JP4764521B2 - Ultrasonic diagnostic equipment - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus that efficiently executes a diagnosis / analysis protocol for the purpose of measurement in the contrast echo method, which is mainly a transient diagnosis.

  Ultrasound diagnosis is a simple operation by simply touching the ultrasound probe from the body surface, and the heart beats and fetal movements can be obtained in real-time display. Is smaller than other diagnostic devices such as X-ray, CT, and MRI, and it is easy to perform inspection while moving to the bedside. Moreover, since there is no influence of exposure like an X-ray etc., there also exists an advantage that it can be used comparatively in comfort.

  As an imaging method using this ultrasonic diagnostic apparatus, there is a contrast echo method (contrast echo method) using an intravenous administration type ultrasonic contrast agent. The purpose of this imaging method is to intensify blood flow signals by injecting an ultrasonic contrast agent from a vein in examinations of the heart and abdominal organs, and to evaluate blood flow dynamics. In many contrast agents, microbubbles serve as a reflection source, and the contrast effect increases if the injection amount / concentration is high. On the other hand, it is also known that due to the nature of the delicate substrate, bubbles, the bubbles are broken by irradiation with ultrasonic waves, and the contrast effect time is shortened.

  In recent years, many quantitative analysis methods for evaluating blood flow dynamics have been studied with respect to this contrast echo method. The most basic is the so-called Time Intensity Curve (TIC) measurement in which the process of enhancing the echo signal in the region of interest after administration of the contrast agent is traced and the luminance change with time is graphed.

  In general, in quantitative analysis, even if the method is theoretically valid, it is easy to predict that the accuracy of analysis will decline unless measurement data suitable for the analysis is acquired. Factors that reduce the analysis accuracy include the main body of the diagnostic system, a doctor or laboratory technician who scans the patient using the system (hereinafter, the person who uses the ultrasonic diagnostic apparatus is simply referred to as “operator”), and the living body of the patient. It exists in many areas such as functions.

  For example, as a factor existing in the diagnostic system main body, the intrinsic S / N ratio of the system is low and a signal sufficient for analysis cannot be obtained. There may be a case where the analysis values are different and the analysis values are different in each part.

  As a factor that exists for the operator, even when it is necessary to continuously record image information of the same cross section, a case where the cross section gradually shifts unintentionally can be considered.

  As a factor existing in the biological function, a decrease in analysis accuracy based on breathing or heartbeat fluctuation can be considered. For example, when the analysis assumption is a steady flow, a change in blood flow velocity due to pulsation is an undesirable event.

  The present invention has been made in view of the above circumstances, and when executing a diagnostic protocol mainly intended for measurement, a support function that reduces the error factor of analysis as much as possible, or an analysis method using the above function It is providing the ultrasonic diagnostic apparatus which equipped.

  In order to achieve the above object, the present invention takes the following measures.

According to the first aspect of the present invention, a plurality of diagnostic images collected over a plurality of cycles based on a biological signal of a subject are arranged over time, and each cycle is used by using the arranged images. Executes quantitative analysis on the corresponding time phases and obtains analysis curves for the analysis processes for multiple time phases, and analysis curves corresponding to the plurality of time phases acquired by the analysis processing are superimposed and displayed An ultrasonic diagnostic apparatus comprising: a display unit configured to display the display unit .

  As described above, according to the present invention, when executing a diagnostic protocol mainly for measurement, an ultrasonic diagnostic apparatus having a support function that reduces the error factors of analysis as much as possible, or an analysis method using the above function. Can be realized.

FIG. 1 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus 10 according to the first and second embodiments. FIG. 2 is a schematic diagram of an ultrasound diagnostic image, showing an organ boundary 51, a characteristic part 52 in the organ, and a main blood vessel 53. FIG. 3 schematically shows a cross-section holding support image. FIG. 4 is a diagram showing an ultrasonic image of one heart beat in the upper stage and a cross-section holding support image in the same cardiac phase corresponding to the lower stage. FIG. 5 is a diagram for explaining the distribution state of the transmission sound pressure to the end portion by electronic scanning. FIG. 6 is a diagram for explaining the scanning line interval in the sector (fan-shaped) scan. FIG. 7 shows a distribution pattern of ultrasonic transmission drive sound pressure values related to a normal ultrasonic image. FIG. 8 is a diagram illustrating a state in which the operator designates a region of interest using a position detection device provided on the screen of the display unit 28. FIG. 9 shows a change with time (TIC) of a luminance histogram measured by a conventional ultrasonic diagnostic apparatus. FIG. 10 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus 70 according to the third embodiment. FIG. 11 shows a diagram in which image data recorded as a one-dimensional array over time is rearranged from electrocardiogram information to two-dimensional array information for each heartbeat. FIG. 12 shows the change over time (TIC) of the luminance histogram measured by the ultrasonic diagnostic apparatus according to the present invention.

  Hereinafter, first to third embodiments of the present invention will be described with reference to the drawings. Note that the ultrasonic diagnostic apparatus according to the present invention, when executing a diagnostic protocol for the purpose of measurement, for example, quantitative analysis (TIC) using a contrast agent, measurement of blood flow velocity and blood flow in a blood vessel or heart, etc. Alternatively, it has a support function that can be used when a diagnostic protocol for stress echo is executed. In the following description, a case where a diagnostic protocol related to quantitative analysis (TIC) using a contrast agent is executed will be described as an example for convenience of description. In the following description, components having substantially the same functions and configurations are denoted by the same reference numerals, and redundant description will be provided only when necessary.

(First embodiment)
FIG. 1 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus 10 according to the present embodiment. First, the configuration and signal flow of the ultrasonic diagnostic apparatus 10 will be described with reference to FIG.

  The ultrasonic diagnostic apparatus 10 includes an ultrasonic probe 12 responsible for transmitting and receiving ultrasonic signals to and from a subject, an apparatus main body 11 that drives the ultrasonic probe and processes reception signals of the ultrasonic probe, and the apparatus main body. And an input unit 13 that can input instruction information from the operator to the apparatus main body, and an ECG 14 that measures an electrocardiographic waveform. The input unit 13 includes buttons, a keyboard, a trackball, and the like that can control the diagnostic apparatus and set various image quality conditions.

  The apparatus main body 11 includes an ultrasonic transmission unit 21, an ultrasonic consultation unit 22, a B-mode processing circuit 23, a Doppler processing circuit 24, an image processing circuit 25, an image memory circuit 26, a display unit 28, a heart rate detection unit 29, and a storage medium 30. , A controller 31, a network circuit 32, and a graphic circuit 33.

  Although not shown, the ultrasonic transmission unit 21 includes a trigger generator, a delay circuit, and a pulsar circuit. The ultrasonic transmission unit 21 generates a pulsed ultrasonic wave and sends it to the vibration element of the probe 12 to generate a convergent ultrasonic pulse. The echo signal scattered by the tissue in the subject is received by the probe 12 again.

  The echo signal output from the probe 12 for each element is taken into the ultrasonic receiving unit 22. Here, although not shown, the echo signal is amplified by a preamplifier for each channel, given a delay time necessary for determining reception directivity by a reception delay circuit after A / D conversion, and added by an adder. By this addition, the reflection component from the direction corresponding to the reception directivity is emphasized. A comprehensive ultrasonic beam for transmission and reception is formed by the transmission directivity and the reception directivity.

  The output from the ultrasonic receiving unit 22 is sent to the B mode processing circuit 23. Here, logarithmic amplification of the echo signal, envelope detection processing, and the like are performed, and the signal intensity is data expressed by brightness. The Doppler processing circuit 24 performs frequency analysis on the speed information from the echo signal and sends the analysis result to the image processing circuit 25.

  In the image processing circuit 25, the scanning line signal sequence of the ultrasonic scan is converted into a scanning line signal sequence of a general video format represented by a television or the like, and character information and scales of various setting parameters, or described later. Are combined with the graphic image of the present invention and output to the display unit 28 as a video signal. Thus, a tomographic image representing the subject tissue shape is displayed. The display unit 28 also functions as a console window when executing various analysis programs.

  In addition, the image processing circuit 25 performs graphing of the change with time in luminance in the region of interest based on the input image signal. This graph is called TIC (Time Intensity Curve) and is used for quantitatively grasping the process of enhancing the echo signal in the region of interest.

  The image memory circuit 26 includes a storage memory for storing image data. This information can be called by an operator after diagnosis, for example, and a moving image can be reproduced using a plurality of pieces.

  The storage medium 30 regularly stores image data in the image memory circuit and stores various software programs used for the analysis program. For example, a control program related to ultrasonic transmission / reception when the focus point is moved to a specific area indicated in the ultrasonic image, which is described in the second embodiment, is stored in the storage medium 30. The data in the storage medium 30 can also be transferred to the external peripheral device via the network circuit 31 by wired or wireless transfer means.

  The graphic circuit 33 is a characteristic part of the present invention. The graphic circuit 33 performs image processing again on the diagnostic image generated by the image processing circuit 25 to generate a new image, or generates an image for diagnosis support. Transfer to the processing circuit 25. At this time, the image processing circuit 25 superimposes and displays the image generated by the graphic processing circuit 33 and the current diagnostic moving image on the display unit 28 by various image processing means described later.

  Biological signal information such as an electrocardiogram obtained by the ECG 14 is converted into a digital signal by the heartbeat detection unit 29, synthesized with a diagnostic image by the image processing circuit 25, and displayed on a display unit or recorded in an image memory.

  The controller 32 has a function as an information processing apparatus (computer), and is a control unit that controls the operation of a necessary circuit based on an instruction from the input unit 13.

  The display unit 28 is a display unit composed of a CRT or the like.

  Next, the operation of the ultrasonic diagnostic apparatus 10 when executing a diagnostic protocol related to quantitative analysis (TIC) using a contrast agent will be described with reference to FIG.

  FIG. 2 is a schematic diagram of an ultrasonic diagnostic image, in which an organ boundary 51 (for example, the contour of the heart of the liver, the intima of the heart), a characteristic part 52 in the organ (for example, the gallbladder and the heart in the observation of the liver) Valve, etc.), major blood vessels 53 (eg, liver, major blood vessels in the kidney, carotid artery, etc.).

  In general, in an ultrasound image, the organ boundary 51 is recognized as an image having higher luminance than the tissue, and the main blood vessel 53 is recognized as an image having lower luminance than the tissue.

  As described above, when acquiring data used for quantitative analysis or the like, it is necessary to continuously observe the same cross section. In such a case, the operator usually holds the probe with the features such as the organ boundary 51 displayed, the characteristic part 52 in the organ, and the main blood vessel 53 as a mark for observation. Maintains the same cross section.

  The ultrasonic diagnostic apparatus 10 has a support function when the operator needs to hold the same probe section in this way. That is, when it is necessary to hold the same probe cross section, first, the operator instructs the controller 21 by operating the button from the input unit 13. In response to the instruction, the image processing circuit 25 transfers the image data generated at that time to the graphic circuit 33. The graphic circuit 33 creates a “cross-section support image” based on the image data and transfers it to the image processing circuit 25. The image processing circuit 25 synthesizes the above-described cross-section support image and the diagnostic image that is subsequently sent, superimposes them, and displays them on the display unit 28.

  Here, the cross-section holding support image will be described. This image is displayed, for example, by superimposing an ultrasonic image as a reference for maintaining a cross section with transparency and superimposing it on a diagnostic moving image. By doing so, the moving image can be observed through the translucent cross-section holding support image. If the cross section of the moving image changes, the two images are projected in a shifted state, and an unnatural image is obtained, so that the operator can detect this.

  In addition to the above example, a cross-section holding support image obtained by extracting the contour of an organ or the like can also be employed. Alternatively, according to the method described below, it is possible to create a cross-section holding support image that allows a master-slave relationship with a moving image to be easily grasped by a relatively simple process.

That is, the graphic circuit 33 generates a cross-section holding support image that can be superimposed and displayed without any trouble in the observation of the diagnostic moving image, for example, by any one of the following methods (1) to (3). ) Threshold processing is performed on the luminance level for the acquired image, and only pixels above a certain threshold are extracted, and the rest are deleted. The portion of the image extracted by the threshold processing may be used as it is, but may be further binarized or converted into a color code such as red or blue. According to this method, the organ boundary 51 is mainly extracted in the example of FIG.

  (2) Threshold processing is performed on the luminance level of the acquired image, and only pixels (black portions) that are below a certain threshold are extracted, and the rest are deleted. Similarly, the extracted portion is subjected to luminance inversion processing, once provided with luminance information, and then converted into a color code. According to this method, in the example of FIG. 2, the characteristic part 52 in the organ, mainly the main blood vessel 53 is extracted.

  (3) Pixels higher than the first threshold value and pixels lower than the second threshold value with respect to the luminance level are extracted and given the same luminance information or color information (that is, one color) Display like a pen drawing). According to this method, all of the organ boundary 51, the characteristic part 52 in the organ, and the main blood vessel 53 are mainly extracted in the example of FIG.

  In addition, a configuration may be employed in which only a specific portion is extracted as an image by performing a predetermined process after image extraction by the above methods (1) to (3). This is because, if threshold processing is simply performed at the luminance level, a bright part or a dark part of a general speckle pattern (checkered pattern) in an organ may be extracted. For example, in the method of (1), in a case where a part in the organ is scattered in a dotted shape in addition to the organ boundary 51, by performing processing such as narrowing down to only a part having a certain area, Information that is not useful as a reference for maintaining a fault plane can be deleted. As a result, it is possible to extract only clearly characteristic structures.

  FIG. 3 is an image obtained by the above method (3), schematically showing an image that is marked with a pen or the like on a characteristic part of an ultrasonic image that is a reference for maintaining a cross section. Yes. By superimposing such a cross-section holding support image on the moving image, the operator can hold the probe with care so that the diagnostic image being observed matches the mark.

  Note that the image processing and the superposition method described in this embodiment can be performed on a plurality of images, and for example, it can be predicted that the heart is a periodic motion.

  FIG. 4 is a diagram showing an ultrasound image of one heart beat in the upper stage and a cross-section holding support image of the same cardiac time phase corresponding to the lower stage.

  In this case, a plurality of images for one cycle of the heartbeat are recorded, the image processing circuit 25 performs the same image processing as described above, and the lower-section holding support image shown in FIG. It is displayed superimposed on the upper ultrasound image.

  According to such a configuration, for example, when the intima or outer membrane of the heart is used as a characteristic pattern, it is possible to observe the line drawing corresponding to the intima or outer membrane so as to expand and contract. Note that information on the heartbeat time phase based on the heartbeat detection unit 29 is added to this image, and the image is superimposed and displayed in synchronization with the heartbeat time phase of the current diagnostic moving image.

  According to the support function to reliably acquire the data necessary for such a diagnosis / analysis protocol, it is possible to obtain an image as if it was marked with a pen or the like on the characteristic part of the image under examination. Can do. By using this image as a tomographic support image, the operator can maintain the same tomographic plane by operating the probe so that the diagnostic image being observed matches the characteristic part of the tomographic support image. Inspection can be performed easily. As a result, the accuracy of quantitative analysis can be improved.

(Second Embodiment)
The configuration of the ultrasonic diagnostic apparatus according to the second embodiment is the same as that of the ultrasonic diagnostic apparatus 10 shown in FIG.

  The second embodiment is an example of supporting a diagnosis work by setting an optimal analysis condition for a desired local region of an ultrasonic image in quantitative analysis using a contrast agent.

  In general, in order to perform an analysis on a diagnostic image, it is desirable to acquire signals under the most recent conditions in all regions. However, in reality, for example, it is known that some parameters shown in the following (1) to (4) differ locally due to physical influence.

  (1) The transmission sound pressure is maximum near the focus point and decreases as the distance from the focus point increases.

  (2) When the focus point is passed, the transmission sound field becomes lower as it goes deeper due to the influence of biological attenuation.

  (3) As shown in FIG. 5, in the electronic scanning, the transmission sound pressure to the end portion is lower than the transmission sound pressure to the central portion because the deflection angle is large.

  (4) As shown in FIG. 6, especially in the sector (fan-shaped) scan, the interval between adjacent scanning lines becomes wider as the depth increases.

  It has been clarified that these phenomena can be relatively reduced by using a method for generating a relatively uniform sound field described in Japanese Patent Application No. 2000-150396, for example. However, the generation of a strictly uniform sound field is essentially impossible, and when the sound pressure of the sound field is made uniform, the transmission power is averaged. The image quality cannot be obtained.

  In the ultrasonic diagnostic apparatus 10 according to the present embodiment, for the purpose of further expanding the degree of freedom of the acquired image, the following ultrasonic transmission / reception conditions different from the conventional ones are set in the designated area.

  (1) The transmission focus point is set in the designated area.

  (2) The ultrasonic transmission drive sound pressure value is reset so as to be approximately constant in any designated region. Specifically, as shown in FIG. 7, correction values are prepared in advance based on a prior sound field pattern.

(3) The scanning line interval is reset so as to be substantially constant even in the designated area. Specifically, when the angle of the adjacent scanning lines is θ, the scanning line interval w at the depth x is
w = x * sinθ
Therefore, θ may be adjusted at each depth x so that w is constant.

  The conditions (1) to (3) are referred to as “optimal analysis conditions”.

  The region for setting the optimum analysis condition is instructed from the input unit 13 by the operator. As a specific operation of the operator, a cursor displayed on the display unit 28 by operating the input unit 13 (a pointing device capable of pointing a part on the diagnostic image, such as a mouse or a trackball). Moves, and a desired area in the ultrasonic image is determined by pressing a button.

  Further, as shown in FIG. 8, the coordinates are detected by the operator pointing directly at a part of the image using a position detection device provided on the screen of the display unit 28. Also good.

  Further, the configuration may be such that an operator's voice is recognized and one area of the image is detected by a microphone provided in the input unit 13 and a voice recognition program provided in the controller 32. As an example, when an operator utters a word such as “upper, middle, end, lower, deep, right, left”, the active part of the nine divided areas shown in FIG. 7 moves. The structure etc. to perform are considered.

  When the position information instructed by the operator is sent to the controller 32 in this way, the controller 32 calls a transmission / reception condition parameter that satisfies the “optimal analysis condition” from the storage medium 30 for the coordinates, Instructs each circuit to change the setting.

  The graphic circuit 33 generates a marker for informing the operator of a point or area on the screen designated by the operator, and displays the marker on the image. Alternatively, it is more useful for the purpose of diagnostic analysis that this marker indicates a region allowed as “optimal analysis condition”.

  By the way, when the above method is executed, good image acquisition is possible in the region where the optimum analysis condition is set, but in other regions, the image quality may be lower than in the conventional case. However, the purpose of this technique is to realize a technique for optimizing the designated area even if other parts are sacrificed, and to increase the degree of freedom of the acquired image. For this reason, it is preferable to provide means for notifying the operator that the current photographing has been changed to the “optimal analysis condition” when the method is being executed. Specifically, the optimum region is clearly indicated by the marker described above, and this mode is being executed by displaying a configuration in which the inside of the marker region and the outside of the marker region are distinguished from each other, or by displaying characters and icons on the screen. A configuration for notifying that this is possible is conceivable.

  According to the support function for reliably acquiring data necessary for such a diagnosis / analysis protocol, transmission / reception conditions optimum for quantitative analysis are set for a local region of interest designated by the operator. Therefore, the operator can easily create a condition capable of quantitative analysis for the region of interest during the examination. In addition, since the above operation can be immediately performed on another region, an image suitable for quantitative analysis can be acquired in various regions, that is, the entire region even in a transient contrast echo.

(Third embodiment)
The third embodiment is an example of supporting a diagnosis / measurement operation by displaying an ultrasonic image in a predetermined form when analyzing a time change of a recorded image.

  In general, there are several attempts to make a diagnosis by analyzing temporal changes in recorded images. A typical example is a contrast echo for administering a contrast medium. In particular, about 1 minute immediately after administration of the contrast agent is called the early phase, and the benign / malignant determination of the tumor, the ischemic site, based on the speed or brightness of the contrast agent flowing into various parts of the diagnostic surface and its inflow pattern Can be diagnosed. Furthermore, it is expected that more detailed information on the degree of lesion progression can be obtained by quantifying these as numerical values.

  As described in the first embodiment, when performing quantitative analysis, it is necessary to keep the same cross section and observe. Normally, the most important time in the early phase is often about 10 to 20 seconds immediately after the inflow of the contrast medium. In such a case, the operator instructs the subject to stop breathing, thereby reducing the displacement of the cross section due to the influence of breathing.

  However, even in the above-described case, it is essential to be affected by a heartbeat that is repeated approximately every one second. When the time-dependent change (TIC) of the luminance histogram at the same place is measured, there are many cases in which extreme values are periodically obtained as shown in FIG. This is because both the movement of the organ itself due to the heartbeat and the synchronization of the ejection of blood with the contraction and expansion of the heart are affected.

  Further, in order to reduce the variation in the measurement values of the quantitative analysis, a smooth curve is often obtained by performing an average process between the measurement values from the viewpoint of analysis processing. However, even in this case, if the original image itself has a lot of fluctuation, it will obviously increase the error.

Therefore, according to the present embodiment, when quantitative analysis is performed, a plurality of image groups for each heartbeat are arranged and displayed in the same heartbeat time phase. Further, the quantitative analysis is performed in synchronization with a certain heartbeat time phase. Furthermore, it is possible to display a plurality of diagnostic images in a two-dimensional matrix in the direction in which they are arranged with time and the direction in which the time phases correspond to each other.

  Hereinafter, the operation of the ultrasonic diagnostic apparatus according to the third embodiment will be described with reference to FIG.

  The analysis unit 42 includes a software program controlled by the controller 32 and a storage medium. An electrocardiogram signal from the heartbeat detection unit 29 and image information of the image memory circuit 26 or at least address information corresponding to the image are sent to the analysis unit 42.

  As shown in FIG. 11, the analysis unit 42 rearranges the image data recorded as a one-dimensional array over time from the electrocardiogram information to the two-dimensional array information for each heartbeat. As a result, the first direction (horizontal direction in FIG. 11) of the two-dimensional array represents the time variation of one heartbeat period, and the second direction (vertical direction in FIG. 11) represents the time variation in the same heartbeat time phase. Will be expressed.

  Various analysis programs are incorporated in the analysis unit 42, and when executing a program for analyzing the temporal change of the diagnostic image in the analysis unit 42, the operator uses the two-dimensionally arranged image information. The image group can be selected in any of the first and second arbitrary directions. For example, as shown in FIG. 12, an image sequence in the second direction can be selected, and a change in luminance histogram with time (TIC) based on the ultrasonic image of the sequence can be acquired.

  Note that the time-dependent change (TIC) in the luminance histogram of FIG. 12 does not have the periodic extreme values seen in FIG. This is because the TIC is obtained from images of the same cardiac time phase by the support function according to the present embodiment.

The time phase to be analyzed can be arbitrarily set by the operator, and a plurality of luminance change curves can be calculated in all time phases. Further, an arithmetic program for performing arithmetic processing such as addition and subtraction between arbitrary curves for obtaining an average curve for the plurality of curves and an interface thereof are also provided. Further, in the analysis, based on a plurality of analysis curves obtained based on the plurality of images of the plurality of the same heartbeat time phases, at least one of luminance average calculation, luminance maximum value calculation, and luminance minimum value calculation is performed. You may make it calculate. Furthermore, a plurality of analysis curves obtained based on a plurality of images of the same heartbeat time phase may be superimposed and displayed.

  According to the support function for reliably acquiring data necessary for such a diagnosis / analysis protocol, images of the same time phase can be extracted during quantitative analysis, and the measurement target organ can also be measured at the same time phase. it can. As a result, a more stable measurement result can be obtained.

  The present invention is not limited to the above-described embodiment, and various modifications can be made without departing from the spirit of the invention in the implementation stage. Further, the embodiments may be combined as appropriate as possible, and in that case, the combined effect can be obtained. Furthermore, the above embodiments include inventions at various stages, and various inventions can be extracted by appropriately combining a plurality of disclosed constituent elements. For example, even if some constituent requirements are deleted from all the constituent requirements shown in the embodiment, the problem described in the column of the problem to be solved by the invention can be solved, and the effect described in the column of the effect of the invention If at least one of the following is obtained, a configuration in which this configuration requirement is deleted can be extracted as an invention.

  DESCRIPTION OF SYMBOLS 10 ... Ultrasonic diagnostic apparatus, 11 ... Apparatus main body, 12 ... Ultrasonic probe, 13 ... Input part, 14 ... ECG (electrocardiogram apparatus), 21 ... Ultrasonic transmission unit, 22 ... Ultrasonic reception unit, 23 ... B-mode process Circuit, 24 ... Doppler processing circuit, 25 ... Image processing circuit, 26 ... Image memory circuit, 28 ... Display unit, 29 ... Heart rate detection unit, 30 ... Storage medium, 31 ... Network circuit, 32 ... Controller, 33 ... Graphic circuit, 42 ... Analysis unit, 51 ... Organ boundary, 52 ... Characteristic part in organ, 53 ... Main blood vessel

Claims (7)

A plurality of diagnostic images collected over a plurality of periods based on a biological signal of a subject are arranged over time, and a quantitative analysis on a time phase corresponding to each period is performed using the plurality of arranged images. An analysis means for executing an analysis process for executing an analysis curve for a plurality of time phases;
Display means for superimposing and displaying analysis curves corresponding to a plurality of time phases acquired by the analysis processing;
An ultrasonic diagnostic apparatus comprising:   The ultrasonic diagnostic apparatus according to claim 1, wherein the display unit simultaneously displays the plurality of arranged diagnostic images in correspondence with time phases between the plurality of periods.   The ultrasonic diagnostic apparatus according to claim 1, wherein the display unit displays a plurality of diagnostic images in a two-dimensional matrix form in a direction in which the temporal arrangement is performed and a direction in which the time phases are associated with each other. The biological signal is an ECG signal;
The time phase is a heartbeat time phase;
The ultrasonic diagnostic apparatus according to claim 1 or 2.   The ultrasonic diagnostic apparatus according to claim 4, wherein the analysis unit measures a time change curve of a luminance histogram.   The analyzing means calculates at least one of a luminance average calculation, a luminance maximum value calculation, and a luminance minimum value calculation based on a plurality of analysis curves obtained based on a plurality of images of the plurality of the same heartbeat time phases. The ultrasonic diagnostic apparatus according to claim 5, having a function of   The ultrasonic diagnostic apparatus according to claim 1, wherein the analysis unit arranges address information for each of the plurality of images over time.

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