1 detected by the position sensor 111 was generated and the current position of the ultrasonic probe 10 detected by the position sensor 111.

[0087] FIG. 11 is a flowchart illustrating mode transition processing executed in the ultrasound diagnostic apparatus 1 according to the fifth embodiment, and corresponds to FIG. 4. The mode transition processing according to the fifth embodiment involves acquiring a two-dimensional ultrasound image and measurement positions, calculating the degree of coincidence between the two-dimensional ultrasound image and its measurement positions and the target image TA1 and the measurement positions on the target image TA1, acquiring the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10, calculating the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10, determining whether the degree of coincidence is equal to or greater than a threshold, and transitioning to the PWD mode. For example, the mode transition processing is executed when processing to set measurement positions on a two-dimensional ultrasound image is started. Note that the processing in steps S11 and S13 shown in FIG. 11 is the same as that in FIG. 4, and therefore description thereof will be omitted.

[0088] 11, the acquisition function 383 in the processing circuitry 38 of the device main body 30 acquires the position of the ultrasonic probe 10 when the target image TA1 was generated and the current position of the ultrasonic probe 10 (step S41). Specifically, the acquisition function 383 acquires the position of the ultrasonic probe 10 when the target image TA1 was generated and the current position of the ultrasonic probe 10 from the position sensor output storage circuit 39.

[0089] Next, as shown in FIG. 11, the calculation function 384a in the processing circuit 38 of the device main body 30 calculates the degree of coincidence between the position of the ultrasonic probe 10 when the target image TA1 was generated and the current position of the ultrasonic probe 10 (step S43).

[0090] 11, the transition control function 385a in the processing circuitry 38 of the apparatus main body 30 determines whether the degree of coincidence is equal to or greater than a threshold (step S15a). Specifically, the transition control function 385a determines whether the degree of coincidence between the two-dimensional B-mode image IM1 and its measurement position calculated in step S13 and the target image TA1 and the measurement position on the target image TA1, and the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated calculated in step S43 and the current position of the ultrasound probe 10, are each equal to or greater than a threshold. More specifically, the transition control function 385a determines whether the degree of coincidence between the two-dimensional B-mode image IM1 and its measurement position calculated in step S13 and the target image TA1 and the measurement position on the target image TA1, and the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated calculated in step S43 and the current position of the ultrasound probe 10, are each equal to or greater than a threshold.

[0091] If the degree of coincidence is not equal to or greater than the threshold value in step S15a (step S15a: No), the process returns to step S11 described above, and the following steps are repeated: acquiring a two-dimensional ultrasound image and a measurement position on the two-dimensional ultrasound image (step S11); calculating a degree of coincidence between the two-dimensional ultrasound image and its measurement position, and the target image TA1 and the measurement position on the target image TA1 (step S13); acquiring the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10 (step S41); and calculating a degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10 (step S43). Note that if the degree of coincidence is equal to or greater than the threshold value in step S15a (step S15a: Yes), the process of step S17 after that is the same as that in the first embodiment described above, and therefore a description thereof will be omitted. Then, in step S17, the mode transition is made to the PWD mode, thereby terminating the mode transition process.

[0092] As described above, the ultrasound diagnostic device 1 acquires a two-dimensional ultrasound image and measurement positions on the two-dimensional ultrasound image, calculates the degree of coincidence between the two-dimensional ultrasound image and its measurement positions, and the target image TA1 and the measurement positions on the target image TA1, acquires the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10, calculates the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10, determines whether the degree of coincidence is equal to or greater than a threshold, and if the degree of coincidence is equal to or greater than the threshold, transitions to PWD mode. Therefore, the ultrasound diagnostic device 1 assists the user in performing an operation to transition to PWD mode, allowing the user to concentrate on depicting the two-dimensional ultrasound image.

[0093] Furthermore, the ultrasound diagnostic device 1 acquires the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10, calculates the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10, and determines whether the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated and the current position of the ultrasound probe 10 is equal to or greater than a threshold value, thereby enabling transition to the PWD mode with a more accurate position of the ultrasound probe 10.

[0094] In the ultrasonic diagnostic apparatus 1 according to the fifth embodiment described above, the position sensor output storage circuit 39 is provided, and the position of the ultrasonic probe 10 output from the position sensor 111 is stored in the position sensor output storage circuit 39. However, the position sensor output storage circuit 39 may not be provided. In this case, the position of the ultrasonic probe 10 output from the position sensor 111 may be stored in the memory circuit 37.

[0095] Furthermore, in the ultrasound diagnostic device 1 according to the fifth embodiment described above, it is determined whether or not each of the degree of coincidence between the two-dimensional ultrasound image and its measurement position calculated in step S13 and the target image TA1 and the measurement position on the target image TA1, and the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated calculated in step S43 and the current position of the ultrasound probe 10 is equal to or greater than one threshold. However, in the ultrasound diagnostic device 1 according to the fifth embodiment described above, different thresholds may be set for each of the degree of coincidence between the target image TA1 and the measurement position on the target image TA1, and the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated calculated in step S43 and the current position of the ultrasound probe 10, and it may be determined whether or not each of the degree of coincidence between the two-dimensional ultrasound image and its measurement position calculated in step S13 and the target image TA1 and the measurement position on the target image TA1, and the degree of coincidence between the position of the ultrasound probe 10 when the target image TA1 was generated calculated in step S43 and the current position of the ultrasound probe 10 is equal to or greater than the respective thresholds.

[0096] Furthermore, in the above-described fifth embodiment, the position of the ultrasound probe 10 when the target image TA1 is generated is not limited to the position of the ultrasound probe 10 when the live display of the two-dimensional B-mode image displayed live on the display 70 is frozen. If the target image is an ultrasound image in which a measurement position was set in a past ultrasound examination, the position of the ultrasound probe 10 when the target image TA1 is generated may be the position of the ultrasound probe 10 when the measurement position was set on the ultrasound probe in the past ultrasound examination. If the target image is an ultrasound image in which a measurement position was set immediately before transitioning to PWD mode, the position of the ultrasound probe 10 when the target image TA1 is generated may be the position of the ultrasound probe 10 immediately before transitioning to PWD mode.

[0097] Sixth Embodiment In the ultrasound diagnostic device 1 according to each of the above-described embodiments, the display control function 382 can also display at least one of a target image TA1 and a body mark related to the two-dimensional ultrasound image, along with the two-dimensional ultrasound image and a Doppler waveform WA1, which is blood flow information, on the display 70. Fig. 12 is a diagram showing an example of a two-dimensional ultrasound image, a Doppler waveform WA1, and a target image TA1 displayed on the display 70 in the ultrasound diagnostic device 1 according to the sixth embodiment, and corresponds to Fig. 3.

[0098] 12, the display control function 382 controls the display 70 to display a target image TA1 and a body mark BM related to the two-dimensional ultrasound image together with a two-dimensional B-mode image IM1 and a Doppler waveform WA1. Specifically, in the example shown in Fig. 12, the display control function 382 displays the target image TA1 and the body mark BM related to the two-dimensional ultrasound image alongside the two-dimensional B-mode image IM1 and the Doppler waveform WA1 on the display 70. More specifically, in the example shown in Fig. 12, the display control function 382 displays the target image TA1 above the Doppler waveform WA1 and to the left of the two-dimensional B-mode image IM1, and displays the body mark related to the two-dimensional ultrasound image above the two-dimensional B-mode image IM1.

[0099] In the example shown in FIG. 12, the display control function 382 displays the target image TA1 and the body mark BM related to the two-dimensional ultrasound image alongside the two-dimensional B-mode image IM1 and the Doppler waveform WA1 on the display 70, but the display control function 382 may also display the target image TA1 and the body mark BM superimposed on at least one of the two-dimensional B-mode image IM1 and the Doppler waveform WA1 on the display 70.

[0100] 12, the display control function 382 displays both the target image TA1 and the body mark BM on the display 70, but the display control function 382 may display either the target image TA1 or the body mark BM on the display 70. In other words, the display control function 382 may control the display 70 to display at least either the target image TA1 or the body mark BM together with the two-dimensional B-mode image IM1 and the Doppler waveform WA1.

[0101] 12, the display control function 382 displays the target image TA1 above the Doppler waveform WA1 and to the left of the two-dimensional B-mode image IM1, and displays the body mark BM above the two-dimensional B-mode image, but the display positions of the target image TA1 and the body mark BM on the display 70 are not limited to this. That is, the display positions of the target image TA1 and the body mark BM are arbitrary.

[0102] 12, the display control function 382 displays the target image TA1 and the body mark BM on the display 70 together with the two-dimensional B-mode image IM1 and the Doppler waveform WA1, but the content that the display control function 382 displays on the display 70 together with the two-dimensional B-mode image IM1 and the Doppler waveform WA1 is not limited to this. In other words, the content that is displayed on the display 70 is arbitrary, and the output result of the position sensor 111 may be displayed on the display 70.

[0103] Seventh Embodiment In the ultrasound diagnostic device 1 according to each of the above-described embodiments, the transition control function 385 controls the transition from a mode for generating a two-dimensional ultrasound image to a Doppler mode. However, the transition control function can also control the transition from a mode for generating a two-dimensional ultrasound image to a Doppler mode, and can also control the transition from a Doppler mode to a mode for generating a two-dimensional ultrasound image. Hereinafter, a case where this modification is applied to the first embodiment will be referred to as the seventh embodiment, and differences from the first embodiment will be described. Note that, although a case where this modification is applied to the first embodiment will be described below, this modification can also be applied to the second to sixth embodiments.

[0104] FIG. 13 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus 1 according to the seventh embodiment, and corresponds to FIG. 1. As shown in FIG. 13, in the device main body 30 of the ultrasound diagnostic apparatus 1 according to this embodiment, the calculation function and transition control function of the processing circuitry 38 are different from those of the first embodiment, and are therefore represented as a calculation function 384b and a transition control function 385a. The ultrasound diagnostic apparatus 1 according to this embodiment is configured by adding a position sensor 111, a transmitter 113, and a position sensor output storage circuit 39 to the ultrasound diagnostic apparatus 1 according to the first embodiment. The configurations of the position sensor 111, the transmitter 113, and the position sensor output storage circuit 39 are the same as those of the position sensor 111, the transmitter 113, and the position sensor output storage circuit 39 according to the fifth embodiment, and therefore will not be described here. Furthermore, the configurations and functions other than the calculation function 384b, transition control function 385a, position sensor 111, transmitter 113, and position sensor output storage circuit 39 are the same as those in FIG. 1 of the first embodiment described above, and therefore will not be described.

[0105] The calculation function 384b according to this embodiment calculates the degree of agreement between the two-dimensional ultrasound image and the first measurement position information, the target image TA1 in which the measurement position is set, and the second measurement position information relating to the measurement position set in the target image TA1, and also calculates the difference between the position of the ultrasound probe 10 when transitioning to the Doppler mode detected by the position sensor 111 and the current position of the ultrasound probe detected by the position sensor 111.

[0106] Furthermore, the transition control function 385a according to this embodiment determines whether or not the difference between the position of the ultrasound probe 10 at the time of transition to the Doppler mode detected by the position sensor 111 and the current position of the ultrasound probe detected by the position sensor 111 exceeds a predetermined threshold, and if the difference exceeds the predetermined threshold, controls the transition to the Doppler mode for measuring blood flow information within the subject P, and also controls the transition from the Doppler mode to a mode for generating a two-dimensional ultrasound image. The mode for generating this two-dimensional ultrasound image is, for example, B mode, color Doppler mode, M mode, etc. In the following, this embodiment will be described taking as an example a case where the mode for generating a two-dimensional ultrasound image is B mode.

[0107] FIG. 14 is a flowchart illustrating mode transition processing executed in the ultrasound diagnostic apparatus 1 according to the seventh embodiment, and corresponds to FIG. 4. The mode transition processing according to the seventh embodiment involves acquiring a two-dimensional ultrasound image and measurement positions, calculating the degree of coincidence between the two-dimensional ultrasound image and its measurement positions and the target image TA1 and the measurement positions on the target image TA1, determining whether the degree of coincidence is equal to or greater than a threshold, transitioning to PWD mode, acquiring the position of the ultrasound probe 10 when transitioning to PWD mode, acquiring the current position of the ultrasound probe 10, calculating the difference between the position of the ultrasound probe 10 when transitioning to PWD mode and the current position of the ultrasound probe 10, determining whether the difference exceeds a threshold, and transitioning to B mode. For example, the mode transition processing is executed when processing to set measurement positions in a two-dimensional ultrasound image is started. Note that the processing from step S11 to step S17 is the same as that in FIG. 4, and therefore description thereof will be omitted.

[0108] 14, the acquisition function 383 in the processing circuitry 38 of the device main body 30 acquires the position of the ultrasonic probe 10 when the mode transitions to the PWD mode (step S51). Specifically, the acquisition function 383 acquires the position of the ultrasonic probe 10 when the mode transitions to the PWD mode in step S17 from the position sensor output storage circuit 39.

[0109] 14, the acquisition function 383 in the processing circuit 38 of the device main body 30 acquires the current position of the ultrasonic probe 10 (step S53). Specifically, the acquisition function 383 acquires the current position of the ultrasonic probe 10 from the position sensor output storage circuit 39.

[0110] 14, the calculation function 384b in the processing circuitry 38 of the device main body 30 calculates the difference between the position of the ultrasonic probe 10 when the mode transitioned to the PWD mode and the current position of the ultrasonic probe 10 (step S55). Specifically, the calculation function 384b calculates the difference between the position of the ultrasonic probe 10 when the mode transitioned to the PWD mode and the current position of the ultrasonic probe 10 based on the position of the ultrasonic probe 10 when the mode transitioned to the PWD mode acquired by the acquisition function 383 in step S51 and the current position of the ultrasonic probe 10 acquired by the acquisition function 383 in step S53.

[0111] 14, the transition control function 385a in the processing circuitry 38 of the device main body 30 determines whether or not the difference exceeds a threshold value (step S57). Specifically, the transition control function 385a determines whether or not the difference between the position of the ultrasonic probe 10 at the time of transition to the PWD mode, calculated in step S55, and the current position of the ultrasonic probe 10 exceeds a threshold value. If the difference does not exceed the threshold value in step S57 (step S57: No), the process returns to the above-mentioned step S53, and waits while repeating the process of acquiring the current position of the ultrasonic probe 10 (step S53) and the process of calculating the difference between the position of the ultrasonic probe 10 at the time of transition to the PWD mode and the current position of the ultrasonic probe 10 (step S45).

[0112] On the other hand, if the difference exceeds the threshold value in step S57 (step S57: Yes), the transition control function 385a in the processing circuitry 38 of the device main body 30 transitions to B mode (step S59). Specifically, the transition control function 385a transitions from PWD mode to B mode. Then, when the transition control function 385a transitions to PWD mode, the display control function 382 freezes the live display of the Doppler waveform WA1 and controls the display 70 to display a live two-dimensional ultrasound image.

[0113] The mode transition process shown in FIG. 14 is repeatedly executed while the user is performing an examination, and ends when the user has finished the examination.

[0114] As described above, the ultrasound diagnostic device 1 acquires a two-dimensional ultrasound image and a measurement position on the two-dimensional ultrasound image, calculates the degree of coincidence between the two-dimensional ultrasound image and its measurement position, and the target image TA1 and the measurement position on the target image TA1, determines whether the degree of coincidence is equal to or greater than a threshold, and if the degree of coincidence is equal to or greater than the threshold, transitions to PWD mode, acquires the position of the ultrasound probe 10 when transitioning to PWD mode and the current position of the ultrasound probe 10, calculates the difference between the position of the ultrasound probe 10 when transitioning to PWD mode and the current position of the ultrasound probe 10, determines whether the difference exceeds a threshold, and if the difference exceeds the threshold, transitions to B mode. Therefore, even if the measurement position of the ultrasound probe 10 is deviated, it is possible to automatically start from setting a marker indicating the measurement position in B mode.

[0115] In the seventh embodiment described above, the transition control function 385a transitions to a mode for generating a two-dimensional ultrasonic image when the difference between the position of the ultrasonic probe 10 at the time of transition to the PWD mode and the current position of the ultrasonic probe 10 exceeds a threshold value, but the transition control function 385a may also control the transition from the PWD mode to a mode for generating a two-dimensional ultrasonic image when a blood flow signal cannot be detected in the Doppler mode. In such a case, even if a blood flow signal cannot be detected due to a shift in the position of the ultrasonic probe 10, it is possible to automatically start from setting the measurement position in the mode for generating a two-dimensional ultrasonic image.

[0116] Eighth Embodiment In the ultrasound diagnostic device 1 according to each of the above-described embodiments, the calculation function 384 calculates the degree of coincidence between the entire two-dimensional ultrasound image and the first measurement position information and the entire target image and the second measurement position information. However, it is also possible to calculate the degree of coincidence between an image around a measurement position in a two-dimensional ultrasound image and the first measurement position information and an image around a measurement position in a target image TA1 and the second measurement position information. Hereinafter, a case where this modification is applied to the first embodiment will be referred to as the eighth embodiment, and differences from the first embodiment will be described. Note that, although a case where this modification is applied to the first embodiment will be described below, this modification can also be applied to the second to seventh embodiments described above.

[0117] Although the configuration of the ultrasound diagnostic apparatus 1 according to the eighth embodiment is not shown, the calculation function of the processing circuit is different from that of the first embodiment, and therefore the calculation function will be referred to as calculation function 384c below. Furthermore, the configuration and functions other than calculation function 384c are the same as those in FIG. 1, and therefore description thereof will be omitted.

[0118] The calculation function 384c calculates the degree of coincidence between the two-dimensional ultrasound image and the first measurement position information, and the target image TA1 and the second measurement position information, by calculating the degree of coincidence between an image around the first measurement position information in the two-dimensional ultrasound image in which the measurement position is set by setting the first measurement position information, and an image around the second measurement position information in the target image TA1 in which the measurement position is set by setting the second measurement position information. Specifically, the calculation function 384c calculates the degree of coincidence between a first image of a predetermined range centered on the first measurement position information in the two-dimensional ultrasound image in which the measurement position is set by setting the first measurement position information, and a second image of a predetermined range centered on the second measurement position information in the target image TA1 in which the measurement position is set by setting the second measurement position information.

[0119] The mode transition process according to this embodiment is similar to that of the first embodiment. Figures 15 and 16 are diagrams illustrating steps S11 and S13 when the ultrasound diagnostic device 1 according to this embodiment executes the mode transition process shown in Figure 4.

[0120] 15 is a diagram showing an example of a process in which the acquisition function 383 acquires a two-dimensional B-mode image and a marker, which is an example of second identification information, in step S11 of the mode transition processing executed in the ultrasound diagnostic apparatus 1 according to the eighth embodiment. As shown in FIG. 15, in step S11, the acquisition function 383 acquires a two-dimensional B-mode image IM1a and a marker MA2a, which is an example of second identification information. The two-dimensional B-mode image IM1a shown in FIG. 15 is an image that includes a part of the target image TA1 shown in FIG. 2.

[0121] FIG. 16 is a diagram illustrating an example of a process in which the calculation function 384c calculates the degree of coincidence between a 2D ultrasound image and its measurement position and a target image TA1 and its measurement position in step S13 of the mode transition process executed by the ultrasound diagnostic apparatus 1 according to the eighth embodiment. First, the calculation function 384c extracts an image surrounding the marker MA1 in the target image TA1. Specifically, as shown in FIG. 16(a), the calculation function 384c extracts a second image IMA2 of a predetermined range RA1 centered on the marker MA1 in the target image TA1, where the measurement position is set by setting the marker MA1. Note that in the example shown in FIG. 16(a), the second image IMA2 of the predetermined range RA1 centered on the marker MA1 in the target image TA1 is extracted, but the second image IMA2 does not have to be the predetermined range RA1 centered on the marker MA2. In other words, the method of extracting the second image IMA2 is arbitrary, as long as the second image IMA2 is extracted in a predetermined range including the marker MA1 in the target image TA1.

[0122] Next, as shown in FIG. 16(b), the calculation function 384c extracts an image around the marker MA2 in the two-dimensional B-mode image IM1. Specifically, as shown in FIG. 16(b), the calculation function 384c extracts a first image IMA1 of a predetermined range RA2 centered on the marker MA2 in the two-dimensional B-mode image IM1 in which the measurement position is set by setting the marker MA2. Note that in the example shown in FIG. 16(b), the first image IMA1 of the predetermined range RA2 centered on the marker MA2 in the two-dimensional B-mode image IM1 is extracted, but the first image IMA1 does not have to be the predetermined range RA2 centered on the marker MA1. In other words, the method of extracting the first image IMA1 is arbitrary, as long as the first image IMA1 is extracted in a predetermined range including the marker MA2 in the two-dimensional B-mode image IM1.

[0123] Then, in step S13, the calculation function 384c calculates the degree of coincidence between the first image IMA1 and the second image IMA2 as the degree of coincidence between the two-dimensional ultrasound image and the first measurement position information and the target image TA1 and the second measurement position information. As described above, the processes in steps S15 and S17 after this step S13 are the same as those in the first embodiment, and therefore, description thereof will be omitted.

[0124] As described above, according to the ultrasound diagnostic device 1 of this embodiment, the degree of coincidence between the two-dimensional ultrasound image and the first measurement position information and the target image TA1 and the second measurement position information is calculated by calculating the degree of coincidence between the image around the first measurement position information in the two-dimensional ultrasound image in which the measurement position is set by setting the first measurement position information and the image around the second measurement position information in the target image TA1 in which the measurement position is set by setting the second measurement position information. Therefore, even if the degree of coincidence between the entire target image TA1 and the entire two-dimensional ultrasound image is low, if the degree of coincidence between the image around the first measurement position information in the two-dimensional ultrasound image and the image around the second measurement position information in the target image TA1 is equal to or greater than a threshold, the transition to Doppler mode is controlled. Therefore, the user only needs to render an image including the image around the second measurement position information in the target image TA1 as a two-dimensional ultrasound image, thereby improving user convenience.

[0125] [Other Modifications] In the first to seventh embodiments described above, the calculation functions 384, 384a, and 384b may weight the images according to the measurement positions when calculating the degree of match between the images. Specifically, the calculation functions 384, 384a, and 384b may set weights on the images so that a high weight value is assigned to an image in an area close to the position where the marker indicating the measurement position is set, and the weight value decreases as the image becomes farther away from the position where the marker indicating the measurement position is set, and may calculate the degree of match between the images taking the weighting into consideration.

[0126] In the above-described first to seventh embodiments, the two-dimensional ultrasound image and the target image TA1 are two-dimensional B-mode images IM1, but the two-dimensional ultrasound image and the target image TA1 may be two-dimensional color Doppler images. In addition, the Doppler mode is PWD mode, but the Doppler mode may be CWD mode.

[0127] In the first to seventh embodiments described above, the first measurement position information and the second measurement position information are markers indicating measurement positions set on the two-dimensional ultrasound image and the target image TA1, respectively, but are not limited to this. That is, the contents of the first measurement position information and the second measurement position information are arbitrary, and may be, for example, XY coordinates indicating the positions of markers set on the two-dimensional ultrasound image and the target image TA1, respectively, based on an arbitrary position on the image, or XY coordinates indicating the positions of markers set on the two-dimensional ultrasound image and the target image TA1, respectively, based on the ultrasound probe 10.

[0128] Furthermore, in the seventh embodiment described above, the transition control function 385a controls the transition from the PWD mode to the mode for generating a two-dimensional ultrasonic image when the difference between the position of the ultrasonic probe 10 at the time of transition to the PWD mode and the current position of the ultrasonic probe 10 exceeds a threshold value, or when a blood flow signal cannot be detected. However, the transition control function 385a may also control the transition from the PWD mode to another mode different from the mode for generating a two-dimensional ultrasonic image.

[0129] The term "processor" used in the above description refers to a circuit such as a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), a programmable logic device (e.g., a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA)). The processor realizes its functions by reading and executing a program stored in the memory circuit 37. Instead of storing the program in the memory circuit 37, the processor may be configured so that the program is directly embedded in its circuit. In this case, the processor realizes its functions by reading and executing the program embedded in the circuit. The processor is not limited to being configured as a single circuit, but may be configured as a single processor by combining multiple independent circuits to realize its functions. Furthermore, multiple components in FIG. 1 may be integrated into a single processor to realize its functions.

[0130] Although several embodiments have been described above, these embodiments are presented only as examples and are not intended to limit the scope of the invention. The novel apparatus and method described herein may be embodied in various other forms. Furthermore, various omissions, substitutions, and modifications may be made to the forms of the apparatus and method described herein without departing from the spirit of the invention. The appended claims and their equivalents are intended to cover such forms and modifications that fall within the scope and spirit of the invention. [Explanation of symbols]

[0131] 1...ultrasound diagnostic device, 10...ultrasound probe, 30...device main body, 31...transmission circuit, 32...receiving circuit, 33...B-mode processing circuit, 34...Doppler processing circuit, 35...image generation circuit, 36...image memory, 37...memory circuit, 38...processing circuit, 39...position sensor output storage circuit, 50...input device, 70...display, 111...position sensor, 113...transmitter, 381...system control function, 382...display control function, 383...acquisition function, 384, 384a, 384b, 384c...calculation function, 385, 385a...transition control function, 386...position control function, 387...notification function

Claims

1. an acquisition unit that acquires a two-dimensional ultrasound image generated based on a signal received by the ultrasound probe and first measurement position information related to a measurement position for measuring blood flow information set in the two-dimensional ultrasound image; a calculation unit that calculates a degree of coincidence between the two-dimensional ultrasound image and the first measurement position information, and a reference image in which measurement positions are set and second measurement position information regarding the measurement positions set in the reference image; a transition control unit that controls a transition to a Doppler mode for measuring blood flow information in the subject based on the calculation result of the calculation unit; An ultrasound diagnostic device comprising:

2. 2. The ultrasound diagnostic device according to claim 1, wherein the reference image is any one of an ultrasound image in which the measurement position is set in a frozen state of live display of the two-dimensional ultrasound image, an ultrasound image in which the measurement position is set in a past ultrasound examination, and an ultrasound image in which the measurement position is set immediately before transitioning to the Doppler mode.

3. 2. The ultrasound diagnostic apparatus according to claim 1, further comprising a position control unit that controls a position of a marker that indicates the measurement position set on the two-dimensional ultrasound image so that the degree of coincidence between the first measurement position information and the second measurement position information increases.

4. 2. The ultrasound diagnostic apparatus according to claim 1, further comprising a notification unit that notifies a user of a degree of coincidence between the two-dimensional ultrasound image and the first measurement position information, and a reference image in which measurement positions are set and second measurement position information regarding the measurement positions set in the reference image.

5. 5. The ultrasound diagnostic device according to claim 4, wherein the notification unit notifies the degree of match between the two-dimensional ultrasound image and the first measurement position information and the reference image and the second measurement position information by one of a color, a number, and a sound, or a combination of two or more of a color, a number, and a sound.

6. The ultrasonic diagnostic apparatus according to claim 1 , further comprising a position sensor that detects the position of the ultrasonic probe.

7. 7. The ultrasound diagnostic device according to claim 6, wherein the calculation unit calculates a degree of coincidence between the two-dimensional ultrasound image and the first measurement position information, a reference image in which measurement positions are set, and second measurement position information related to the measurement positions set in the reference image, as well as a degree of coincidence between a position of the ultrasound probe detected by the position sensor when the reference image was generated and a current position of the ultrasound probe detected by the position sensor.

8. The transition control unit determining whether or not a difference between the position of the ultrasound probe at the time of transition to the Doppler mode detected by the position sensor and the current position of the ultrasound probe detected by the position sensor exceeds a predetermined threshold; and controlling a transition from the Doppler mode to a mode for generating the two-dimensional ultrasound image when the difference exceeds a predetermined threshold. The ultrasonic diagnostic apparatus according to claim 6.

9. The ultrasonic diagnostic apparatus according to claim 1 , wherein the transition control unit controls transition from the Doppler mode to a mode for generating the two-dimensional ultrasonic image when a blood flow signal cannot be detected in the Doppler mode.

10. 2. The ultrasound diagnostic apparatus according to claim 1, further comprising a display control unit that controls the display unit to freeze the live display of the two-dimensional ultrasound image and to live display a Doppler waveform in the blood flow information when the transition to the Doppler mode is made by the transition control unit.

11. 11. The ultrasound diagnostic apparatus according to claim 10, wherein the display control unit controls the display unit to display at least one of the reference image and a body mark related to the two-dimensional ultrasound image together with the two-dimensional ultrasound image and the blood flow information.

12. The ultrasound diagnostic apparatus according to claim 10 , wherein the display control unit causes the display unit to display at least one of the reference image and a body mark together with the two-dimensional ultrasound image and the blood flow information.

13. 11. The ultrasound diagnostic device according to claim 10, wherein the display control unit causes the display unit to display at least one of the reference image and a body mark related to the two-dimensional ultrasound image superimposed on at least one of the two-dimensional ultrasound image and the blood flow information.

14. 2. The ultrasound diagnostic device according to claim 1, wherein the calculation unit calculates, as the degree of coincidence between the two-dimensional ultrasound image and the first measurement position information, and the reference image and the second measurement position information, a degree of coincidence between an image around the first measurement position information in the two-dimensional ultrasound image, in which measurement positions are set by setting the first measurement position information, and an image around the second measurement position information in the reference image, in which the measurement positions are set by setting the second measurement position information.

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