JP2005323657A - Ultrasonic diagnosing apparatus, and image processing device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ultrasonic diagnosing apparatus which effectively extracts diagnosis information at a fine blood vessel divergence level. <P>SOLUTION: This ultrasonic diagnosing apparatus is equipped with an ultrasonic probe 12 which transmits an ultrasonic wave to a subject P, and receives an echo signal from the ultrasonic wave, an image forming section 24f which forms a plurality of sheets of first image data F from the echo signal received by the ultrasonic probe 12, and an image processing circuit 24c. The image processing circuit 24c performs an unnecessary signal filtering process for removing white noises existing on each first image data by using at least two sheets from among a plurality of sheets of the first image data formed by the image forming section 24f, and forms a plurality of sheets of second image data G. At the same time, the image processing circuit 24c performs a maximum value retaining operation for adopting a maximum luminosity value from among spatially corresponding pixels by using at least two sheets from among a plurality of sheets of the second image data, and forms third image data H. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to an ultrasonic diagnostic apparatus and an image processing apparatus that present micro blood flow reflux as diagnostic information in a contrast echo method performed using an ultrasonic contrast agent.

  Ultrasound diagnosis can be obtained by real-time display of heart beats and fetal movements with a simple operation by simply touching the ultrasound probe from the body surface. Compared with diagnostic equipment such as CT and MRI, the scale of the system is small, and the inspection can be easily performed while moving to the bedside.

  Ultrasound diagnostic devices vary depending on the types of functions they have, but small ones that can be carried with one hand have been developed, and the effects of exposure, such as X-rays, have been developed. It can also be used in obstetrics and home medical care.

  In recent years, intravenous administration-type ultrasound contrast agents have been commercialized, and contrast echoes have been performed. This method is intended to evaluate blood flow dynamics by injecting an ultrasound contrast agent from a vein, for example, in an examination of the heart, liver, or the like to enhance the blood flow signal. Many of the contrast agents function by using microbubbles as a reflection source. Due to the sensitive nature of the bubble, the bubble is broken by the mechanical action of the ultrasonic wave at the normal diagnostic level, and as a result, the signal intensity from the scan plane decreases.

  Therefore, in order to observe the dynamic state of reflux in real time, it is necessary to reduce the collapse of bubbles due to scanning, such as by imaging with low sound pressure ultrasonic transmission. However, since imaging with such low sound pressure ultrasonic transmission also reduces the signal / noise ratio (hereinafter referred to as “S / N ratio”), various signal processing methods to compensate for this decrease. Has also been devised.

  In addition, when an ultrasonic contrast agent is used, a very fine blood vessel structure can be imaged as compared with the ultrasonic Doppler method. This level of blood flow information is said to be important information for differential diagnosis of diffuse liver disease or liver cancer, such as blood vessel short circuit and the degree of progression of regenerative nodules.

  By the way, when imaging the fine blood vessel structure, a so-called maximum value holding operation that uses a plurality of ultrasonic tomographic images and adopts the maximum luminance value among spatially corresponding pixels is used as the imaging method. (For example, refer nonpatent literature 1.).

  FIG. 8 is a conceptual diagram for explaining a conventional maximum value holding operation.

That is, as shown in FIG. 8A, even if the signal 400 from the contrast agent displayed in each ultrasonic tomographic image 100 is sparse, a plurality of ultrasonic tomograms are obtained by performing the maximum value holding calculation. The image 100 is superimposed, and the blood vessel structure 500 is displayed on the diagnostic image 200 by the contrast agent signal 400.
The Eye European Symposium on Ultrasound Contrast Imaging to be held on January 23-24, 2003 Rotterdam The Netherlands.

  However, when the maximum value holding calculation is used, it must be performed under low sound pressure transmission in which the S / N ratio is reduced, and as shown in FIG. When the derived white noise 300 is mixed, the ultrasonic tomographic images 100 are superimposed, the white noise 300 accumulates, and the diagnostic image 200 may become unclear.

  The present invention has been made in view of the above circumstances, and an object of the present invention is to provide an ultrasonic diagnostic apparatus and an image diagnostic apparatus that can effectively extract diagnostic information of a fine blood vessel branch level. .

  In order to solve the problems and achieve the object, the ultrasonic diagnostic apparatus and the image diagnostic apparatus of the present invention are configured as follows.

(1) In an ultrasonic diagnostic apparatus for acquiring an ultrasonic diagnostic image by scanning a predetermined portion of a subject to which a contrast agent bubble is administered with an ultrasonic wave, the ultrasonic wave is transmitted to the subject, and the ultrasonic wave An ultrasonic transmission / reception unit that receives an echo signal from the image generation unit, an image generation unit that generates a plurality of original images based on the echo signal received by the ultrasonic transmission / reception unit, and a plurality of sheets generated by the image generation unit An image for generating a plurality of first ultrasonic diagnostic images with reduced noise from the original image and generating a second ultrasonic diagnostic image from the plurality of first ultrasonic diagnostic images by a maximum value holding calculation. And a processing means.

(2) The ultrasonic diagnostic apparatus according to (1), wherein at least two of the plurality of original images are used and a minimum luminance value is adopted from spatially corresponding pixels. The first ultrasonic diagnostic image is generated by executing the minimum value holding calculation.

(3) The ultrasonic diagnostic apparatus according to (1), wherein an average using an average luminance value of spatially corresponding pixels using at least two or more of the plurality of original images The first ultrasonic diagnostic image is generated by executing a value holding calculation.

(4) In an ultrasonic diagnostic apparatus for acquiring an ultrasonic wave by scanning a predetermined part of a subject to which a contrast agent bubble is administered with an ultrasonic wave, the ultrasonic wave is transmitted to the subject, Ultrasonic transmission / reception means for receiving an echo signal, scanning line information generation means for generating a first scanning line signal sequence for a plurality of frames based on the echo signal received by the ultrasonic transmission / reception means, and the scanning line information A plurality of first scanning line signal sequences for a plurality of frames generated by the generation unit, wherein a plurality of first scanning line signal sequences having the same ultrasonic transmission direction are reduced in noise for each transmission direction. A second scanning line signal sequence forming the same frame among a plurality of second scanning line signal sequences generated by the scanning line processing unit. Combine the frame Image processing means for generating a first ultrasonic diagnostic image and generating a second ultrasonic diagnostic image by a maximum value holding calculation from a plurality of first ultrasonic diagnostic images generated for each frame It is characterized by comprising.

(5) The ultrasonic diagnostic apparatus according to (4), wherein at least two of the plurality of first scanning line signal sequences having the same transmission direction of the ultrasonic waves are used, The second scanning line signal sequence is generated by executing a minimum value holding operation that employs a minimum value of spatially corresponding amplitude values.

(6) The ultrasonic diagnostic apparatus according to (4), wherein at least two of the plurality of first scanning line signal sequences having the same ultrasonic transmission direction are used in time or space. The second scanning line signal sequence is generated by executing an average value holding operation that adopts an average value of corresponding amplitude values.

(7) The ultrasonic diagnostic apparatus according to any one of (1) to (6), further including display means for simultaneously displaying the first ultrasonic diagnostic image and the second ultrasonic diagnostic image. It is characterized by that.

(8) Storage means for storing a plurality of original images obtained by scanning a predetermined portion of the subject with ultrasound, and a plurality of first ultrasonic diagnostics in which noise is reduced from the plurality of original images. And an image processing means for generating a second ultrasonic diagnostic image by a maximum value holding calculation from the plurality of first ultrasonic diagnostic images.

(9) The image processing apparatus according to (8), wherein a minimum luminance value is adopted from spatially corresponding pixels by using at least two of the plurality of original images. The first ultrasonic diagnostic image is generated by executing a minimum value holding calculation.

(10) In the image processing apparatus described in (8), an average value that employs an average luminance value of spatially corresponding pixels using at least two or more of the plurality of original images. The first ultrasonic diagnostic image is generated by executing a holding operation.

  According to the present invention, it is possible to effectively extract minute blood vessel branching level diagnostic information.

  The best mode for carrying out the present invention will be described below with reference to the drawings.

  First, a first embodiment of the present invention will be described with reference to FIGS.

  FIG. 1 is a block diagram showing the configuration of the ultrasonic diagnostic apparatus according to the first embodiment of the present invention.

  As shown in FIG. 1, this ultrasonic diagnostic apparatus includes an ultrasonic probe 12 (ultrasonic transmission / reception means), an input device 13, a monitor 14, a transmission / reception unit 21, a B-mode processing unit 22 (scanning line information generation means), a Doppler. A processing unit 23, an image generation circuit 24 (image processing means), a control processor 26, an image memory 27 (storage means), an internal storage device 28, and an interface unit 29 are provided.

  The transmission / reception unit 21 or the like built in the apparatus main body 11 may be configured by hardware such as an integrated circuit, but may be a software program modularized in software. Hereinafter, the function of each component will be described.

  The ultrasonic probe 12 generates ultrasonic waves based on a drive signal from the transmission / reception unit 21, converts a reflected wave from the subject P into an electric signal, and a matching layer provided in the piezoelectric vibrator. And a backing material for preventing the propagation of ultrasonic waves from the piezoelectric vibrator to the rear.

  When an ultrasonic wave is transmitted from the ultrasonic probe 12 to the subject P, the transmitted ultrasonic wave is reflected one after another on the discontinuous surface of the acoustic impedance of the body tissue and is received by the ultrasonic probe 12 as an echo signal. This echo signal depends on the difference in acoustic impedance at the discontinuous surface that is to be reflected. Further, when the transmission ultrasonic wave is reflected by the moving blood or the surface of the heart wall, the echo signal is subjected to frequency shift depending on the velocity component in the ultrasonic transmission direction of the moving body due to the Doppler effect.

  The input device 13 is connected to the device main body 11, and various switches 13 a and buttons for taking various instructions, conditions, region of interest (ROI) setting instructions, various image quality condition setting instructions, etc. from the operator into the device main body 11. 13b, a trackball 13c, a mouse 13d, a keyboard 13e, and the like.

  The monitor 14 displays in vivo morphological information and blood flow information as an image based on a video signal from an image generation circuit 24 (details will be described later).

  The transmission / reception unit 21 includes a trigger generation circuit, a delay circuit, a pulsar circuit, and the like. In the pulsar circuit, rate pulses for forming transmission ultrasonic waves are repeatedly generated at a predetermined frequency fr [Hz] (period: 1 / fr [s]). In the delay circuit, the delay time necessary for converging the ultrasonic wave into a beam shape for each channel and determining the transmission directivity is given to each rate pulse. In the trigger generation circuit, a drive pulse is applied to the ultrasonic probe 12 at a timing based on this rate pulse.

  The transmission / reception unit 21 has a function of instantaneously changing a transmission frequency, a transmission drive voltage, and the like in order to execute a scan sequence (details will be described later) in accordance with an instruction from the control processor 26. The change of the transmission drive voltage is realized by a linear amplifier type transmission circuit capable of instantaneously switching the value or a mechanism for electrically switching a plurality of power supply units.

  The transmission / reception unit 21 includes an amplifier circuit, an A / D converter, an adder, and the like. The amplifier circuit amplifies the echo signal captured from the ultrasonic probe 12 for each channel. In the A / D converter, a delay time necessary for determining reception directivity is given to the amplified echo signal. The adder performs addition processing of echo signals given a delay time. By this addition, the reflection component from the direction corresponding to the reception directivity of the echo signal is emphasized, and a comprehensive beam for ultrasonic transmission / reception is formed by the reception directivity and the transmission directivity.

  The B-mode processing unit 22 receives the echo signal from the transmission / reception unit 21, performs logarithmic amplification, envelope detection processing, and the like, and generates data in which the signal intensity is expressed by brightness. This data is transmitted to the image generation circuit 24 and is displayed on the monitor 14 as a B-mode image representing the intensity of the reflected wave as luminance.

  The Doppler processing unit 23 performs frequency analysis on velocity information from the echo signal received from the transmission / reception unit 21, extracts echo components such as blood flow, tissue, and contrast agent due to the Doppler effect, and blood flow such as average velocity, dispersion, and power. Ask for information on multiple points. The obtained blood flow information is sent to the image generation circuit 24 and displayed on the monitor 14 in color as an average velocity image, a dispersion image, a power image, and a combination image thereof.

  The image generation circuit 24 converts a scanning line signal sequence of ultrasonic scanning into a scanning line signal sequence of a general video format represented by a television or the like, and generates a diagnostic image. The image generation circuit 24 can perform various operations such as image processing according to the present invention. The data before entering the image generation circuit 24 may be referred to as “raw data”.

  Next, details of the image generation circuit 24 will be described.

  FIG. 2 is a block diagram showing a configuration of the image generation circuit 24 according to the embodiment.

  As shown in FIG. 2, the image generation circuit 24 has a signal processing circuit 24a (scanning line processing means), a scan converter 24b, an image processing circuit 24c (image processing means), and an image data buffer 24d (storage means). doing.

  The signal processing circuit 24a performs filtering that determines the image quality at the level of the scanning line signal string of the ultrasonic scan. The output of the signal processing circuit 24a is sent to the scan converter 24b and simultaneously stored in the image memory 27. The scan converter 24b converts the scanning line signal sequence of the ultrasonic scan into a scanning line signal sequence of a general video format represented by a television or the like.

  The output of the scan converter 24b is temporarily stored in the image data buffer 24d as first image data. For this reason, if ultrasonic scanning is repeated, a plurality of first image data are stored in the image data buffer 24d.

  The signal processing circuit 24a and the scan converter 24b constitute an image generation unit 24f (image generation means) for generating first image data.

  The image processing circuit 24c generates a diagnostic image using a plurality of first image data stored in the image data buffer 24d, and synthesizes it with character information and scales of various setting parameters. The output of the image processing circuit 24 c is output to the monitor 14 and is simultaneously stored in the image memory 27. Thus, a tomographic image representing the shape of the subject tissue is displayed on the monitor 14.

  What is important in the present invention is that the first image data, which is the output of the scan converter 24b, is temporarily stored in the image data buffer 24d, and a plurality of first image data is stored in the image data buffer 24d. A diagnostic image is generated using one image data. Details of this function will be described in (Scan Sequence).

  The image memory 27 includes a storage memory that stores image data received from the signal processing circuit 24a. The image data can be called by an operator after diagnosis, for example, and can be reproduced as a still image or as a moving image using a plurality of images. The difference between the image memory 27 and the image data buffer 24d is that the operator can call the image data stored in the image memory 27, but the operator can call the image data stored in the image data buffer 24d. This is not possible.

  The internal storage device 28 stores a scan sequence (details will be described later), a control program for executing image generation and display processing, diagnostic information (patient ID, doctor's findings, etc.), diagnostic protocol, transmission / reception conditions, and the like.

  The internal storage device 28 is also used for storing image data in the image memory 27 as necessary. Data in the internal storage device 28 can be transferred to an external peripheral device via the interface unit 29.

  The control processor 26 has a function as an information processing apparatus, and is a control means for controlling the operation of the apparatus main body 11 of the ultrasonic diagnostic apparatus.

  The interface unit 29 is an interface related to the input device 13, the network, and a new external storage device (not shown). Data such as ultrasonic images and analysis results obtained by the apparatus can be transferred to another apparatus by the interface unit 29 via the network.

(Scan sequence)
Next, an image processing protocol executed by the ultrasonic diagnostic apparatus will be described.

  FIG. 3 is a conceptual diagram for explaining image processing according to the embodiment.

  Note that this scan sequence is a contrast echo using a contrast agent, and obtains a diagnostic image by collapsing the contrast agent bubble as much as possible by performing low sound pressure transmission.

  As shown in FIG. 3, when m pieces of first image data F1, F2,... Fm (original images) are stored in the image data buffer 24d by repeating ultrasonic scanning, these first image data F1. , F2,... Fm are used to perform a minimum value holding calculation to generate first image data G1 (first ultrasonic diagnostic image).

  The minimum value holding operation is an image processing technique that compares the luminance values of spatially corresponding pixels of the first image data F1, F2,... Fm and adopts the minimum luminance value.

  If the minimum value holding calculation is used, the luminance existing in common in the first image data F1, F2,... Fm like a contrast agent bubble is held and appears in the second image data G1, but white noise (unnecessary) The luminance that occurs randomly in time and space as shown in FIG. 9 disappears by being dragged by the luminance value when it does not occur, and is removed from the second image data G1.

  Next, when m first image data Fm + 1, Fm + 2,... F2m are stored in the image data buffer 24d by performing a new ultrasonic scan, these first image data Fm + 1, Fm + 2,. In the same manner as described above, the minimum value holding calculation is performed to generate the second image data G2 for the second sheet.

  Then, the second image data G1, G2,... Generated one after another by repeating the above procedure is stored in the image memory 27 each time.

  By the way, since the contrast agent bubble in the bloodstream has a movement, when the generation rate (hereinafter referred to as “frame rate”) of the first image data F1, F2,. As a result, the luminance may be lost from the second image data G1, G2,. Therefore, it is desirable to use a faster frame rate than usual when implementing this method.

  For example, according to the results of the inventor's investigation, for a breast cancer or the like that can usually be observed at a frame rate of about 20 [Hz], when the scanning depth is about 4 [cm], the frame rate can be increased up to about 80 [Hz]. Is possible.

  Therefore, if four pieces of first image data F1 to F4 are generated at a frame rate of 80 [Hz], and the second image data G1 is generated using the first image data F1 to F4, the apparent amount is obtained. The frame rate (that is, the frame rate of the second image data G1, G2,...) Can be set to about 20 [Hz].

  However, with this method, in order to obtain n second image data G1, G2,... Gn, m × n first image data F1, F2,. The frame rate (that is, the frame rate of the first image data F1, F2,...) Is considerably increased.

  As a process that does not increase the actual frame rate, when the first image data Fm + 1 is obtained by a new ultrasonic scan, the m first image data F2, F3,... Fm + 1 obtained before that time. There is a method of generating the second image data G2 by using.

  In this method, since it is sufficient to obtain m + n−1 first image data F1, F2,... Fm + n−1 to obtain n second image data G1, G2,. Depending on the selection method, the second image data G1, G2,... Can be obtained at substantially the same frame rate as the first image data F1, F2,.

  As another process, there is also a method of calculating the average value using the spatially corresponding pixels of the first image data F1, F2,... Fm and generating the second image data G1, G2,. is there.

  The average value calculation is an image processing method that averages the luminance values of spatially corresponding pixels of the first image data F1, F2,... And adopts the average luminance value. Even if this method is used, white noise generated randomly in time and space is considerably reduced compared to the signal brightness of a standing bubble. Therefore, the second image data G1, G2 free from unnecessary noise is present. You can get ...

  When n second image data G1, G2,... Gn are stored in the image memory 27 by repeating the above procedure, the maximum value holding operation is performed using these second image data G1, G2,. The third image data Hn (second ultrasonic diagnostic image) is generated. Each time this third image data Hn is generated, it is displayed on the monitor 14 as a diagnostic image and used as a diagnostic material.

  The maximum value holding calculation is an image processing technique that compares the luminance values of the spatially corresponding pixels of the second image data G1, G2,... Gn and adopts the maximum luminance value.

  When displaying the third image data Hn on the monitor 14, when the first second image data G1 is first generated, a maximum value holding operation is performed using the second image data G1, First third image data H1 is generated.

  Needless to say, the first third image data H1 and the first second image data G1 are the same. When the second image data G2 for the second sheet is generated, the maximum value holding calculation is performed using the second image data G1 and G2 at that time, and the third image data H2 for the second sheet is generated. To do.

  That is, every time new second image data Gn is obtained, the third image is obtained by performing the maximum value holding calculation using all the second image data G1, G2,... Gn obtained so far. Data Hn is updated sequentially. Thereby, the movement in the subject is displayed on the monitor 14 in real time.

  The first image data F1, F2,... And the second image data G1, G2,... Are stored in the image memory 27 every time they are generated. Therefore, when the operator wants to see the original image, the first image data F1, F2,... And the second image data G1, G2,. Can also be displayed.

  According to the ultrasonic diagnostic apparatus having the above-described configuration, a plurality of first image data obtained by ultrasonic scanning are temporarily stored in the image data buffer 24d, and the m first images stored in the image data buffer 24d. The minimum value holding calculation is performed using the image data.

  For this reason, since there are no unnecessary signals such as white noise in the obtained plurality of second image data, even if the maximum value holding calculation is performed using these second image data, the generated second image data is generated. The above-mentioned unnecessary signal does not appear in the image data 3. As a result, a very clear diagnostic image is displayed on the monitor 14, and the diagnostic information on the minute blood vessel branching level can be extracted effectively.

  Next, a modification of the embodiment will be described with reference to FIGS. 4 and 5.

  FIG. 4 is a block diagram showing a configuration of an image generation circuit 24A according to a modification of the embodiment, and FIG. 5 is a conceptual diagram for explaining image processing according to the modification.

  The ultrasonic diagnostic apparatus of this modification has almost the same system configuration as that of the first embodiment. The difference from the first embodiment is that, as shown in FIG. 4, the image memory 27 executes the function of the image data buffer 24d (shown only in FIG. 2).

  That is, as shown in FIG. 5, in the present embodiment, a plurality of pieces of first image data F1, F2,... Obtained by ultrasonic scanning are not stored in the image data buffer 24d, Stored in the memory 27. The minimum value calculation is performed by calling m pieces of first image data F1, F2,... Fm stored in the image memory 27.

  According to the ultrasonic diagnostic apparatus according to the modified example, a plurality of pieces of first image data generated by ultrasonic scanning are stored in the image memory 27, and m pieces of first image data are stored from the image memory 27. The minimum value holding operation is performed after taking out.

  Therefore, the second image data to be generated does not include unnecessary signals such as white noise. Therefore, even if the maximum value holding calculation is performed using these second image data, the third image to be generated is generated. Such unnecessary signals do not appear in the data. As a result, a very clear diagnostic image is displayed on the monitor 14, and the diagnostic information on the fine blood vessel branching level can be extracted effectively.

  Next, a second embodiment of the present invention will be described with reference to FIGS. In addition, the description is abbreviate | omitted here about the structure and effect | action similar to 1st Embodiment.

  FIG. 6 is a block diagram showing a configuration of an image generation circuit 24B according to the second embodiment of the present invention.

  As shown in FIG. 6, the image generation circuit 24B according to the present embodiment includes a line buffer 24e instead of the image data buffer 24d. The line buffer 24e temporarily stores image data output from the signal processing circuit 24a before being converted into a video signal.

(Scan sequence)
Next, an image processing protocol executed by the ultrasonic diagnostic apparatus will be described.

  FIG. 7 is a conceptual diagram for explaining image processing according to the embodiment.

  As shown in FIG. 7, the received signal obtained by transmitting and receiving ultrasonic waves in one direction is sent to the signal processing circuit 24a, and the first time-series signal S1 (first first) indicating the luminance value of one scanning line is sent. Scanning line signal sequence). Then, by repeating transmission and reception of ultrasonic waves in the same direction, a plurality of first time series signals S2, S3,... Indicating the luminance value of the scanning line are generated. These first time series signals S1, S2,... Are temporarily stored in the line buffer 24e.

  When the m first time series signals S1, S2,... Sm are stored in the line buffer 24e, the signal processing circuit 24a holds the minimum value using these first time series signals S1, S2,. The calculation is performed to generate the first second time series signal T1 (second scanning line signal sequence).

  When the minimum value holding operation is used in this way, the luminance existing in common in the first time series signals S1, S2,... Sm like the signal from the contrast agent bubble is held, and the second time series signal T1. However, the luminance that occurs randomly in time and space, such as white noise, is removed from the second time-series signal T1 by being dragged to the luminance value when it does not occur.

  Next, ultrasonic wave transmission / reception is repeated in a direction different from the one direction to generate first time series signals Sm + 1, Sm + 2,. When m first time series signals Sm + 1, Sm + 2,... S2m are stored in the line buffer 24e, the signal processing circuit 24a uses the first time series signals Sm + 1, Sm + 2,. A value holding operation is performed to generate a second second time series signal T2.

  Then, when k second time-series signals T1, T2,... Tk are generated by repeating the above procedure, the first sheet is generated based on these second time-series signals T1, T2,. The second image data G1 is generated. The generated second image data G1 is stored in the image memory 27.

  When a series of procedures are repeated and n pieces of second image data G1, G2,... Gn are stored in the image memory 27, an image processing circuit is used by using these second image data G1, G2,. The maximum value holding operation is performed at 24c to generate the third image data Hn. Each time this third image data Hn is generated, it is displayed on the monitor 14 as a diagnostic image and used as a diagnostic material. Thereby, the movement in the subject can be obtained on the monitor 14 in real time.

  Since the second image data G1, G2,... Are stored in the image memory 27 every time they are generated, when the operator wants to see the original image, an instruction from the button 13b or the like of the input device 13 is given. , The second image data G1, G2,... Can be displayed on the monitor 14.

  According to the ultrasonic diagnostic apparatus according to the second embodiment, when performing an ultrasonic scan, ultrasonic waves are transmitted / received a plurality of times in each direction to generate a plurality of first time-series signals. ing. Then, a minimum value holding calculation is performed using these first time series signals to generate a second time series signal.

  For this reason, since there is no unnecessary signal such as white noise in the plurality of second time series signals obtained by repeating such a procedure, the maximum is obtained after converting these second time series signals into video signals. Even if the value holding operation is performed, the above-described unnecessary signal does not appear in the generated third image data. As a result, a very clear diagnostic image is displayed on the monitor 14, and the diagnostic information on the fine blood vessel branching level can be extracted effectively.

  That is, as in the present embodiment, unnecessary value signals such as white noise can be removed by performing a minimum value holding operation at the stage of the first time-series signal before being converted into a video signal. Good.

  As described above, in the first and second embodiments, the ultrasonic diagnostic apparatus has been described. However, the present invention is not limited to the ultrasonic diagnostic apparatus, and any image processing technique that performs a maximum value holding calculation can be used. Can be applied to anything.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying constituent elements without departing from the scope of the invention in the implementation stage. Moreover, various inventions can be formed by appropriately combining a plurality of constituent elements disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, you may combine suitably the component covering different embodiment.

1 is a block diagram showing a configuration of an ultrasonic diagnostic apparatus according to a first embodiment of the present invention. FIG. 3 is a block diagram showing a configuration of an image generation circuit according to the embodiment. The conceptual diagram for demonstrating the image processing which concerns on the embodiment. The block diagram which shows the structure of the image generation circuit which concerns on the modification of the embodiment. The conceptual diagram for demonstrating the image processing which concerns on the modification. The block diagram which shows the structure of the image generation circuit which concerns on the 2nd Embodiment of this invention. The conceptual diagram for demonstrating the image processing which concerns on the embodiment. The conceptual diagram for demonstrating the conventional maximum value holding calculation.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 12 ... Ultrasonic probe (ultrasonic transmission / reception means), 22 ... B-mode processing unit (scanning line information generation means), 24a ... Signal processing circuit (scanning line processing means), 24c ... Image processing circuit (image processing means), 24d ... image data buffer (storage means), 24f ... image generation unit (image generation means), 27 ... image memory, P ... subject, F ... first image data (original image), G ... second image data ( First ultrasonic diagnostic image), H ... third image data (second ultrasonic diagnostic image), S ... first time series signal (first scanning line signal sequence), T ... second time Series signal (second scanning line signal string).

Claims (10)

In an ultrasonic diagnostic apparatus for acquiring an ultrasonic diagnostic image by scanning a predetermined part of a subject to which a contrast agent bubble is administered with an ultrasonic wave,
Ultrasonic transmission / reception means for transmitting ultrasonic waves to the subject and receiving echo signals from the ultrasonic waves;
Image generating means for generating a plurality of original images based on echo signals received by the ultrasonic transmitting / receiving means;
A plurality of first ultrasonic diagnostic images with reduced noise are generated from a plurality of original images generated by the image generating means, and a maximum value holding operation is performed from the plurality of first ultrasonic diagnostic images. Image processing means for generating a second ultrasonic diagnostic image;
An ultrasonic diagnostic apparatus comprising:   The first ultrasonic diagnosis is performed by executing a minimum value holding operation that employs a minimum luminance value among spatially corresponding pixels using at least two or more of the plurality of original images. The ultrasonic diagnostic apparatus according to claim 1, wherein an image is generated.   The first ultrasonic diagnostic image is obtained by executing an average value holding operation that employs an average luminance value of spatially corresponding pixels using at least two of the plurality of original images. The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic diagnostic apparatus is generated. In an ultrasonic diagnostic apparatus for acquiring an ultrasonic wave by scanning a predetermined portion of a subject to which a contrast agent bubble is administered with an ultrasonic wave,
Ultrasonic transmission / reception means for transmitting ultrasonic waves to the subject and receiving echo signals from the ultrasonic waves;
Scanning line information generating means for generating a first scanning line signal sequence for a plurality of frames based on an echo signal received by the ultrasonic transmitting / receiving means;
The first scanning line signal sequence for a plurality of frames generated by the scanning line information generation unit, wherein noise is transmitted for each transmission direction from a plurality of first scanning line signal sequences having the same transmission direction of the ultrasonic waves. Scanning line processing means for generating a plurality of reduced second scanning line signal sequences;
Of the plurality of second scanning line signal sequences generated by the scanning line processing means, the second scanning line signal sequence constituting the same frame is combined to generate a first ultrasonic diagnostic image for each frame. And image processing means for generating a second ultrasonic diagnostic image by a maximum value holding calculation from the plurality of first ultrasonic diagnostic images generated for each frame,
An ultrasonic diagnostic apparatus comprising:   Using at least two of the plurality of first scanning line signal sequences having the same ultrasonic transmission direction, a minimum value holding operation that employs the minimum value of the amplitude value corresponding temporally or spatially is performed. The ultrasonic diagnostic apparatus according to claim 4, wherein the second scanning line signal sequence is generated by executing.   Using at least two or more of the plurality of first scanning line signal sequences having the same ultrasonic transmission direction, an average value holding operation that employs an average value of amplitude values corresponding temporally or spatially is executed. The ultrasonic diagnostic apparatus according to claim 4, wherein the second scanning line signal sequence is generated.   The ultrasonic diagnostic apparatus according to claim 1, further comprising display means for simultaneously displaying the first ultrasonic diagnostic image and the second ultrasonic diagnostic image. Storage means for storing a plurality of original images obtained by scanning a predetermined portion of a subject with ultrasound;
A plurality of first ultrasonic diagnostic images with reduced noise are generated from the plurality of original images, and a second ultrasonic diagnostic image is obtained from the plurality of first ultrasonic diagnostic images by a maximum value holding calculation. Image processing means for generating
An image processing apparatus comprising:   The first ultrasonic diagnosis is performed by executing a minimum value holding operation that employs a minimum luminance value among spatially corresponding pixels using at least two or more of the plurality of original images. The image processing apparatus according to claim 8, wherein an image is generated.   The first ultrasonic diagnostic image is obtained by executing an average value holding operation that employs an average luminance value of spatially corresponding pixels using at least two of the plurality of original images. The image processing apparatus according to claim 8, wherein the image processing apparatus is generated.

Images