JP5481407B2 - Ultrasonic diagnostic apparatus and ultrasonic signal processing apparatus - Google Patents

Description

  In order to distinguish between structures such as tumors in vivo, in particular hepatic hemangioma and liver cancer, the present invention applies a mechanical action locally in addition to ultrasonic irradiation for image construction, and its motion The present invention relates to a technique for facilitating confirmation of an image, an ultrasonic diagnostic apparatus and the like that can realize quantitative evaluation of the motion using an M-mode image.

  An ultrasonic diagnostic apparatus is a diagnostic apparatus that displays an image of in-vivo information, and is cheaper, less exposed, and non-invasively observing in real time compared to other diagnostic imaging apparatuses such as X-rays and CT diagnostic apparatuses. It is used as a useful device. The application range of the ultrasonic diagnostic apparatus is wide, and it is applied from the circulatory organ such as the heart to the abdomen such as the liver and kidney, peripheral blood vessels, obstetrics and gynecology, and cerebral blood vessels.

  The ultrasound diagnosis as an example of the abdominal region is briefly described as follows. In other words, if a tumor is found during the examination, it must be distinguished whether it is malignant or benign, and it is necessary to determine what kind of treatment should be performed if it is a follow-up or treatment. Taking the liver as an example, hepatic hemangioma is a benign liver tumor, but it may not always be easy to distinguish it from malignant liver cancer using a normal ultrasound diagnostic apparatus that does not use a contrast agent. On the other hand, there are contrast-enhanced CT and contrast-enhanced ultrasound examinations, both of which are highly invasive, and in addition, the former suffers from the problem of X-ray exposure, and the latter is complicated in procedure and requires more personnel for the examination. Will have to. Although there is an inspection using MRI, not all facilities are owned, and there are problems such as a long waiting time for the inspection, and it is difficult to deal with early inspection. In view of such a background, it is desirable for doctors and patients that a tumor can be differentiated by a normal ultrasonic diagnostic test without using a contrast medium.

  On the other hand, according to recent clinical studies, it is reported that hepatic hemangioma is often observed in the low echo part of the B-mode of the ultrasonic diagnostic apparatus liver due to its internal structure (for example, non-patent literature). 1). Here, “fluctuation” refers to a phenomenon in which B-mode luminance texture information, that is, speckle pattern, gradually changes in a few seconds. As this mechanism, hemangioma is considered to be a very slow blood flow or movement such as fluctuation of endothelial cells because hemangiomas are vascular endothelial cell proliferation and blood fullness. Yes. In any case, by confirming the phenomenon caused by the movement of the hemangioma, the possibility of discriminating hepatic hemangioma from liver cancer is shown even with a normal ultrasonic diagnostic apparatus.

  In clinical examination, it is necessary to record diagnostic information as a history. At present, in order to record the above-described phenomenon, means using a moving image can be considered, but here some new problems can be presented.

  First, it is necessary to use a video tape or the like for moving images, which is complicated when reconfirmed. Although there is a means called an electronic moving image file, there is a tendency that the recording capacity tends to increase as compared with a still image, and there still arises a problem that it cannot be attached to a medical chart.

  Secondly, the above phenomenon is a gradual change over several seconds, and there is a risk that even if it is a moving image, the phenomenon may be overlooked unless it is watched carefully. Therefore, an expression method that significantly suggests this phenomenon is desired. In addition, it is a general matter when diagnosing from an image, but it is desirable that an objective and quantitative record can be kept.

(The 76th Annual Meeting of the Japanese Society of Ultrasonic Medicine 2003.05.08-11, 76-C108 “Examination of fluttering signal in hepatic hemangioma”, Tokyo Medical University, Arashima et al.)

  The present invention has been made in view of the above circumstances, and an ultrasonic diagnostic apparatus or ultrasonic signal having a unique function effective for diagnosing a structure such as a tumor in a living body, for example, a structure of a hepatic hemangioma, etc. An object is to provide a processing apparatus.

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

An ultrasonic diagnostic apparatus according to an embodiment transmits a first ultrasonic wave for causing a mechanical action to a predetermined structure of a subject, and then transmits a second ultrasonic wave for imaging the predetermined structure. A signal acquisition unit that acquires an echo signal obtained by transmitting a sound wave to the predetermined structure, and a time-series comparison of the echo signals obtained from the predetermined structure, detects a position change of the predetermined structure. And a calculation means for obtaining an evaluation index for quantitatively evaluating the mechanical action generated on the predetermined structure, and an evaluation obtained by imaging the distribution of the evaluation index related to the predetermined structure based on the evaluation index Image generating means for generating an image .
An ultrasonic diagnostic apparatus according to another embodiment transmits a first ultrasonic wave for moving a predetermined structure of a subject, and then performs a second operation for imaging the movement of the predetermined structure in a B mode. A signal acquisition means for acquiring an echo signal obtained by transmitting the ultrasonic wave of the predetermined structure to the predetermined structure, an image generation means for generating an M-mode image relating to the motion of the predetermined structure based on the echo signal, And a calculation means for calculating an evaluation index for quantitatively evaluating the motion of the predetermined structure based on the M-mode image.
An ultrasonic signal processing apparatus according to an embodiment transmits a first ultrasonic wave for generating a mechanical action to a predetermined structure of a subject, and then performs a second operation for imaging the predetermined structure. A storage means for storing an echo signal obtained by transmitting an ultrasonic wave to the predetermined structure and a position change of the predetermined structure are detected based on a time-series comparison of the echo signals obtained from the predetermined structure. And a calculation means for obtaining an evaluation index for quantitatively evaluating the mechanical action generated on the predetermined structure, and an evaluation obtained by imaging the distribution of the evaluation index related to the predetermined structure based on the evaluation index Image generating means for generating an image.
An ultrasonic signal processing apparatus according to another embodiment transmits a first ultrasonic wave for moving a predetermined structure of a subject, and then images the movement of the predetermined structure in a B mode. Storage means for storing an echo signal obtained by transmitting two ultrasonic waves to the predetermined structure, image generation means for generating an M-mode image relating to the motion of the predetermined structure based on the echo signal, and And a calculation means for calculating an evaluation index for quantitatively evaluating the motion of the predetermined structure based on the M-mode image.

  As described above, according to the present invention, it is possible to realize an ultrasonic diagnostic apparatus or an ultrasonic signal processing apparatus having a unique function effective for diagnosing a structure such as a tumor in a living body, for example, a structure of a hepatic hemangioma. it can.

FIG. 1 is a block diagram of an ultrasonic diagnostic apparatus 10 according to the embodiment. FIG. 2 is a diagram illustrating an example of a scanning line L and a gate G that are displayed in a pseudo manner while being superimposed on an ultrasonic image. FIG. 3 is a diagram illustrating an example of a GUI for manually setting transmission parameters for the second type of ultrasonic transmission. FIG. 4 is a diagram showing an example of a coordinate system defined on the M-mode image used in the quantitative evaluation. FIG. 5 is a diagram for explaining the setting operation of the target time region in this quantitative evaluation. FIG. 6 is a diagram for explaining the setting operation of the target time region in this quantitative evaluation. FIG. 7 is a diagram for explaining the setting operation of the target time region in this quantitative evaluation. FIG. 8 is a diagram for explaining the setting operation of the target time region in this quantitative evaluation. FIG. 9 is a diagram showing an example of a display suitable for presenting an evaluation index. FIG. 10 is a diagram showing another example of a display suitable for presenting an evaluation index. FIG. 11 is a diagram showing another example of a display suitable for presenting an evaluation index. FIG. 12 is a diagram showing another example of a display suitable for presenting an evaluation index. FIG. 13 is a flowchart showing the flow of each process executed in an imaging operation including an ultrasonic scan and the like for generating a hepatic blood vessel type motion.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary.

  FIG. 1 is a block diagram of an ultrasonic diagnostic apparatus 10 according to the present embodiment. The ultrasonic diagnostic apparatus 10 is created by an ultrasonic probe 12, an apparatus main body 11, an apparatus main body 11, and an external input device 13 and an apparatus main body 11 that are connected to the apparatus main body 11 and incorporate various instructions, commands, and information from the operator into the apparatus main body 11. And a monitor 14 which is an external display device for displaying the displayed image. The input device 13 is provided with a trackball 13a, a switch 13b, and the like for setting a region of interest (ROI), a time region described later, and the like.

  The ultrasonic probe 12 has a piezoelectric vibrator as an acoustic / electric reversible conversion element such as a piezoelectric ceramic. The plurality of piezoelectric vibrators are arranged in parallel and are provided at the tip of the probe 12.

  The apparatus main body 11 is connected to other units, the internal storage device 26 and the storage unit 30 via a bus, with a control processor (CPU) 25 serving as a control center for the entire system. The storage unit 30 includes an image memory 27, a software storage unit 28, an interface unit 29, and the like. An ultrasonic transmission / reception unit 21 is connected to the probe 12. The ultrasonic transmission / reception unit 21 reads the transmission / reception conditions stored in the internal storage device 26 by the control processor 25 and generates pulses according to the transmission / reception conditions. In the ultrasonic transmission / reception unit 21, the delay time necessary for focusing the ultrasonic wave into a beam and determining the transmission directivity is given to each rate pulse, and the voltage pulse is sent to the probe 12 for each channel at the timing of receiving the rate pulse. Apply. Thereby, an ultrasonic beam is transmitted to the subject.

  Here, unlike the ultrasonic transmission for normal image generation, this ultrasonic diagnostic apparatus emphasizes changes in structures such as tumors (positional changes, blood flow, and other structural movements). Executes ultrasonic transmission. In order to add mechanical action such as changing the transmission sound pressure or frequency periodically or irregularly, mode selection, ROI setting, time domain setting, transmission input from the user input device 13 or other interface unit 29 Based on the start / end and the like, the transmission / reception conditions and the device control program stored in the internal storage device 26 are read, and the control processor 25 controls the transmission / reception unit 21.

  On the other hand, the ultrasonic beam irradiated into the subject for generating a normal image is reflected by a discontinuous surface of the acoustic impedance in the subject, and the reflected wave is received by the probe 12. The echo signal output from the probe 12 for each channel is taken into the transmission / reception unit 21. The echo signal is amplified for each channel in the transmission / reception unit 21, given a delay time necessary for determining the reception directivity, and added. By this addition, the reflection component from the direction corresponding to the reception directivity is emphasized. The overall directivity of ultrasonic transmission / reception is determined by the transmission directivity and the reception directivity. This directivity is called a scanning line.

  The echo signal output from the transmission / reception unit 21 is sent to the B-mode processing unit 22 and the Doppler processing unit 23. Although not shown, the B mode processing unit 22 includes a logarithmic converter, an envelope detection circuit, and an analog / digital converter (A / D). The logarithmic converter logarithmically converts the echo signal. The envelope detection circuit detects the envelope of the output signal from the logarithmic converter. This detection signal is digitized via an analog-digital converter and output as detection data. The output detection data is calculated into spatial distribution information such as frame correlation and coordinate conversion by the image generation circuit 24 at the subsequent stage. The image generation circuit 24 is connected to the image memory 27 and is provided for storing data handled by the image generation circuit 24.

  The Doppler processing unit 23 extracts the blood flow component by frequency analysis using the analysis result and a filter, and obtains blood flow information such as average velocity, variance, power, etc. at multiple points. The obtained blood flow information is sent to the image generation circuit 24 to create an average velocity image, a dispersion image, a power image, and a combination image thereof. The created image information is sent to the monitor 14 and displayed in color.

  Each calculation process for quantitative evaluation of the movement of the hepatic blood vessel type is based on the data stored in the image memory 27, and using a program read from the software storage unit 28, the host CPU which is the control processor 25 Alternatively, it is processed by software in the local CPU. Designation of the ROI range for calculation, selection and start of the evaluation method, etc. are input by the user through the input device 13 and other interface unit 29 and processed by the control processor 25. The calculated evaluation result is stored again in the image memory 27 via the bus and sent to the image generation circuit 24. In the image generation circuit 24, the calculation result is colored corresponding to the graph or map, and the target image is combined. The finally created image is sent to the monitor 14 and displayed.

  The input device 13 or other interface unit 29 is prepared in various ways according to the purpose, such as a measurement start switch among a mode transition switch, an image quality adjustment switch, and an image storage switch. A selection, start, and end switch (SW) necessary for performing ultrasonic irradiation for emphasizing the “fluctuation phenomenon” caused, and a measurement start SW for quantification are also prepared.

(Ultrasonic transmission function for generating motion of structures such as in vivo tumors)
Next, an ultrasonic transmission function for generating a motion of a structure such as a tumor in the body of the ultrasonic diagnostic apparatus 10 will be described. This function transmits ultrasonic waves based on a predetermined control to a structure such as a tumor in a living body, and dynamically moves the structure, so that luminance texture information (speckle pattern) in an ultrasonic image can be obtained. It actively generates (more emphasizes) fluctuation phenomena. Hereinafter, in order to make the explanation more specific, a case where the target in-vivo structure is a hepatic blood vessel type is taken as an example. In addition, ultrasonic transmission for imaging is referred to as “first type ultrasonic transmission”, and ultrasonic transmission for generating displacement in a structure in a hepatic blood vessel type is referred to as “second type ultrasonic transmission”. I will decide.

  The second type of ultrasonic transmission is performed according to two typical patterns. A 1st pattern is a transmission pattern which transmits the ultrasonic wave by a comparatively strong mechanical index (Mechanical Index) to a target intermittently (intermittently). A 2nd pattern is a transmission pattern which transmits the ultrasonic wave which changed the mechanical parameter | index periodically to the target. Here, the mechanical index is controlled by the transmission sound pressure and the transmission frequency.

  Note that the second type of ultrasonic transmission pattern is not limited to the above two. For example, the combination of the first pattern and the second pattern, or the structure in the hepatic blood vessel type in other ultrasonic images. Any transmission pattern may be used as long as the displacement of the object is positively generated. In the present embodiment, the first or second pattern is employed for the sake of specific description.

  The sound pressure, frequency, wave number, transmission interval, sound pressure change period, and the like of the transmission ultrasonic wave according to each pattern are registered in advance by a plurality of combinations (transmission parameter patterns) of various parameters. When performing an imaging sequence including the second type of ultrasonic transmission, the operator selects and sets a desired one from a plurality of transmission parameter patterns registered in advance and stored in the internal storage device 26. Thus, the second type of ultrasonic transmission according to the pattern can be executed. If necessary, it is also possible to manually set desired values for each parameter on a setting screen as shown in FIG. 3, for example. The transmission parameter pattern set manually as described above is automatically registered in the internal storage device 26.

  In addition, when performing ultrasonic transmission according to the second pattern, it is preferable that the period is automatically optimized based on an evaluation index or the like described later so that the fluctuation is most emphasized. This optimization can be realized by controlling the period based on, for example, the ratio of the luminance change on the image. In addition, the period of the second pattern ranges from a period of several tens of seconds or several seconds to a range of several hundreds of Msec.

  The second type of ultrasonic transmission is performed with the target tumor site as a focus. The setting of the focal position is executed by the following procedure, for example.

  That is, first, the operator performs an imaging sequence start operation including second ultrasonic transmission that emphasizes the “fluctuation phenomenon” separately from the visualization.

  Next, as shown in FIG. 2, the operator displays an ultrasonic image depicting a region including the tumor site on the monitor 14, and the scanning line L and the gate G (transmission) pseudo-displayed on the screen of the monitor 14. The focal point of the ultrasonic wave) is moved to the target by the trackball 13a or the like and set. In addition, after setting, the width of the gate G is changed by an operation from the switch 13b or the trackball 13a so that the fluctuation in the target tumor is not obscured by the pseudo-displayed scanning line or gate. Move the gate position along.

  For the target (tumor site) set in this way, the second type of ultrasonic transmission is executed with a predetermined operation as a trigger. The transmission pattern can be switched to another pattern at an arbitrary timing by a predetermined operation.

  In the second type of ultrasonic transmission, regions other than the tumor site may not contribute much to the diagnosis. Therefore, it is not always necessary to perform the second type of ultrasonic transmission for the region. For example, a configuration for executing ultrasonic transmission for configuring the background B mode with a predetermined sound pressure, or an ultrasonic transmission. The configuration may not be executed. In particular, when the ultrasonic transmission conditions and the execution / non-execution of transmission are distinguished between the area where the second type of ultrasonic transmission is executed and the other area (background area), the transmission conditions for the background are set. The configuration may include a dedicated I / F for determining.

  The motion of the tumor site generated by the second type of ultrasonic transmission is visualized by an echo signal obtained by the first type of ultrasonic transmission performed thereafter. The first type of ultrasonic transmission for imaging the motion of the tumor site is executed according to transmission conditions according to normal imaging. Based on the echo signal obtained by the first type of ultrasonic transmission, for example, a plurality of B-mode images are generated and continuously displayed, so that the speckle pattern of each B-mode image gradually indicates the movement of the tumor site. It can be observed as a phenomenon that changes to (ie, “fluctuation phenomenon”).

Note that the observation of the hepatic blood vessel type movement may use an M-mode image. When using an M-mode image, it is preferable that the M-mode image is enlarged and displayed corresponding to the size of the area of the gate G shown in FIG. In the case of observing, the configuration may be such that the second type of ultrasonic transmission is executed only on the scanning line that targets the tumor site. In such a configuration, when the second type of ultrasonic transmission is intermittently executed (that is, executed according to the first pattern), the second type of ultrasonic transmission is arbitrarily performed by manual operation in addition to automatic control by the apparatus. It may be turned ON / OFF at the timing.

(Quantitative evaluation function of hepatic blood vessel type movement)
Next, the quantitative evaluation function of hepatic blood vessel type movement possessed by the ultrasonic diagnostic apparatus 10 will be described. Quantitative evaluation by this function is executed by calculating any of the evaluation indices described later using an M-mode still image and displaying it in a predetermined form.

  FIG. 4 is a diagram showing an example of a coordinate system defined on the M-mode still image used in this quantitative evaluation. In the figure, the vertical coordinate n (0 ≦ n ≦ N−1) indicates each position in the gate G, and the horizontal coordinate m (0 ≦ m ≦ M−1) indicates each time. When executing this quantitative evaluation, first, a time region to be evaluated is set in the coordinate system on the M-mode still image shown in FIG.

  That is, when a predetermined operation for starting quantitative evaluation is executed by the operator, a start point straight line Ts as shown in FIG. 5 is displayed perpendicularly to the time axis on the M-mode image. The start point straight line Ts is for designating the start point time of the evaluation range. On the M-mode image, the operator confirms the time region in which the tumor margin or surrounding organ (the liver in this case) is stationary, and sets the start point straight line Ts at the start time of the time region to an external device such as a trackball. It is moved by the input key, and a predetermined operation for setting the start point straight line Ts at the moved position is executed.

  When the start point straight line Ts corresponding to the start point time is set, the end point straight line Te for continuously specifying the end point time of the evaluation range appears as shown in FIG. The operator performs the same operation, and sets the start point straight line Ts at the end point time of the time region where the tumor margin or the like is stationary as shown in FIG.

  When the time region to be evaluated is set, the following quantitative evaluation is executed for the region.

  In general, the vertical axis of the M mode indicates the position on the M mode sample line set in the B mode, and the horizontal axis indicates the elapsed time for observation. Now, the sample point position n on the vertical axis indicating the position (0 ≦ n ≦ N−1) and the time domain sample point position m (0 ≦ M ≦ M−1) designated for evaluation on the horizontal axis indicating the elapsed time. The brightness or signal value at) is fm, n. An evaluation index is calculated using the signal values fm, n, and the movement of the hepatic blood vessel type is quantitatively evaluated.

As specific evaluation indexes, for example, the following can be adopted.

  The above (1) and (2) are evaluation indexes indicating the amount of change in luminance or signal intensity in the time axis direction at the position n (0 ≦ n ≦ N−1) on the vertical axis.

In addition, among m (0 ≦ m ≦ M−1), the evaluation indexes (3) and (4) based on the luminance or signal intensity f _{mo, n} at a specific position M0 may be employed.

In addition, as an evaluation index indicating the amount of change in luminance or signal intensity in the time axis direction at the position n (0 ≦ n ≦ N−1) on the vertical axis, analysis is performed using the generally known FFT shown below, The result is displayed in a graph or the like described later. Or the thing extracted by the band pass filter (BPF) for the speed component of the "fluctuation phenomenon" estimated to be based on the movement of blood flow is displayed on a graph or the like to be described later.

  Here, H (k) is a bandpass filter coefficient, and a band that the user wants to extract can be designated. In addition, from the viewpoint of improving operability, a configuration may be adopted in which bandpass filter coefficients registered in advance are selected and set by a predetermined operation.

Also, a function of luminance or signal intensity in the time axis direction at a first position s (0 ≦ s ≦ N−1) fixed as a reference at an arbitrary position on the vertical axis, and an arbitrary position on the vertical axis. The following expression is evaluated as an evaluation expression indicating the similarity to the function of the luminance or signal intensity in the time axis direction at the second position r (0 ≦ r ≦ N−1) that moves.

Here, F _{m, t} is obtained by the expression (a) normalized by the average value in the time direction on the axis of the vertical axis position t, or normalized by the maximum value f _{MAX, t} in the time direction. Which is obtained by the formula (b). (F _{MAX, t} = (f _{0, t} , f _{1, t} , f _{2, t} , f _{3, t} , ..., f _{m-1, t} ), max () is the maximum in () (This function selects a value.)

  The first position is set to a desired position by, for example, the following operation. That is, after setting the time region to be evaluated, a pointer P for setting the first position as shown in FIG. 8 and a straight line parallel to the time axis are displayed. The operator moves the appearing straight line or the pointer P to a desired position by an external input device such as the trackball 13a, and sets the first position by performing a predetermined operation. After the first position setting, the evaluation index calculation of (6) and (7) above is executed for the time domain to be evaluated, and the result is a predetermined form such as a numerical value, graph, or map as will be described later. Is displayed.

  The calculation formula for each evaluation index is set in advance, and can be switched by pressing an “evaluation selection” switch. In addition, the display may be updated by executing the calculation immediately with the evaluation formula specified almost at the same time as switching, or after pressing the “Update” switch, the calculation formula may be executed. Settings can be made on a preset screen such as a preset.

  The evaluation index calculation for quantitative evaluation described above is positioned as one of the measurement functions of the ultrasonic diagnostic apparatus, and the software storage unit is used via the data bus using information on luminance or signal strength in the designated cine memory. Using the program read from 28, it is processed by software in the host CPU or local CPU which is the control processor 25. Further, range specification for evaluation index calculation, selection and start of an evaluation method, and the like are input by the user through the input device 13 and other interface unit 29 and processed by the control processor 25. Furthermore, the functions used in the evaluation index calculation described later are generally well-known arithmetic functions such as difference, sum of squares, FFT, bandpass filter, integration processing, or a combination thereof, and can be easily realized by software. The circuit may be realized by hardware.

(Evaluation index presentation function)
Each evaluation index calculated in the quantitative evaluation is presented to the observer in the following form, for example.

  FIG. 9 is an example of a display suitable for presenting each evaluation index of (1) to (4), (6), and (7). As shown in the figure, the accumulated square or accumulated absolute value error at each position is associated with a color and displayed as a map at each time.

  FIG. 10 is an example of a display suitable for presenting each evaluation index of (1) to (7). As shown in the figure, the final calculated value of the accumulated square or accumulated absolute value error at each position, or the integrated value of the component extracted by BPF after FFT is displayed on a map (color bar).

  FIG. 11 is an example of a map display suitable for presenting each evaluation index of (1) to (7). As shown in the figure, the distribution of the final calculated value of the accumulated square or accumulated absolute value error at each position, or the frequency distribution of the component extracted by BPF after FFT is displayed in a graph.

  FIG. 12 is an example of a display suitable for presenting the evaluation index (5). As shown in the figure, the frequency analysis result obtained by applying FFT or BPF processing after FFT is displayed in a graph.

  Whether the evaluation index is presented in any of the above-described FIGS. 9 to 12 is determined by the operator selecting a desired form from among combinations of the evaluation indices set in advance.

(Operation)
Next, a series of imaging operations including an ultrasonic scan for generating displacement in a structure in the liver blood vessel type and a quantitative evaluation regarding the displacement of the structure in the liver blood vessel type will be described with reference to the drawings. .

  FIG. 13 is a flowchart showing the flow of each process executed in an imaging operation including an ultrasonic scan and the like for generating a hepatic blood vessel type motion. In the figure, first, an instruction to start an ultrasound image diagnosis sequence for hepatic blood vessel types is executed (step S1), selection of patient ID, desired transmission parameter pattern, evaluation method, evaluation index presentation form, etc., gate position Are set (step S2).

  Next, the second type and the first type of ultrasonic transmission according to the selected transmission parameter pattern are executed (step S3), and based on the echo signal obtained by the first type of ultrasonic transmission, an ultrasonic image ( Here, an M-mode image) is generated and displayed on the monitor 14 in a predetermined form. In addition, the operator temporarily stops breathing by causing the subject to temporarily stop the movement of the organ, and when an image suitable for evaluation can be displayed, the operator presses the freeze switch to appropriately display the ultrasonic image in the image memory 27. Store (step S4).

  Next, the operator reads out each stored ultrasonic image and displays it on the monitor 14, while turning the ultrasonic image displayed by the trackball 13 a etc. An M mode image is selected (step S5).

  Next, a time region to be evaluated is set on the selected M-mode image (step S6), and an evaluation index corresponding to the selected evaluation method is calculated (step S7). The calculated evaluation index is displayed on the monitor 14 in any of the forms described above and presented to the observer (step S8).

  According to the configuration described above, the following effects can be obtained.

  According to the present ultrasonic diagnostic apparatus, the movement of the hepatic blood vessel type can be effectively and actively generated by the second type of ultrasonic transmission. Therefore, by executing the first type of ultrasonic transmission after the second type of ultrasonic transmission, it is possible to observe the movement of the hepatic blood vessel type as a fluctuation phenomenon of the luminance texture information in the ultrasonic image. Information effective for diagnosis can be provided without performing highly invasive tests such as sound waves.

  According to this ultrasonic diagnostic apparatus, the transmission pattern of the second type of ultrasonic transmission, the transmission parameter pattern, the time interval between the second type of ultrasonic transmission and the first type of ultrasonic transmission, etc. are preset. It can be set by selecting from the contents. Accordingly, in ultrasonic diagnosis of hepatic blood vessel types, a quick and simple device operation can be realized, and the mental and physical burden on the operator can be reduced.

  Further, according to the present ultrasonic diagnostic apparatus, it is possible to quantitatively evaluate the fluctuation phenomenon of the ultrasonic image caused by the movement of the hepatic blood vessel type on the basis of various evaluation indexes. It is possible to provide effective and objective information. The quantitative evaluation is displayed in a predetermined form such as a graph or a color bar. Accordingly, the observer can observe the fluctuation phenomenon of the ultrasonic image due to the movement of the hepatic blood vessel type, which is generally not easy to observe, with excellent visibility. In addition, doctors can explain diagnosis results to patients in an easy-to-understand manner by using quantitative evaluations presented by graphs, color bars, etc., and realize diagnosis that respects informed consent Can do.

  Further, according to the present ultrasonic diagnostic apparatus, the fluctuation phenomenon of the ultrasonic image caused by the movement of the hepatic blood vessel type can be stored as quantitative information having a smaller data amount than the ultrasonic moving image. Therefore, it is possible to effectively use hardware resources with limited capacity. Further, since the amount of data is small, it can be attached to an electronic medical record, and the quantitative information can be exchanged by communication.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. For example, the following modifications can be given.

  (1) The evaluation index that can be adopted in the quantitative evaluation of hepatic blood vessel type movement is not limited to the above example, but is a value indicating the amount of fluctuation in the time axis direction in the M mode image, or the time change at different vertical axis positions. Any evaluation index may be used as long as the degree of similarity can be shown.

  (2) The above-described quantitative evaluation process of hepatic blood vessel type movement can also be realized by developing a program for causing a computer to execute each process on an image processing apparatus such as a workstation or an ultrasonic diagnostic apparatus. is there. It can also be realized by storing the program in a removable storage medium, reading the storage medium from the external storage device of the interface unit 29 into the apparatus, and developing it.

  (3) In the above embodiment, in order to make the explanation easy to understand, the second type of ultrasonic transmission is only intended to dynamically affect the hepatic blood vessel type, and is not used for imaging. did. However, the present invention is not limited to this, and an echo signal resulting from the second type of ultrasonic transmission may be used for imaging as necessary.

  In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

  As described above, according to the present invention, an ultrasonic diagnostic apparatus or an ultrasonic signal processing apparatus having a unique function effective for diagnosing the structure of hepatic hemangioma can be realized.

DESCRIPTION OF SYMBOLS 10 ... Ultrasonic diagnostic apparatus, 11 ... Apparatus main body, 12 ... Ultrasonic probe, 13 ... Input device, 13
a ... trackball, 13b ... switch, 14 ... monitor, 21 ... transmission / reception unit, 22
... B mode processing unit, 23 ... Doppler processing unit, 25 ... Image generation circuit, 26 ... Internal storage device, 27 ... Image memory, 25 ... Control processor, 28 ... Software storage unit, 29
... interface part, 30 ... storage part,

Claims (10)

Obtained by transmitting a first ultrasonic wave for generating a mechanical action to a predetermined structure of a subject and then transmitting a second ultrasonic wave for imaging the predetermined structure to the predetermined structure. Signal acquisition means for acquiring an echo signal to be transmitted;
An evaluation index for detecting a change in position of the predetermined structure based on a time-series comparison of echo signals obtained from the predetermined structure and quantitatively evaluating a mechanical action generated on the predetermined structure. A calculation means for obtaining
An image generating means for generating an evaluation image obtained by imaging the distribution of the evaluation index related to the predetermined structure based on the evaluation index;
An ultrasonic diagnostic apparatus comprising: After transmitting the first ultrasonic wave for moving the predetermined structure of the subject, the second ultrasonic wave for imaging the movement of the predetermined structure by the B mode is transmitted to the predetermined structure. Signal acquisition means for acquiring the obtained echo signal;
Image generating means for generating an M-mode image related to the motion of the predetermined structure based on the echo signal;
Calculation means for calculating an evaluation index for quantitatively evaluating the motion of the predetermined structure based on the M-mode image;
An ultrasonic diagnostic apparatus comprising:   The ultrasonic diagnostic apparatus according to claim 1, wherein the evaluation index is a difference value of a signal regarding a predetermined period at at least one point of the predetermined structure.   The ultrasonic diagnostic apparatus according to claim 1, wherein the evaluation index is an integral value of a signal change amount related to a predetermined period at at least one point of the predetermined structure.   The evaluation index includes a signal change amount related to a predetermined period of the first position consisting of at least one point of the predetermined structure and a predetermined value of a second position consisting of at least one point of the predetermined structure different from the first position. The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic diagnostic apparatus is a value indicating a similarity with a signal change amount related to a period.   The ultrasonic diagnostic apparatus according to claim 1, wherein the evaluation index is a frequency analysis value of a signal related to a predetermined period at at least one point of the predetermined structure. 7. The display apparatus according to claim 1, further comprising a display unit configured to display a fluctuation phenomenon based on a motion of the predetermined structure by displaying the ultrasonic image in time series. The ultrasonic diagnostic apparatus as described . The metrics, a color map or color bars corresponding to the value, graph other any one of claims 1 to 7, wherein the further comprising a display means for displaying by quantitative display form the ultrasonic diagnostic apparatus. Obtained by transmitting a first ultrasonic wave for generating a mechanical action to a predetermined structure of a subject and then transmitting a second ultrasonic wave for imaging the predetermined structure to the predetermined structure. Storage means for storing echo signals to be transmitted;
An evaluation index for detecting a change in position of the predetermined structure based on a time-series comparison of echo signals obtained from the predetermined structure and quantitatively evaluating a mechanical action generated on the predetermined structure. A calculation means for obtaining
An image generating means for generating an evaluation image obtained by imaging the distribution of the evaluation index related to the predetermined structure based on the evaluation index;
An ultrasonic signal processing apparatus comprising: After transmitting the first ultrasonic wave for moving the predetermined structure of the subject, the second ultrasonic wave for imaging the movement of the predetermined structure by the B mode is transmitted to the predetermined structure. Storage means for storing the obtained echo signal;
Image generating means for generating an M-mode image related to the motion of the predetermined structure based on the echo signal;
Calculation means for calculating an evaluation index for quantitatively evaluating the motion of the predetermined structure based on the M-mode image;
An ultrasonic signal processing apparatus comprising:

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