JP2006204594A - Ultrasonic diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide ultrasonic diagnostic apparatus which can display an ultrasonic image which has higher resolution than a conventional one or information quality different from the conventional one by effectively utilizing frequency components contained in an ultrasonic echo. <P>SOLUTION: This ultrasonic diagnostic apparatus comprises transmitting circuits 12-14 which form driving signals for transmitting ultrasonic waves having the frequency components, receiving circuits 21-26 for processing receiving signals which are obtained by receiving the ultrasonic waves, a frequency component extracting means 30 to extract the frequency components from the received signal, an image generation means 31a, etc. which form two or more kinds of image data respectively based on a strength variation of the frequency components, an image processing means 32a, etc. which subject at least one kind of image data to space filter processing, and an image composition means 33 to compose two or more kinds of images respectively expressed by two or more kinds of image data obtained through the space filter processing by the image processing means. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to an ultrasonic diagnostic apparatus that performs imaging of an organ or bone in a living body by transmitting and receiving ultrasonic waves to generate an ultrasonic image used for diagnosis.

  In an ultrasonic imaging apparatus used for medical use, an ultrasonic probe (probe) including a plurality of ultrasonic transducers having an ultrasonic transmission / reception function is usually used. Using such an ultrasonic probe, the subject is scanned with an ultrasonic beam formed by combining a plurality of ultrasonic waves, and an ultrasonic echo reflected inside the subject is received. Thus, image information related to the subject is obtained based on the intensity of the ultrasonic echo. Furthermore, based on this image information, a two-dimensional or three-dimensional image relating to the subject is reproduced.

  By the way, the human body includes various tissues such as soft tissue such as muscle and hard tissue such as bone. It is conceivable to use a plurality of frequency components included in an ultrasonic echo as information for distinguishing these tissues in an ultrasonic image.

  As a related technique, the following Patent Document 1 discloses an ultrasonic image processing method for performing image processing of a tissue and a body fluid from a response frequency different from the transmission frequency, particularly a harmonic echo of a transmission fundamental frequency, returning from the tissue or body fluid. An apparatus is disclosed. For example, for harmonic echoes reflected from shallow areas in the body, an ultrasonic image is generated using many harmonic components, and for fundamental echoes reflected from deep areas in the body, many fundamental frequency components are used. The ultrasonic images are generated, and the ultrasonic images are blended. However, such harmonic echoes are not always generated at a sufficient level from any tissue, and even if harmonic echoes generated in a tissue are received, the frequency response characteristics of the tissue cannot be obtained. Absent.

  In Patent Document 2 below, structure-enhanced image data in which the structure of the tissue in the living body is emphasized and texture-enhanced image data in which the texture pattern resulting from the properties of the tissue in the living body is emphasized are extracted from the B-mode image data. An ultrasonic imaging apparatus that can obtain a combined image obtained by weighting and combining these two extracted image data is disclosed. However, use of a plurality of frequency components included in the ultrasonic echo is not disclosed.

  On the other hand, Patent Document 3 below discloses a biological tissue property diagnostic apparatus that can perform an accurate diagnosis regardless of a measurement target. In this biological tissue characterization apparatus, the signal analysis means includes a pulse width setting means for setting a signal pulse width of an electrical signal obtained from the received ultrasonic pulse, and at least a region within the set signal pulse width. A region extraction unit that extracts a plurality of signal regions that are partially different, a waveform feature value calculation unit that calculates a predetermined waveform feature value in each of the extraction regions, and a difference that calculates a difference between the calculated waveform feature values Calculating means, and corresponding time determining means for associating the result of the difference calculation with the reception time of the ultrasonic pulse to associate the result of the difference calculation with the position of the living tissue that generated the ultrasonic pulse. Yes. As the waveform feature value, a peak frequency, a center frequency, a specific bandwidth, a 6 dB lowering frequency, a first moment, a second moment, or the like is used. However, extracting a plurality of signal regions that are at least partly different from the set signal pulse width is equivalent to using a difference in information in the depth direction within the subject, so that distance resolution Will get worse. That is, a difference characteristic in the depth direction is obtained and does not represent a characteristic at one point.

Further, Patent Document 4 below discloses a sound impedance measuring apparatus with a possibility of being able to display an image of the acoustic impedance of a measurement object at high speed with high resolution. This acoustic impedance measuring apparatus calculates a frequency impedance of an object to be measured using a frequency conversion means for obtaining a frequency characteristic of an ultrasonic response signal, a parameter extraction means for extracting a predetermined parameter from the frequency characteristic, and the extracted parameter. And an acoustic impedance calculating means. In this acoustic impedance measuring apparatus, a broadband pulse signal such as a trapezoidal pulse or a rectangular pulse is used to measure the acoustic impedance of a measurement object. Such a pulse signal includes only a specific frequency component determined by a waveform even in a wide band, and the ratio of these components is also limited.
JP-A-10-179589 (second page, FIG. 1) JP 2004-129773 A (first page, FIG. 3) Japanese Patent Laid-Open No. 2001-170046 (first, second, fifth page, FIG. 4) JP 2000-5180 A (2nd, 5th, 6th pages, FIG. 1)

  Accordingly, in view of the above points, the present invention transmits an ultrasonic beam including a plurality of frequency components toward the subject, and also includes a plurality of frequency components included in the ultrasonic echo reflected from the subject. An object of the present invention is to provide an ultrasonic diagnostic apparatus capable of displaying an ultrasonic image having a resolution higher than that of the prior art or a quality of information different from that of the prior art by being effectively used. Furthermore, an object of the present invention is to provide an ultrasonic diagnostic apparatus capable of highlighting and displaying a specific tissue.

  In order to solve the above problems, an ultrasonic diagnostic apparatus according to the present invention generates a drive signal for driving an ultrasonic probe so as to transmit ultrasonic waves having a plurality of frequency components to a subject. A circuit, a reception circuit that processes a reception signal obtained by receiving an ultrasonic wave reflected from or transmitted through the subject, and a frequency component that extracts a plurality of frequency components from the reception signal processed by the reception circuit An extraction unit; an image generation unit that generates a plurality of types of image data based on intensity changes of a plurality of frequency components extracted by the frequency component extraction unit; and a plurality of types of image data generated by the image generation unit An image processing unit that performs spatial filtering on at least one type of image data, and a plurality of types of image data after the spatial filtering by the image processing unit Comprising an image combining means for combining a plurality of types of images represented respectively.

  According to the present invention, a plurality of types of image data are respectively generated based on a plurality of frequency components extracted by the frequency component extraction means, and a plurality of types of image data are applied after performing spatial filtering on at least one type of image data. By synthesizing the images, it is possible to display an ultrasonic image having a higher resolution than before or having information quality different from that of the conventional one, or to display a specific tissue with emphasis.

Hereinafter, the best mode for carrying out the present invention will be described in detail with reference to the drawings. The same constituent elements are denoted by the same reference numerals, and the description thereof is omitted.
FIG. 1 is a block diagram showing a configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention. As shown in FIG. 1, the ultrasonic diagnostic apparatus according to the present embodiment includes an ultrasonic probe 10, a scanning control unit 11, a transmission delay pattern storage unit 12, a transmission control unit 13, and a drive signal generation. Part 14.

  An ultrasonic probe 10 used in contact with a subject includes a plurality of ultrasonic transducers 10a arranged in a one-dimensional or two-dimensional manner to constitute a transducer array. These ultrasonic transducers 10a transmit an ultrasonic beam according to an applied drive signal, receive a propagating ultrasonic echo, and output a received signal.

  Each ultrasonic transducer is, for example, a piezoelectric ceramic represented by PZT (Pb (lead) zirconate titanate), a polymer piezoelectric element represented by PVDF (polyvinylidene difluoride), or the like. It is comprised by the vibrator | oscillator which formed the electrode at the both ends of the material (piezoelectric body) which has the piezoelectricity. When a voltage is applied to the electrodes of such a vibrator by sending a pulsed electric signal or a continuous wave electric signal, the piezoelectric body expands and contracts. By this expansion and contraction, pulsed ultrasonic waves or continuous wave ultrasonic waves are generated from the respective vibrators, and an ultrasonic beam is formed by synthesizing these ultrasonic waves. Each vibrator expands and contracts by receiving propagating ultrasonic waves and generates an electrical signal. These electric signals are output as ultrasonic reception signals.

  Alternatively, a plurality of types of elements having different conversion methods may be used as the ultrasonic transducer. For example, the above-described vibrator is used as an element that transmits ultrasonic waves, and a photodetection type ultrasonic transducer is used as an element that receives ultrasonic waves. The photodetection type ultrasonic transducer converts an ultrasonic signal into an optical signal and detects it, and is constituted by, for example, a Fabry-Perot resonator or a fiber Bragg grating.

  Further, an ultrasonic probe that transmits ultrasonic waves and an ultrasonic probe that receives ultrasonic waves are arranged to face each other, so that ultrasonic waves that pass through the subject may be received. . In that case, the distance between the transmitting probe and the receiving probe can be adjusted, and these probes are used by pressing them against the subject.

  The scanning control unit 11 sequentially sets the transmission direction of the ultrasonic beam and the reception direction of the ultrasonic echo. The transmission delay pattern storage unit 12 stores a plurality of transmission delay patterns used when forming an ultrasonic beam. The transmission control unit 13 selects a predetermined pattern from a plurality of delay patterns stored in the transmission delay pattern storage unit 12 according to the transmission direction set in the scanning control unit 11, and based on the pattern The delay time given to each of the plurality of ultrasonic transducers 10a is set.

  The drive signal generation unit 14 generates a signal having a plurality of frequency components, gives a desired delay to the signal generated by the signal generation circuit, and supplies a plurality of drive signals supplied to the plurality of ultrasonic transducers 10a. And a plurality of drive circuits that respectively generate. These drive circuits delay the signal generated by the signal generation circuit based on the delay time set in the transmission control unit 13.

  In the present embodiment, a signal having a plurality of frequency components such as a chirp signal, a burst signal, or a frequency multiplexed signal is used as the drive signal. Alternatively, a wideband ultrasonic signal having a plurality of frequency components may be transmitted by using a wideband ultrasonic transducer in a pulsed drive signal. The frequency band of the drive signal is preferably at least 0.5 MHz to 3 MHz. Thereby, an ultrasonic wave having a frequency band of at least 0.5 MHz to 3 MHz is transmitted. In ultrasonic imaging, the beam diameter, penetration, and the like differ depending on the frequency of the transmitted and received ultrasonic waves. Therefore, by transmitting and receiving ultrasonic waves having a plurality of frequency components, a plurality of ultrasonic images having different information quality are acquired. Because it can.

  The ultrasonic diagnostic apparatus according to the present embodiment includes an operation console 15, a control unit 16 configured by a CPU, and a recording unit 17 such as a hard disk. The control unit 16 controls the scanning control unit 11, the drive signal generation unit 14, and the image composition unit 36 based on an operator's operation using the console 15. The recording unit 17 stores a control program that causes the CPU constituting the control unit 16 to execute various operations.

  Furthermore, the ultrasonic diagnostic apparatus according to the present embodiment includes a preamplifier 21, a TGC (time gain compensation) amplifier 22, an A / D (analog / digital) converter 23, a received signal storage unit 24, Reception delay pattern storage unit 25, reception control unit 26, chirp compression unit 27, envelope detection processing unit 28, B-mode image data generation unit 29, frequency component extraction unit 30, and frequency component image generation unit 31a , 31b,..., Image processing units 32a, 32b,..., Frequency component image synthesis unit 33, automatic frequency determination unit 34, parameter determination unit 35, image synthesis unit 36, and display unit 37.

  The reception signal output from each of the plurality of ultrasonic transducers 10a is amplified by the preamplifier 21, and the TGC amplifier 22 corrects the attenuation due to the distance that the ultrasonic wave has reached within the subject.

  The reception signal output from the TGC amplifier 22 is converted into a digital signal by the A / D converter 23. Note that the sampling frequency of the A / D converter 23 needs to be at least about 10 times the frequency of the ultrasonic wave, and is preferably 16 times or more the frequency of the ultrasonic wave. The resolution of the A / D converter 23 is preferably 10 bits or more. The reception signal storage unit 24 stores the digital reception signal output from the A / D converter 23 in time series for each ultrasonic transducer.

  The reception delay pattern storage unit 25 stores a plurality of reception delay patterns used when receiving focus processing is performed on a plurality of reception signals output from the plurality of ultrasonic transducers 10a. The reception control unit 26 selects a predetermined pattern from a plurality of reception delay patterns stored in the reception delay pattern storage unit 25 based on the reception direction set in the scanning control unit 11, and based on the pattern. The reception focus process is performed by adding a delay to a plurality of reception signals. By this reception focus processing, sound ray data representing the sound ray signal in which the focus of the ultrasonic echo is narrowed is formed. Note that the reception focus process may be performed before A / D conversion or before correction by the TGC amplifier.

  The chirp compression unit 27 is used to encode a transmission wave with respect to the chirp signal represented by the sound ray data output from the reception control unit 26 when a chirp signal is used as a drive signal when transmitting an ultrasonic wave. The autocorrelation coefficient is obtained by multiplying and adding the same chirp codes. By decoding the sound ray data in this way, it is possible to compress information included in a plurality of frequency components included in the broadband chirp signal and obtain information with high time resolution and SN ratio.

  The envelope detection processing unit 28 obtains envelope data representing the envelope of the sound ray signal by performing envelope detection processing on the decoded sound ray data. The B-mode image data generation unit 29 generates B-mode image data by performing processing such as scan conversion on the envelope data.

  The frequency component extraction unit 30 performs a fast Fourier transform (FFT) on the sound ray data output from the reception control unit 26, thereby extracting a plurality of frequency components included in the sound ray signal. Based on the change in the amplitude (intensity) of the frequency components, envelope data representing the envelope of those frequency components is obtained. Alternatively, the frequency component extraction unit 30 is included in the sound ray signal by performing a plurality of narrowband bandpass filter processes having different pass bands on the sound ray data output from the reception control unit 26. While obtaining data representing a plurality of frequency components, envelope data representing the envelopes of these frequency components may be obtained by performing envelope detection processing on the data representing those frequency components.

  Here, the frequency component extraction unit 30 calculates a plurality of frequencies included in the ultrasonic wave transmitted from the ultrasonic probe 10 from the sound ray signal represented by the sound ray data output from the reception control unit 26. You may make it extract the several frequency component which each has. For example, when the transmitted ultrasonic wave has a frequency band of 0.5 MHz to 3 MHz, the frequency component extraction unit 30 extracts a frequency component of fa = 1 MHz and a frequency component of fb = 2 MHz. Further, each frequency component may have a fixed bandwidth as represented by fa = 1 MHz ± Δf.

  The frequency component image generation units 31a, 31b,... Perform a process such as scan conversion on the plurality of types of envelope data extracted by the frequency component extraction unit 30, thereby providing a plurality of types of image data ( Frequency component image data) is generated.

  The image processing units 32a, 32b,... Are for at least one type of frequency component image data among the plurality of types of frequency component image data generated by the frequency component image generation units 31a, 31b,. Apply spatial filtering. Alternatively, the image processing units 32a, 32b,... Independently perform the spatial filter processing on a plurality of types of frequency component image data generated by the frequency component image generation units 31a, 31b,. May be. As the spatial filter processing, frequency enhancement processing, noise removal processing, morphology processing, and the like are performed singly or in combination.

  For example, since an ultrasonic beam with a frequency fa = 1 MHz has a relatively large beam diameter, an image (fa image) obtained based on a frequency component with fa = 1 MHz has a relatively low resolution (both vertically and horizontally). However, the SN ratio is relatively good. On the other hand, since the ultrasonic beam having the frequency fb = 2 MHz has a relatively small beam diameter, the resolution (both vertical and horizontal) is relatively high in the image (fb image) obtained based on the frequency component of fb = 2 MHz. However, the S / N ratio gets worse. Therefore, the fa image is subjected to frequency enhancement in the vicinity of the spatial frequency corresponding to the reception frequency of 1 MHz, and the fb image is reduced in components other than the spatial frequency corresponding to the reception frequency of 2 MHz. It is desirable to increase the level while performing noise removal processing.

  The frequency component image synthesizing unit 33 synthesizes a plurality of types of images respectively represented by a plurality of types of frequency component image data subjected to spatial filter processing by the image processing units 32a, 32b,. For example, by adding and synthesizing pixel values in the fa image and the fb image that have been subjected to the spatial filter processing as described above, compared with a normal B-mode image, the SN ratio is the same and abundant in high-frequency information. Can create a simple image.

  Alternatively, the frequency component image synthesis unit 33 weights the pixel values of the plurality of types of frequency component image data that have been subjected to the spatial filter processing by the image processing units 32a, 32b,. When the pixel values of the other type of image data are subtracted from the pixel values of the data and combined to create a difference in tissue properties when multiple types of frequency component image data represent specific tissue properties, respectively. It is possible to generate image data representing an image with emphasis.

  Here, since each image based on a plurality of types of frequency components has different resolutions, noise components, etc., taking the difference between the two images as it is may increase noise or cause artifacts at the edge due to the difference in resolution. There is. Therefore, the image processing units 32a, 32b,... Perform spatial filter processing so as to match the spatial resolution in the plurality of types of images respectively represented by the plurality of types of frequency component image data, and cut unnecessary frequency components. Later, when the frequency component image synthesis unit 33 calculates the difference between the two images, an easily viewable image can be obtained. For example, the fa image is subjected to notch filter processing centered on the spatial frequency corresponding to the 1 MHz reception frequency, and the fb image corresponds to the spatial frequency resolution corresponding to the 1 MHz reception frequency. The frequency difference image data is generated by taking the difference between the two images after reducing the resolution by halving the resolution.

  The attention frequency automatic determination unit 34 automatically determines a plurality of frequency components to be noticed from among a large number of frequency components obtained by the frequency component extraction unit 30 performing FFT on the sound ray data. . For example, the attention frequency automatic determination unit 34 may determine a component having a predetermined frequency as a notable frequency component, or may determine a frequency component having a high intensity as a notable frequency component. Then, a frequency component having a large peak or dip in all or a part of the depth direction of the subject may be determined as a notable frequency component.

  2 to 4 show the difference in the relative transmittance of ultrasonic waves due to the difference in the tissue in the subject. 2 shows the frequency characteristics of relative transmittance in the spine A part, FIG. 3 shows the spine B part, and FIG. 4 shows the relative transmittance in the spine C part. As the drive signal, a chirp signal having a center frequency of 1 MHz and a chirp signal having a center frequency of 2.25 MHz are used. Here, the backbone A portion and the backbone B portion are relatively soft tissues, and the backbone C portion is a relatively hard tissue. As shown in FIGS. 2 to 4, the frequency characteristics of the relative transmittance in each part are greatly different.

  By determining the frequency of each frequency component based on the characteristics related to the frequency characteristics of a specific tissue in the part where the ultrasonic echo intensity is high, the difference in the properties of multiple tissues contained in the subject is further emphasized. Can be displayed. On the other hand, by determining the frequency of a plurality of frequency components by paying attention to a portion where the ultrasonic echo intensity is low, it is possible to reduce the speckle component generated as a result of adding and interfering with many weak echoes. In any case, the SN ratio can be improved.

  Specifically, the ratio of the frequency component intensity of 2 MHz to the intensity of the 1.6 MHz frequency component extracted by the frequency component extraction unit 30 is +8 dB in the spine A portion, +24 dB in the spine B portion, and − in the spine C portion. In the case of 14 dB, the frequency component image generation units 31a and 31b generate and output two types of image data corresponding to the frequency components 1.6 MHz and 2 MHz, respectively. These two types of image data are subjected to spatial filter processing in the image processing units 32a and 32b, respectively, and unnecessary frequency components are cut.

  Further, the frequency component image composition unit 33 generates frequency difference image data by taking the difference between the two types of images respectively represented by the two types of image data. In this frequency difference image data, the ratio of the intensity of the 2 MHz frequency component to the intensity of the 1.6 MHz frequency component is +8 dB in the spine A portion, +24 dB in the spine B portion, and −14 dB in the spine C portion. The difference between the parts can be clearly imaged.

  When image data is simply generated based on one frequency component, the image data is strongly influenced by the intensity change of the frequency component. However, as in the present embodiment, the relative relationship between a plurality of frequency components is obtained. When generating image data based on the above, it is possible to reduce the influence of intensity changes of those frequency components, and to generate image data that reflects the difference in frequency characteristics representing the characteristics of tissue properties in the subject. is there.

  The parameter setting unit 35 is used in the spatial filter processing performed by the image processing units 32a, 32b,... Based on the frequencies of the plurality of frequency components to be noted determined by the attention frequency automatic determination unit 34. Set the parameter value.

  The image synthesis unit 36 synthesizes the B-mode image data generated by the B-mode image data generation unit 29 and the frequency component image data generated by the frequency component image synthesis unit 33, or one of them. Select to output. The display unit 37 includes, for example, a display device such as a CRT or LCD, and displays an ultrasonic image based on the image data subjected to image processing by the image processing unit 37.

  FIG. 5 schematically shows an example of an ultrasonic image displayed in the ultrasonic diagnostic apparatus according to the present embodiment. FIG. 5A is a diagram showing a B-mode image, where the inside of the hard tissue (bone) is almost unknown, but the soft tissue (muscle) existing outside the hard tissue (bone) is represented. An ultrasonic image is generated. On the other hand, FIG. 5B is a diagram showing a frequency component image. By extracting an appropriate frequency component, the inside of the hard tissue (bone) can be emphasized and displayed. In addition, the separation between the hard tissue (bone) and the soft tissue (muscle) is clearly shown, and it is possible to image from the bone to the epidermis.

  FIG. 5C shows the B-mode image and the frequency component image synthesized and displayed. For example, the image synthesis unit 36 (see FIG. 1) is generated by the B-mode image data generation unit 29. A luminance signal (or chromaticity signal) may be output based on the image data, and a chromaticity signal (or luminance signal) may be output based on the image data generated by the frequency component image synthesis unit 33.

  INDUSTRIAL APPLICABILITY The present invention can be used in an ultrasonic diagnostic apparatus that performs imaging of an organ or bone in a living body by transmitting and receiving ultrasonic waves to generate an ultrasonic image used for diagnosis.

1 is a block diagram illustrating a configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention. It is a figure which shows the frequency characteristic of the relative transmittance | permeability in the backbone A part. It is a figure which shows the frequency characteristic of the relative transmittance | permeability in the backbone B part. It is a figure which shows the frequency characteristic of the relative transmittance | permeability in the backbone C part. It is a figure which shows typically the example of the ultrasonic image displayed in the ultrasonic diagnosing device which concerns on the 1st Embodiment of this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Ultrasonic probe 10a Ultrasonic transducer 11 Scan control part 12 Transmission delay pattern memory | storage part 13 Transmission control part 14 Drive signal generation part 15 Operation console 16 Control part 17 Recording part 21 Preamplifier 22 TGC amplifier 23 A / D converter 24 reception signal storage unit 25 reception delay pattern storage unit 26 reception control unit 27 chirp compression unit 28 envelope detection processing unit 29 B-mode image data generation unit 30 frequency component extraction units 31a, 31b, ... frequency component image generation unit 32a , 32b,... Image processing unit 33 Frequency component image composition unit 34 Automatic frequency of interest determination unit 35 Parameter setting unit 36 Image composition unit 37 Display unit

Claims (7)

A transmission circuit for generating a drive signal for driving the ultrasonic probe so as to transmit ultrasonic waves having a plurality of frequency components to the subject;
A receiving circuit for processing a reception signal obtained by receiving an ultrasonic wave reflected from the subject or transmitted through the subject;
Frequency component extraction means for extracting a plurality of frequency components from the received signal processed by the receiving circuit;
Image generation means for generating a plurality of types of image data based on intensity changes of a plurality of frequency components extracted by the frequency component extraction means;
Image processing means for performing spatial filter processing on at least one kind of image data of the plurality of kinds of image data generated by the image generation means;
Image combining means for combining a plurality of types of images respectively represented by a plurality of types of image data after the spatial filter processing by the image processing means;
An ultrasonic diagnostic apparatus comprising:   The image composition means weights the pixel values of a plurality of types of image data, and then subtracts the pixel value of the other type of image data from the pixel value of the one type of image data, thereby The ultrasonic diagnostic apparatus according to claim 1, wherein image data representing an image in which differences in properties of a plurality of tissues included are emphasized is generated.   The ultrasonic diagnosis according to claim 1, wherein the transmission circuit generates a drive signal for driving the ultrasonic probe so as to transmit an ultrasonic wave having a frequency band of at least 0.5 MHz to 3 MHz. apparatus.   The frequency component extraction unit extracts a plurality of frequency components each having a plurality of frequencies included in the ultrasonic wave transmitted by the transmission circuit from the reception signal processed by the reception circuit. The ultrasonic diagnostic apparatus of any one of Claims.   The ultrasonic diagnostic apparatus according to claim 1, wherein the image processing unit independently performs a spatial filter process on a plurality of types of image data generated by the image generation unit.   The said image processing means performs the frequency emphasis process and / or noise removal process as a spatial filter process with respect to the multiple types of image data produced | generated by the said image generation means. Ultrasound diagnostic equipment.   The ultrasonic diagnostic apparatus according to claim 1, wherein the image processing unit performs a spatial filter process so as to match a spatial resolution in a plurality of types of images respectively represented by a plurality of types of image data.