JP2007244501A - Ultrasonic diagnostic apparatus, and method and program for processing image thereof - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To change a frame rate to a suitable one according to whether a virtual image is generated in an area while suppressing the occurrence of the virtual image by a residual multiple echo. <P>SOLUTION: In an ultrasonic diagnostic apparatus 1, a residual multiple echo virtual image occurrence judging part 33 judges whether or not the virtual image due to the residual multiple echo occurs based on the difference images of two or more images generated by transmission and reception of ultrasonic waves of two or more different pulse repeated frequencies, a residual multiple echo virtual image occurrence depth/area calculation part 34 calculates a depth and area where the virtual image due to the residual multiple echo occur, a residual multiple echo virtual image occurrence suppression pulse repeated frequency calculation part 35 calculates a residual multiple echo virtual image occurrence suppression pulse repeated frequency, and a repeated frequency changing part 36 changes a pulse repeated frequency to the residual multiple echo virtual image occurrence suppression pulse repeated frequency. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus, an image processing method thereof, and an image processing program thereof, and more particularly, suitable frames depending on whether or not a virtual image is generated while suppressing generation of a virtual image due to residual multiple echoes. The present invention relates to an ultrasonic diagnostic apparatus which can be changed to a rate, an image processing method thereof, and an image processing program thereof.

  In the B-mode tomographic image display mode of the ultrasonic diagnostic apparatus, an electrical signal having a relatively short wavelength is applied to an ultrasonic transducer, and the ultrasonic wave is transmitted to a target patient (hereinafter referred to as “subject”). By continuously receiving the reflected wave of the ultrasonic wave from the subject, the surface from the subject surface (contact surface with the ultrasonic probe) to a predetermined depth (hereinafter referred to as “depth”). Structural information (such as tomographic images) can be acquired.

Here, in general, in scanning for acquiring a tomographic image in the B-mode tomographic image display mode of the ultrasonic diagnostic apparatus, ultrasonic waves are repeatedly transmitted and received at a predetermined time interval while moving a spatial position (while scanning). I do. The time interval at which this ultrasonic transmission pulse is repeatedly transmitted is called “pulse repetition period (S)”, and the number of times the ultrasonic transmission pulse is transmitted per unit time is “pulse repetition frequency (1 / S)”. That's it. In addition, the number of scans of ultrasonic transmission / reception repeated to acquire one tomographic image is called “number of scanning lines”, and “frame rate (1 / S)” which is the number of tomographic images acquired per unit time. Can be obtained according to [Equation 1]. Note that the pulse repetition period and the pulse repetition frequency have a reciprocal relationship.
[Equation 1]
Frame rate (1 / S) = Pulse repetition frequency (1 / S) / Number of scanning lines

  This frame rate is used as an index representing the response performance of the B-mode tomographic image of the ultrasonic diagnostic apparatus, and the higher the frame rate, the better the B-mode tomographic image can be acquired. Therefore, in the B-mode tomographic image display mode of the ultrasonic diagnostic apparatus, it is particularly required to improve the frame rate as much as possible.

  Here, considering the above [Equation 1], two methods are conceivable as methods for improving the frame rate. As a first method, a method of reducing the number of scanning lines which is the number of times of ultrasonic transmission / reception repeated for obtaining one tomographic image is conceivable. As a second method, a method of increasing the pulse repetition frequency is considered. Conceivable.

  In the first method, the frame rate can be increased by reducing the number of scanning lines. However, as a result, the information used in constructing the B-mode tomographic image is reduced. The resolution is extremely reduced. That is, if the acceptable resolution of the B-mode tomographic image is maintained, the number of scanning lines that can be reduced is naturally limited.

  At present, the more difficult it is to reduce the number of scanning lines, the more the number of scanning lines is reduced to the limit of the allowable range of resolution of the B-mode tomographic image, so the frame rate is improved by further reducing the number of scanning lines. That is not realistic.

Therefore, it is examined whether the frame rate can be improved by the second method of increasing the pulse repetition frequency. The pulse repetition frequency is the number of times an ultrasonic transmission pulse is transmitted per unit time, of which the highest pulse repetition frequency (hereinafter referred to as “maximum pulse repetition frequency”) that can be set under a predetermined condition. It can be obtained according to [Equation 2] based on the display depth of the B-mode tomographic image obtained by an operator of the ultrasonic diagnostic apparatus (for example, a doctor or an engineer, hereinafter referred to as “operator”).
[Equation 2]
Maximum pulse repetition frequency = 1 / {(time for ultrasonic wave to reciprocate to display depth) + (control time for ultrasonic diagnostic apparatus to control transmission / reception)} = 1 / {(2 × display depth / acoustic wave propagation speed) ) + Control time}

  That is, theoretically, the pulse repetition frequency can be increased to the maximum pulse repetition frequency. However, the ultrasonic wave is attenuated by the composition and structure of the subject in the body until it is reciprocated in the subject's body and received by the ultrasound probe, but the pulse repetition frequency is the highest pulse repetition frequency. The pulse repetition cycle, which is the time interval at which the ultrasonic transmission pulse is repeatedly transmitted, is naturally shortened. Therefore, after the transmission / reception of the ultrasonic wave, the time until the transmission / reception of the next ultrasonic wave is performed. Sound waves cannot be sufficiently attenuated due to the composition and structure in the body of the subject.

  If the next ultrasonic wave is transmitted while the ultrasonic wave is not sufficiently attenuated due to the composition and structure in the body of the subject, a reflected signal from a region deeper than the display depth of the already transmitted ultrasonic wave and a new ultrasonic wave Thus, a signal in which a reflected signal from a short distance that is shallower than the display depth is mixed is received. In such a case, it becomes impossible to correctly display the depth and position of the living body soft tissue of the subject based on the reflected signal of the ultrasonic wave.

  Specifically, for example, as shown in FIG. 1, the tomographic image a and the tomographic image b are not displayed as a tomographic image because they exist in the region A outside the set display depth. Thus, the tomographic image c and the tomographic image d are displayed in the vicinity of the tomographic image e used for the operator's diagnosis. Such a phenomenon is called a virtual image generation phenomenon due to residual multiple echoes of ultrasonic waves, and hinders an operator's ultrasonic diagnosis. In particular, since the attenuation of the ultrasonic wave becomes smaller as the transmission / reception frequency of the ultrasonic wave becomes lower, the generation of a virtual image due to the residual multiple echo is likely to occur when using the low-frequency ultrasonic wave.

  Therefore, in order to suppress the occurrence of such a virtual image due to residual multiple echo, the ultrasonic pulse repetition period is set in advance to a period longer than the pulse repetition period according to the display depth of the B-mode tomographic image that the operator seeks, A method has been proposed in which the ultrasonic pulse repetition frequency is set in advance lower than the maximum pulse repetition frequency (see, for example, Patent Document 1).

According to the method proposed in Patent Document 1, the upper limit value of the pulse repetition frequency is changed according to the transmission / reception frequency and the depth of field of the ultrasonic wave while suppressing the generation of a virtual image due to the residual multiple echo. Can do.
Japanese Patent Laid-Open No. 5-245141

  The soft tissue in the body of the subject includes a region where a virtual image due to residual multiple echo is likely to occur and a region where a virtual image due to residual multiple echo is difficult to occur. For example, when there is a strong reflector (for example, bone) that reflects ultrasonic waves deeply in the body of the subject, the pulse repetition frequency of the ultrasonic waves in advance to suppress the generation of virtual images due to residual multiple echoes Is set lower than the maximum pulse repetition frequency, the signal intensity of the reflected signal is strong, so that the ultrasonic wave cannot be sufficiently attenuated in the body of the subject, and a virtual image due to residual multiple echoes is likely to occur. In addition, when an operator diagnoses a subject's heart or the like using an ultrasonic diagnostic apparatus, the ultrasonic wave is attenuated relatively little in water or blood in the subject's body. Cannot be sufficiently attenuated, and a virtual image due to residual multiple echoes is likely to occur.

  Therefore, according to the method proposed in Patent Document 1, a low pulse repetition frequency is set in advance in order to suppress the generation of a virtual image due to residual multiple echoes, and the ultrasonic transmission / reception frequency and the visual field depth are made to correspond. Although the upper limit of the pulse repetition frequency can be changed, in the region where a virtual image due to residual multiple echo is likely to occur, the frame rate is slightly lowered and the ultrasonic pulse repetition frequency is set low in advance. Eventually, there was a problem that the generation of virtual images due to residual multiple echoes could not be suppressed.

  Of course, even with the method proposed in Patent Document 1, theoretically, it is possible to completely suppress the generation of virtual images due to residual multiple echoes by extremely reducing the pulse repetition frequency. Is extremely impractical and is not practical. Also, in this case, even in a region where a virtual image due to residual multiple echo is unlikely to occur, the frame rate is drastically reduced at the same time, so the frame rate is excessively reduced in a region where a virtual image due to residual multiple echo is unlikely to occur. There was a problem.

  In addition, whether or not a virtual image due to residual multiple echoes is generated depends not only on the part where the subject is diagnosed, but also on the diagnostic environment such as the body movement of the subject and the position where the ultrasonic probe is contacted. It is not so easy to determine whether or not the site to be diagnosed is a region where residual multiple echoes are likely to occur. Therefore, if the residual multiple echo is more likely to occur than the operator predicted in advance before scanning the ultrasonic wave, even if the ultrasonic pulse repetition frequency is set low in advance, the residual multiple echo There has been a problem that the virtual image is displayed as a tomographic image, which hinders an operator's diagnosis.

  Thus, it has been difficult to simultaneously suppress the generation of virtual images due to residual multiple echoes and improve the frame rate.

  The present invention has been made in view of such a situation, and changes the frame rate to a suitable frame rate depending on whether or not the area is where a virtual image is generated while suppressing the generation of a virtual image due to residual multiple echoes. It is an object of the present invention to provide an ultrasonic diagnostic apparatus, an image processing method thereof, and an image processing program thereof.

  In order to solve the above-described problems, an ultrasonic diagnostic apparatus of the present invention transmits and receives ultrasonic waves having a predetermined pulse repetition frequency, and generates ultrasonic image data from received signals, and a plurality of different pulses. Virtual image generation determination means for determining whether or not a virtual image due to residual multiple echo is generated based on a plurality of image data generated by the image data generation means by transmission and reception of ultrasonic waves at a repetition frequency, and a virtual image due to residual multiple echo A residual multiple echo virtual image generation depth calculation means for calculating the depth at which the residual multiple echo is generated, and a residual multiple echo virtual image generation depth calculation means based on the depth at which a virtual image due to the residual multiple echo calculated by the residual multiple echo virtual image generation depth calculation means is generated. Residual multiple echo virtual image generation suppression pulse repetition frequency that is the pulse repetition frequency that suppresses virtual image generation Characterized in that it comprises a multiple echo virtual image generation suppression pulse repetition frequency calculation unit, and a pulse repetition pulse repetition frequency changing means changes the frequency when transmitting and receiving ultrasonic waves.

  The pulse repetition frequency changing means determines the residual multiple echo virtual image generation suppression pulse repetition when the residual multiple echo virtual image generation determination means determines that a virtual image due to residual multiple echo is generated. If it is determined that a virtual image due to residual multiple echo is not generated by the residual multiple echo virtual image generation determination means, the pulse repetition frequency when transmitting and receiving ultrasonic waves is set as the residual multiple echo virtual image generation suppression pulse repetition frequency. The frequency can be changed to a higher frequency.

  This ultrasonic diagnostic apparatus calculates a region where a virtual image due to residual multiple echo is generated when the virtual image generation determination unit determines that a virtual image due to residual multiple echo is generated. The pulse repetition frequency changing means changes the pulse repetition frequency when transmitting / receiving ultrasonic waves to a residual multiple echo virtual image generation suppression pulse repetition frequency in a scanning line related to a region where a virtual image due to residual multiple echo is generated. In a scanning line that does not relate to a region where a virtual image due to residual multiple echo is generated, the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed to a frequency higher than the residual multiple echo virtual image generation suppression pulse repetition frequency. Can do.

  The virtual image generation determination means is based on a predetermined reference value set in advance in the difference image based on a difference image of the plurality of image data generated by the image data generation means by transmission / reception of ultrasonic waves having a plurality of different pulse repetition frequencies. Brightness determination means for determining whether there is a portion having a large brightness difference, and the residual multiple echo virtual image generation determination means has a brightness difference larger than a predetermined reference value preset in the difference image by the brightness determination means. When it is determined that there is a portion, it is determined that a virtual image due to residual multiple echo has occurred, and it is determined by the luminance determination means that there is no portion having a luminance difference larger than a predetermined reference value set in advance in the difference image. In this case, it can be determined that a virtual image due to residual multiple echo has not occurred.

  The ultrasonic diagnostic apparatus includes a residual multiple echo virtual image generation region area ratio calculating unit that calculates a residual multiple echo virtual image generation region area ratio that is a ratio of a region area occupied by a generated virtual image due to the residual multiple echo on the entire display screen; A residual multiple echo virtual image generation region area ratio determining means for determining whether the residual multiple echo virtual image generation region area ratio is greater than a predetermined reference value based on the residual multiple echo virtual image generation region area ratio; The pulse repetition frequency changing means transmits and receives ultrasonic waves when the residual multiple echo virtual image generation area area ratio determination means determines that the residual multiple echo virtual image generation area area ratio is greater than a predetermined reference value set in advance. Change the pulse repetition frequency to the residual multiple echo virtual image generation suppression pulse repetition frequency When it is determined by the co-virtual image generation area ratio determination means that the residual multiple echo virtual image generation area area ratio is not larger than a predetermined reference value set in advance, the pulse repetition frequency when transmitting / receiving ultrasonic waves is determined as the residual multiple echo. The frequency can be changed to a frequency higher than the virtual image generation suppression pal repetition frequency.

  The image data generating means transmits / receives ultrasonic waves having the changed pulse repetition frequency after the pulse repetition frequency when the ultrasonic waves are transmitted / received by the pulse repetition frequency changing means, and generates ultrasonic image data from the received signal. To be able to.

  The ultrasonic diagnostic apparatus further includes a display control unit that displays data related to a residual multiple echo virtual image generation suppression pulse repetition frequency, and an input unit that inputs data of a predetermined pulse repetition frequency when transmitting and receiving ultrasonic waves, The pulse repetition frequency changing means can change the pulse repetition frequency when transmitting / receiving ultrasonic waves to a predetermined pulse repetition frequency based on data of the predetermined pulse repetition frequency input by the input means. .

  In order to solve the above-described problem, an image processing method of an ultrasonic diagnostic apparatus according to the present invention is based on a plurality of image data generated by scanning ultrasonic waves having a plurality of different pulse repetition frequencies. A residual multiple echo virtual image generation determination step for determining whether or not a virtual image is generated by a residual multiple echo virtual image generation depth calculation step for calculating a depth at which a virtual image due to residual multiple echo is generated, and a residual multiple echo virtual image generation Based on the depth at which the virtual image due to the residual multiple echo calculated by the processing of the depth calculation step is generated, the residual multiple echo virtual image generation suppression pulse repetition frequency that suppresses the generation of the virtual image due to the residual multiple echo is calculated. The residual multiple echo virtual image generation suppression pulse repetition frequency calculation step and ultrasonic transmission / reception Characterized in that it comprises a pulse repetition frequency changing step changes the Kino pulse repetition frequency. In order to solve the above-described problem, an image processing program for an ultrasonic diagnostic apparatus according to the present invention is based on a plurality of image data generated by scanning ultrasonic waves having a plurality of different pulse repetition frequencies. A residual multiple echo virtual image generation determination step for determining whether or not a virtual image is generated by a residual multiple echo virtual image generation depth calculation step for calculating a depth at which a virtual image due to residual multiple echo is generated, and a residual multiple echo virtual image generation Based on the depth at which the virtual image due to the residual multiple echo calculated by the processing of the depth calculation step is generated, the residual multiple echo virtual image generation suppression pulse repetition frequency that suppresses the generation of the virtual image due to the residual multiple echo is calculated. Residual multiple echo virtual image generation suppression pulse repetition frequency calculation step and ultrasonic transmission / reception Characterized in that to execute the pulse repetition and the pulse repetition frequency changing step changes the frequency to the computer at the time of.

  In the ultrasonic diagnostic apparatus of the present invention, ultrasonic image data having a predetermined pulse repetition frequency is transmitted and received, ultrasonic image data is generated from the received signal, and a plurality of ultrasonic waves generated by transmission and reception of ultrasonic waves having a plurality of different pulse repetition frequencies are generated. Based on the image data, it is determined whether or not a virtual image due to the residual multiple echo is generated, the depth at which the virtual image due to the residual multiple echo is generated is calculated, and a virtual image due to the calculated residual multiple echo is generated Based on the depth, a residual multiple echo virtual image generation suppression pulse repetition frequency, which is a pulse repetition frequency that suppresses generation of a virtual image due to residual multiple echoes, is calculated, and the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed.

  In the image processing method and image processing program of the ultrasonic diagnostic apparatus of the present invention, a virtual image is generated by residual multiple echoes based on a plurality of image data generated by scanning an ultrasonic wave having a plurality of different pulse repetition frequencies. The depth at which the virtual image due to the residual multiple echo is generated is calculated, and the generation of the virtual image due to the residual multiple echo is calculated based on the calculated depth at which the virtual image due to the residual multiple echo is generated. The residual multiple echo virtual image generation suppression pulse repetition frequency, which is the pulse repetition frequency to be suppressed, is calculated, and the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed.

  According to the present invention, the frame rate can be changed to a suitable frame rate depending on whether or not the virtual image is generated by the residual multiple echo while suppressing the generation of the virtual image by the residual multiple echo.

  Embodiments of the present invention will be described with reference to the drawings.

  FIG. 2 shows an internal configuration of the ultrasonic diagnostic apparatus 1 to which the present invention is applied.

  The ultrasonic diagnostic apparatus 1 includes a main body 11, an ultrasonic probe 12 connected to the main body 11 via an electric cable, an input unit 13, and a display unit 14.

  As shown in FIG. 2, the main body 11 of the ultrasonic diagnostic apparatus 1 includes a control unit 21, a transmission unit 22, a reception unit 23, an image data generation unit 24, a data storage unit 25, a calculation unit 26, and a residual multiple echo virtual image generation. A suppression unit 27 and a DSC (Digital Scan Converter) 28 are included.

  The control unit 21 includes a CPU (Central Processing Unit), an MPU (Micro Processing Unit), and the like, and generates various control signals and supplies them to the respective units to control the driving of the ultrasonic diagnostic apparatus 1 as a whole.

  The transmission unit 22 includes a rate pulse generator, a transmission delay circuit, and a pulsar (all not shown). The rate pulse generator is incident on the inside of the subject based on a control signal supplied from the control unit 21. A rate pulse for determining the pulse repetition frequency of the ultrasonic pulse to be generated is generated and supplied to the transmission delay circuit. The transmission delay circuit is a delay circuit for setting the convergence distance and the deflection angle of the ultrasonic beam at the time of transmission, and based on the control signal supplied from the control unit 21, the focus of the ultrasonic beam at the time of transmission. A delay time is added to the rate pulse supplied from the rate pulse generator so that the position and deflection angle become a predetermined focal position and deflection angle, and the pulse is supplied to the pulser. Furthermore, the pulser is a drive circuit that generates a high-pressure pulse for driving the ultrasonic transducer, and generates a high-voltage pulse for driving the ultrasonic transducer based on the rate pulse supplied from the transmission delay circuit. Then, the generated high-pressure pulse is output to the ultrasonic probe 12.

  The receiving unit 23 includes a preamplifier, a reception delay circuit, and an adder (all not shown), and the preamplifier acquires a reception signal based on the reflected wave of the ultrasonic pulse supplied from the ultrasonic probe 12 to the subject. Then, the acquired reception signal is amplified to a predetermined level, and the amplified reception signal is supplied to the reception delay circuit.

  Based on the control signal supplied from the control unit 21, the reception delay circuit delays the amplified reception signal supplied from the preamplifier corresponding to the difference in propagation time of ultrasonic waves from the focus position of each ultrasonic transducer. Give time and feed to adder. The adder adds the reception signals from the ultrasonic transducers supplied from the reception delay circuit, and supplies the added reception signal to the image data generation unit 24.

  The image data generation unit 24 includes a B mode processing unit 31 and a Doppler mode processing unit 32. The B-mode processing unit 31 includes a logarithmic amplifier, an envelope detection circuit, and a TGC (Time Gain Control) circuit (all not shown), and performs the following processing based on the control signal supplied from the control unit 21. Do.

  That is, the logarithmic amplifier of the B-mode processing unit 31 logarithmically amplifies the reception signal supplied from the reception unit 23 and supplies the logarithmically amplified reception signal to the envelope detection circuit. The envelope detection circuit is a circuit that detects only the amplitude by removing the ultrasonic frequency components, detects the envelope of the received signal supplied from the logarithmic amplifier, and supplies the detected received signal to the TGC circuit. To do. The TGC circuit adjusts the intensity of the received signal supplied from the envelope detection circuit so that the final image brightness is uniform, generates B-mode image data, and stores the generated B-mode image data as data To the unit 25.

  The data storage unit 25 acquires B-mode image data and Doppler mode image data supplied from the B-mode processing unit 31 and the Doppler mode processing unit 32, and stores the acquired B-mode image data and Doppler mode image data. Further, the data storage unit 25 supplies the stored B-mode image data and Doppler mode image data to the DSC 28 according to an instruction from the control unit 21 as necessary. Furthermore, the data storage part 25 memorize | stores the calculation result calculated in the calculating part 26, and supplies the memorize | stored calculation result to the display part 14 as needed.

  The data storage unit 25 stores the change result supplied from the pulse repetition frequency changing unit 36 of the residual multiple echo virtual image generation suppressing unit 27.

  The calculation unit 26 reads desired image data from a plurality of image data stored in the data storage unit 25, extracts feature points based on the read image data, and outputs the extraction result to the data storage unit. 25. In addition, the calculation unit 26 reads desired image data from the plurality of image data stored in the data storage unit 25, performs a tracking calculation of the feature points based on the read image data, and performs a tracking calculation result. Based on the above, various parameters in the diagnostic region of the subject are calculated, and the calculation results are supplied to the data storage unit 25.

  The residual multiple echo virtual image generation suppression unit 27 includes a residual multiple echo virtual image generation determination unit 33, a residual multiple echo virtual image generation depth / region calculation unit 34, a residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 35, and a pulse repetition frequency change unit. 36, the residual multiple echo virtual image generation determination unit 33 determines whether or not a residual multiple echo virtual image is generated based on the B-mode image data stored in the data storage unit 25, and determines the determination result. The residual multiple echo virtual image generation depth / region calculation unit 34 and the pulse repetition frequency change unit 36 are supplied.

  Based on the determination result supplied from the residual multiple echo virtual image generation determination unit 33, the residual multiple echo virtual image generation depth / region calculation unit 34 calculates the depth or region where the virtual image due to the residual multiple echo is generated, and the calculation result Is supplied to the residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 35 and the pulse repetition frequency change unit 36.

  The residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 35 is a pulse repetition frequency that suppresses the generation of a virtual image due to the residual multiple echo based on the calculation result supplied from the residual multiple echo virtual image generation depth / region calculation unit 34. The residual multiple echo virtual image generation suppression pulse repetition frequency is calculated, and the calculation result is supplied to the pulse repetition frequency changing unit 36.

  The pulse repetition frequency changing unit 36 is a pulse for transmitting and receiving ultrasonic waves based on the calculation results supplied from the residual multiple echo virtual image generation depth / region calculation unit 34 and the residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 35. The repetition frequency is changed to the calculated residual multiple echo virtual image generation suppression pulse repetition frequency or the highest pulse repetition frequency, and the change result is supplied to the data storage unit 25 and the control unit 21.

  The DSC 28 acquires the B-mode image data and the Doppler mode image data supplied from the data storage unit 25, and converts the acquired B-mode image data and the Doppler mode image data into a video format from the scanning line signal sequence of the ultrasonic scan. The signal is converted into a scanning line signal string and supplied to the display unit 14.

  The ultrasonic probe 12 is connected to the main body 11 via an electric cable, and is an ultrasonic transducer that transmits and receives ultrasonic waves by bringing the front surface into contact with the surface of the subject, and is arranged in a one-dimensional array. Alternatively, the ultrasonic transducers (not shown) arranged in a two-dimensional matrix array are provided at the tip portion. This ultrasonic transducer is an electroacoustic transducer as a piezoelectric transducer. The ultrasonic probe 12 converts an electric pulse input from the transmission unit 22 of the main body 11 into an ultrasonic pulse (transmission ultrasonic wave) during transmission, and converts a reflected wave reflected by the subject into an electric signal during reception. , Output to the main body 11.

  The input unit 13 is connected to the main body 11 via an electric cable, and instructs the operator to start a residual multiple echo virtual image generation suppression process (described later with reference to FIGS. 4 and 5) on the operation panel. In addition to the residual multiple echo virtual image generation suppression processing button, it has input devices such as a display panel, keyboard, trackball, and mouse for inputting various instructions of the operator, patient information, measurement parameters, physical parameters, It is used for an operator to input a template size, a time phase of an image used for image calculation, a lattice interval, and the like.

  The display unit 14 is connected to the DSC 28 of the main body 11 via a cable, and is provided with an unillustrated LCD (Liquid Crystal Display) and an unillustrated CRT (Cathode Ray Tube). The B-mode image data and Doppler mode image data from the DSC 28 converted from the video format to the scanning line signal sequence of the video format are acquired, and the acquired B-mode image data and Doppler mode image data are not shown on the LCD or the like. Display on the CRT.

  Next, the pulse repetition frequency setting process before residual multiple echo virtual image generation suppression in the ultrasonic diagnostic apparatus 1 of FIG. 2 will be described with reference to the flowchart of FIG.

  In step S <b> 1, the control unit 21 determines whether the display magnification of the image displayed on the display unit 14 is input by the operator operating the input unit 13, and the operator operates the input unit 13. It waits until it determines with the display magnification of the image displayed on the display part 14 having been input.

  When it is determined in step S1 that the display magnification of the image displayed on the display unit 14 has been input by operating the input unit 13 by the operator, the control unit 21 determines in step S2 the operator supplied from the input unit 13. Based on the image display magnification instruction signal corresponding to the instruction, the display depth corresponding to the image display magnification for transmitting and receiving the ultrasonic wave requested by the operator is calculated.

  In step S <b> 3, the control unit 21 determines a residual multiple echo that is a pulse repetition frequency when transmitting / receiving ultrasonic waves before the residual multiple echo virtual image generation suppression process based on the display depth calculation result calculated in the process of step S <b> 2. The pulse repetition frequency before virtual image generation suppression processing is calculated according to a preset ratio. That is, the pulse repetition frequency before the residual multiple echo virtual image generation suppressing process is set to the display depth (hereinafter referred to as “set display depth”) of the B-mode tomographic image required by the operator in order to somewhat suppress the generation of virtual images due to the residual multiple echo. A fixed value is set in advance so as to be a predetermined value lower than the corresponding maximum pulse repetition frequency (pulse repetition frequency obtained from [Expression 2]), and the set fixed value is calculated.

  In step S4, the control unit 21 sets the pulse repetition frequency when transmitting and receiving the ultrasonic wave to the calculated pulse repetition frequency before the residual multiple echo virtual image generation suppression process. Thus, before the residual multiple echo virtual image generation suppression process (described later with reference to FIGS. 4 and 5) is performed, the residual multiple echo virtual image generation lower than the maximum pulse repetition frequency corresponding to the set display depth by a predetermined value. Ultrasonic waves are transmitted and received at the pulse repetition frequency before the suppression process. As described above, since there are regions where virtual images due to residual multiple echoes are likely to occur and regions where virtual images due to residual multiple echoes are difficult to occur, even if a predetermined value lower than the maximum pulse repetition frequency is set, Depending on the region where the sound waves are scanned, a virtual image due to residual multiple echoes may occur.

  The control unit 21 supplies the data storage unit 25 with the pulse repetition frequency data before the residual multiple echo virtual image generation suppression process, which is the set data of the pulse repetition frequency before the residual multiple echo virtual image generation suppression process.

  In step S5, the data storage unit 25 acquires the pulse repetition frequency data before the residual multiple echo virtual image generation suppression process supplied from the control unit 21, and stores the acquired pulse repetition frequency data before the residual multiple echo virtual image generation suppression process. To do.

  In step S6, the control unit 21 generates a pulse repetition frequency setting control signal before the residual multiple echo virtual image generation suppression process based on the pulse repetition frequency before the residual multiple echo virtual image generation suppression process set in the process of step S4, This is supplied to the transmission unit 22.

  Thereafter, in the rate pulse generator (not shown) of the transmission / reception unit 22, the light enters the subject based on the pulse repetition frequency setting control signal before residual multiple echo virtual image generation suppression processing supplied from the control unit 21. A rate pulse is generated that determines the pulse repetition frequency of the ultrasonic pulse as a pulse repetition frequency before the residual multiple echo virtual image generation suppression processing that is a predetermined value lower than the maximum pulse repetition frequency corresponding to the set display depth. After this setting process, the tip of the ultrasonic probe 12 (ultrasonic transmission / reception surface) is fixed at a predetermined position on the body surface of the subject by the operator, and the set pulse repetition frequency before the residual multiple echo virtual image generation suppression process is set. Generation of image data in a predetermined time phase is started by transmission and reception of sound waves.

  A residual multiple echo virtual image generation suppression process in the ultrasonic diagnostic apparatus 1 in FIG. 2 will be described with reference to the flowcharts in FIGS. 4 and 5. This processing is performed when a virtual image due to residual multiple echo has already occurred in image data generated by transmission / reception of ultrasonic waves having a pulse repetition frequency set by the pulse repetition frequency setting processing before the suppression of residual multiple echo virtual image generation, or When the operator predicts that a virtual image due to the residual multiple echo is likely to be generated, the operator operates the button for suppressing the generation of the residual multiple echo virtual image.

  In step S <b> 11, the control unit 21 determines whether or not an instruction to start the residual multiple echo virtual image generation suppression process has been given by the operator operating a residual multiple echo virtual image generation suppression button (not shown) of the input unit 13. The process waits until it is determined that an instruction to start the residual multiple echo virtual image generation suppression process has been issued.

  When it is determined in step S11 that an instruction to start the residual multiple echo virtual image generation suppression process has been issued, the control unit 21 generates a first ultrasonic transmission control signal and a first ultrasonic reception control signal in step S12. The data are supplied to the transmission unit 22 and the reception unit 23, respectively. Here, the first ultrasonic transmission control signal includes ultrasonic waves at the maximum pulse repetition frequency corresponding to the set display depth calculated based on the display magnification of the image input by the operator operating the input unit 13. A control signal for transmission is included, and the first ultrasonic reception control signal has a set display depth calculated based on the display magnification of the image input by the operator operating the input unit 13. A control signal for receiving an ultrasonic wave at the highest pulse repetition frequency according to the frequency is included.

  In step S <b> 13, the transmission unit 22 transmits an ultrasonic beam to the subject based on the first ultrasonic transmission control signal supplied from the control unit 21. That is, the rate pulse device of the transmission unit 22 has the pulse repetition frequency of the ultrasonic pulse incident on the inside of the subject according to the set display depth based on the first ultrasonic transmission control signal supplied from the control unit 21. A rate pulse that is determined to be the highest pulse repetition frequency is generated and supplied to the transmission delay circuit. Also, the transmission delay circuit has a predetermined focal position and deflection angle (θ1) based on the first ultrasonic transmission control signal supplied from the control unit 21 so that the focal position and deflection angle of the ultrasonic beam at the time of transmission. As described above, the delay time is added to the rate pulse supplied from the rate pulse generator, and the pulse is supplied to the pulser. Further, the pulser generates a high-pressure pulse for driving the ultrasonic transducer based on the rate pulse supplied from the transmission delay circuit, and outputs the generated high-pressure pulse to the ultrasonic probe 12. The ultrasonic probe 12 converts the high-pressure pulse (electric pulse) input from the transmission unit 22 into an ultrasonic pulse, and transmits the converted ultrasonic pulse to the subject. A part of the ultrasonic wave transmitted into the subject is reflected at the boundary surface or tissue between organs in the subject having different acoustic impedances.

  In step S <b> 14, the ultrasonic probe 12 converts the reflected wave reflected by the subject into an electric signal and outputs it to the main body 11. In step S15, the reception unit 23 amplifies the reception signal input from the ultrasonic probe 12 based on the first ultrasonic reception control signal supplied from the control unit 21, adds a predetermined delay time, This is supplied to the image data generation unit 24. That is, the preamplifier of the reception unit 23 acquires a reception signal based on the reflected wave of the ultrasonic wave input to the subject from the ultrasonic probe 12, amplifies the acquired reception signal to a predetermined level, and receives the amplified reception signal. The signal is supplied to the reception delay circuit.

  Based on the first ultrasonic reception control signal supplied from the control unit 21, the reception delay circuit of the reception unit 23 converts the ultrasonic wave from the focus position of each ultrasonic transducer to the amplified reception signal supplied from the preamplifier. A delay time corresponding to the difference in propagation time is given and supplied to the adder. The adder adds the reception signals from the ultrasonic transducers supplied from the reception delay circuit, and supplies the added reception signal to the image data generation unit 24.

  In step S <b> 16, the B mode processing unit 31 and the Doppler mode processing unit 32 of the image data generation unit 24 perform various processes on the reception signal supplied from the reception unit 23, and the first B mode image data in the θ <b> 1 direction and the first Doppler mode image data is generated, and the generated first B-mode image data and first Doppler mode image data in the θ1 direction are supplied to the data storage unit 25.

  In step S17, the data storage unit 25 acquires the first B-mode image data and the first Doppler mode image data in the θ1 direction supplied from the B-mode processing unit 31 and the Doppler mode processing unit 32 of the image data generation unit 24, The acquired first B-mode image data and first Doppler mode image data in the θ1 direction are stored.

  Next, the ultrasonic wave transmission / reception direction is sequentially updated by Δθ while changing to θ1 + (N−1) Δθ, and ultrasonic wave transmission / reception is performed in the same procedure as above by scanning in the N direction, and the inside of the subject is scanned in real time. To do. At this time, the control unit 21 sequentially switches the delay times of the transmission delay circuit of the transmission unit 22 and the reception delay circuit of the reception unit 23 according to the control signal in accordance with a predetermined ultrasonic transmission / reception direction, while θ1 + Δθ to θ1 +. (N-1) First B mode image data and first Doppler mode image data in the Δθ direction are generated.

  In addition, the data storage unit 25 generates the first B mode image data and the first Doppler mode image data in the θ1 + Δθ to θ1 + (N−1) Δθ directions and the first B mode image data in the θ1 direction that is already stored. Along with the first Doppler mode image data, two-dimensional first B mode image data and first Doppler mode image data of a predetermined time phase are stored.

  For example, as shown in FIG. 6A, the data storage unit 25 stores the maximum according to the set display depth calculated based on the display magnification of the image input by the operator operating the input unit 13. Two-dimensional first B-mode image data of a predetermined time phase when ultrasonic waves are transmitted at a pulse repetition frequency is stored.

  In the case of the example shown in FIG. 6A, the ultrasonic wave is generated at the highest pulse repetition frequency corresponding to the set display depth calculated based on the display magnification of the image input by the operator operating the input unit 13. Because it has been transmitted, it receives a signal that is a mixture of the reflected signal from a region deeper than the set display depth of the already transmitted ultrasound and the reflected signal from a short distance that is shallower than the set display depth of the new ultrasound. Therefore, a virtual image due to residual multiple echoes is likely to occur. In particular, when there is a strong reflector that reflects ultrasonic waves deep in the body of the subject, or when an operator diagnoses the heart of the subject, the ultrasound is sufficiently attenuated in the body of the subject. It is not possible to easily generate a virtual image due to residual multiple echo. In the case of the example shown in FIG. 6A, a tomographic image g and a tomographic image h, which are virtual images due to residual multiple echoes, are displayed near the upper part of the tomographic image i.

  In step S18, the control unit 21 generates a second ultrasonic transmission control signal and a second ultrasonic reception control signal, and supplies them to the transmission unit 22 and the reception unit 23, respectively. Here, in the second ultrasonic transmission control signal, ½ of the maximum pulse repetition frequency corresponding to the set display depth calculated based on the display magnification of the image input by the operator operating the input unit 13. A control signal for transmitting an ultrasonic wave at a double pulse repetition frequency (a pulse repetition frequency sufficiently lower than the maximum pulse repetition frequency) is included, and an operator inputs an input unit to the second ultrasonic reception control signal 13 is a pulse repetition frequency that is 1/2 times the maximum pulse repetition frequency corresponding to the set display depth calculated based on the display magnification of the image input by operating 13 (pulse repetition frequency sufficiently lower than the maximum pulse repetition frequency) A control signal for receiving an ultrasonic wave at a frequency) is included. In addition, when ultrasonic waves are transmitted and received at a pulse repetition frequency that is 1/2 times the maximum pulse repetition frequency, it is twice as high as images generated when ultrasonic waves are transmitted and received at the highest pulse repetition frequency. Images up to depth are generated.

  In addition, the second ultrasonic transmission control signal and the second ultrasonic reception control signal include a pulse repetition frequency that is 1/2 times or less of the maximum pulse repetition frequency (for example, a pulse repetition frequency that is 倍 times the maximum pulse repetition frequency, etc.) ) May include a control signal for transmitting and receiving ultrasonic waves.

  In step S19, the transmission unit 22 transmits an ultrasonic beam to the subject based on the second ultrasonic transmission control signal supplied from the control unit 21. That is, the rate pulse device of the transmission unit 22 has the pulse repetition frequency of the ultrasonic pulse incident on the inside of the subject according to the set display depth based on the first ultrasonic transmission control signal supplied from the control unit 21. A rate pulse that is determined to be a pulse repetition frequency that is 1/2 times the maximum pulse repetition frequency is generated and supplied to the transmission delay circuit.

  Further, the transmission delay circuit, based on the second ultrasonic transmission control signal supplied from the control unit 21, makes the focal position and deflection angle of the ultrasonic beam at the time of transmission the predetermined focal position and deflection angle (θ1). As described above, the delay time is added to the rate pulse supplied from the rate pulse generator, and the pulse is supplied to the pulser. The pulser generates a high-pressure pulse for driving the ultrasonic transducer based on the rate pulse supplied from the transmission delay circuit, and outputs the generated high-pressure pulse to the ultrasonic probe 12. The ultrasonic probe 12 converts the high-pressure pulse (electric pulse) input from the transmission unit 22 into an ultrasonic pulse, and transmits the converted ultrasonic pulse to the subject. A part of the ultrasonic wave transmitted into the subject is reflected at the boundary surface or tissue between organs in the subject having different acoustic impedances.

  In step S <b> 20, the ultrasonic probe 12 converts the reflected wave reflected by the subject into an electrical signal and outputs it to the main body 11. In step S21, the reception unit 23 amplifies the reception signal based on the reflected wave of the ultrasonic wave input from the ultrasonic probe 12 based on the second ultrasonic wave reception control signal supplied from the control unit 21, A delay time is added and supplied to the image data generation unit 24. That is, the preamplifier of the reception unit 23 acquires a reception signal based on the reflected wave of the ultrasonic wave input to the subject from the ultrasonic probe 12, amplifies the acquired reception signal to a predetermined level, and receives the amplified reception signal. The signal is supplied to the reception delay circuit.

  Based on the second ultrasonic reception control signal supplied from the control unit 21, the reception delay circuit of the reception unit 23 converts the ultrasonic wave from the focus position of each ultrasonic transducer to the amplified reception signal supplied from the preamplifier. A delay time corresponding to the difference in propagation time is given and supplied to the adder. The adder adds the reception signals from the ultrasonic transducers supplied from the reception delay circuit, and supplies the added reception signal to the image data generation unit 24.

  In step S <b> 22, the B mode processing unit 31 and the Doppler mode processing unit 32 of the image data generation unit 24 perform various processes on the reception signal supplied from the reception unit 23, and the second B mode image data in the θ <b> 1 direction and the second Doppler mode image data is generated, and the generated second B-mode image data and second Doppler mode image data in the θ1 direction are supplied to the data storage unit 25.

  In step S23, the data storage unit 25 acquires the second B-mode image data and the second Doppler mode image data in the θ1 direction supplied from the B-mode processing unit 31 and the Doppler mode processing unit 32 of the image data generation unit 24, The acquired second B-mode image data and second Doppler mode image data in the θ1 direction are stored.

  Next, the ultrasonic wave transmission / reception direction is sequentially updated by Δθ while changing to θ1 + (N−1) Δθ, and ultrasonic wave transmission / reception is performed in the same procedure as above by scanning in the N direction, and the inside of the subject is scanned in real time. To do. At this time, the control unit 21 sequentially switches the delay times of the transmission delay circuit of the transmission unit 22 and the reception delay circuit of the reception unit 23 according to the control signal in accordance with a predetermined ultrasonic transmission / reception direction, while θ1 + Δθ to θ1 +. (N-1) Each of the second B-mode image data and the second Doppler mode image data in the Δθ direction is generated. Further, the data storage unit 25 generates the generated second B mode image data and second Doppler mode image data in the θ1 + Δθ to θ1 + (N−1) Δθ directions, and the already stored second B mode image data in the θ1 direction. Along with the second Doppler mode image data, two-dimensional second B mode image data and second Doppler mode image data of a predetermined time phase are stored.

  For example, as shown in FIG. 6B, the data storage unit 25 stores the maximum according to the set display depth calculated based on the display magnification of the image input by the operator operating the input unit 13. Two-dimensional second B mode image data of a predetermined time phase when ultrasonic waves are transmitted at a pulse repetition frequency that is 1/2 times the pulse repetition frequency is stored.

  In the case of the example shown in FIG. 6B, 1/2 of the maximum pulse repetition frequency corresponding to the set display depth calculated based on the display magnification of the image input by the operator operating the input unit 13. Since the ultrasonic waves are transmitted at the double pulse repetition frequency, the ultrasonic waves are sufficiently attenuated in the body of the subject, and a virtual image due to residual multiple echoes is unlikely to occur. In the case of the example shown in FIG. 6B, in the case of the example shown in FIG. 6A, the tomographic image g and the tomographic image that have been displayed near the top of the tomographic image i as a virtual image due to residual multiple echoes. The tomographic image k and the tomographic image l corresponding to h are displayed at the original correct depth / area deeper than the set display depth, and a virtual image due to residual multiple echoes is not generated.

  In step S24, the residual multiple echo virtual image generation determination unit 33 of the residual multiple echo virtual image generation suppression unit 27 performs the first B mode image data (FIG. 6A) and the second B mode image data stored in the data storage unit 25. (FIG. 6 [B]) is read out. In step S25, the residual multiple echo virtual image generation determination unit 33 calculates a difference between the two images based on the read first B-mode image data and second B-mode image data. That is, based on the second B mode image data of FIG. 6B, the image is cut out to the set display depth preset by the operator, and compared with the first B mode image data of FIG. The difference in luminance information is taken.

  Here, two parts can be considered as the difference extracted from the luminance information of the two images. For one thing, the two images are not images generated by scanning ultrasound at exactly the same time phase, and there is a slight time difference. For example, the subject moves during the time difference. The ultrasonic scanning area may move slightly, and in such a case, there may be a difference between the luminance information of the two images. Second, since the pulse repetition frequency when transmitting and receiving ultrasonic waves differs greatly between two images, two images are generated when a virtual image due to residual multiple echoes is generated only in one image. There may be a difference in luminance information.

  The brightness of the virtual image due to the residual multiple echo is generally relatively higher than the brightness of the surrounding image, particularly in the case where there is a strong reflector that strongly reflects ultrasonic waves deep inside the body of the subject. Despite being attenuated in the body of the subject, it is received as an ultrasonic reflected signal, and therefore tends to be higher than the brightness of the surrounding image. Accordingly, in the case where a virtual image due to residual multiple echo is generated among the two parts extracted as the difference between the luminance information of the images (the latter), the difference extracted from the luminance information of the two images becomes large. . On the other hand, when the ultrasound scanning area slightly moves due to the body movement of the subject (the former), the scanning area moves slightly, so that it is extracted from the luminance information of the two images. The difference is small.

  For example, when the difference between the two images is obtained based on the first B mode image data and the second B mode image data of FIGS. 6A and 6B, a difference image as shown in FIG. 7 is obtained. In the case of the example of FIG. 7, the tomographic image m and the tomographic image n of the difference image take the difference in luminance information between the image of FIG. 6A and the image of FIG. It is an image corresponding to the tomographic image g and the tomographic image h.

  Therefore, when a difference between two images is taken, a threshold value (reference value) of a luminance difference that is extracted as a luminance information difference when a virtual image due to residual multiple echo is generated in one image is set in advance. By doing so, it can be determined whether or not a virtual image due to residual multiple echo has occurred.

  When the difference between the two images is taken, the portion displayed at the correct depth and position without forming a virtual image due to residual multiple echoes (the tomographic image i in FIG. 6A and the tomographic image in FIG. 6B) Since j) has almost no difference as luminance information, it is canceled out and is not extracted as a difference from the luminance information of two images.

  In step S <b> 26, the residual multiple echo virtual image generation determination unit 33 determines whether the difference image (FIG. 7) includes a portion having a luminance difference larger than a predetermined reference value set in advance.

  If it is determined in step S26 that the difference image has a portion having a luminance difference larger than a predetermined reference value set in advance, the residual multiple echo virtual image generation determination unit 33 determines in step S27 the predetermined diagnosis currently being diagnosed by the operator. It is determined that a virtual image due to residual multiple echo has occurred at the site, and based on the determination result, an indication to the effect that a virtual image due to residual multiple echo has occurred at the predetermined site currently being diagnosed by the operator is displayed. This is supplied to the echo virtual image generation depth / region calculation unit 34. Further, the residual multiple echo virtual image generation determination unit 33 supplies a difference image between the first B mode image data and the second B mode image data to the residual multiple echo virtual image generation depth / region calculation unit 34.

  In step S <b> 28, the residual multiple echo virtual image generation depth / region calculation unit 34 acquires a difference image between the first B mode image data and the second B mode image data supplied from the residual multiple echo virtual image generation determination unit 33, and the residual multiple echo In accordance with the instruction that the virtual image is generated by the residual multiple echo supplied from the virtual image generation determination unit 33, the virtual image by the residual multiple echo is obtained based on the acquired difference image between the first B mode image data and the second B mode image data. Calculate the maximum depth at which. Specifically, as shown in FIG. 7, the maximum depth D from the body surface of the subject of the tomographic image n corresponding to the virtual image by the residual multiple echo existing in the difference image is calculated.

Here, as shown in FIG. 6 [B] and Figure 6 [A], and the distance D _A to the tomographic image h displayed on the deepest as a virtual image by residual multiple echoes from the body surface of the subject, distance D _B to the tomographic image l that is displayed from the setting display depth in the correct depth and location generally exhibit almost the same value.

Further, since the difference image in FIG. 7 is the difference between the images in FIG. 6A and FIG. 6B, the tomographic image h displayed at the deepest place as a virtual image by residual multiple echoes from the body surface of the subject. until the distance D _a of shows the same value as the maximum depth D from the body surface of a subject whose tomographic image n corresponding to the virtual image by residual multiple echo present in the difference image. Therefore, by calculating the maximum depth D from the body surface of the subject of the tomographic image n corresponding to the virtual image due to the residual multiple echoes existing in the difference image, the tomographic image l in FIG. It is possible to calculate the residual multiple echo virtual image generation suppression display depth that suppresses the generation of virtual images due to residual multiple echoes as (set display depth + maximum depth D of the tomographic image n from the body surface of the subject). The pulse repetition frequency corresponding to the calculated residual multiple echo virtual image generation suppression display depth can be calculated.

  The residual multiple echo virtual image generation depth / region calculation unit 34 converts the residual multiple echo virtual image generation maximum depth data, which is data of the maximum depth at which the calculated virtual image is generated by the residual multiple echo, into the residual multiple echo virtual image generation suppression pulse repetition frequency. It supplies to the calculation part 35.

In step S29, the residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 35 receives the portion requested by the operator based on the residual multiple echo virtual image generation depth / region calculation unit 34 supplied from the residual multiple echo virtual image generation depth / region calculation unit 34. The residual multiple echo virtual image generation suppression pulse repetition frequency for suppressing the generation of the virtual image due to the residual multiple echo is calculated according to [Equation 3].
[Equation 3]
Residual multiple echo virtual image generation suppression pulse repetition frequency = maximum pulse repetition frequency− {propagating sound speed / (maximum depth at which virtual image due to residual multiple echo is generated + α)}

  In general, when there is a strong reflector that strongly reflects ultrasonic waves deep inside the body of the subject, the depth and position of the virtual image due to the generated residual multiple echoes are almost the same. Some deviation occurs due to changes in the diagnostic environment such as movement and the position of contact of the ultrasonic probe. If the last pulse repetition frequency at which the tomographic image 1 in FIG. 6B is displayed at the correct depth and position is calculated as the residual multiple echo virtual image suppression pulse repetition frequency, the body motion and super A virtual image due to residual multiple echoes may or may not be displayed on the screen due to changes in the diagnostic environment such as the position where the acoustic probe contacts. This is a hindrance when the operator makes a diagnosis.

  Therefore, in [Equation 3], the margin coefficient α is added to the maximum depth D where the virtual image due to the residual multiple echo is generated in order to ensure suppression of the generation of the virtual image due to the residual multiple echo at the part requested by the operator. Like that. As a result, as shown in FIG. 8, even if the display depth and position of a tomographic image that is displayed as a virtual image due to residual multiple echoes are slightly shifted, generation of virtual images due to residual multiple echoes can be suppressed. it can. Therefore, it is possible to prevent a virtual image due to a sudden residual multiple echo caused by a change in the diagnostic environment such as the body movement of the subject or the position of contact with the ultrasonic probe from being displayed on the screen.

  The residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 35 supplies the residual multiple echo virtual image generation suppression pulse repetition frequency data, which is data of the calculated residual multiple echo virtual image generation suppression pulse repetition frequency, to the pulse repetition frequency change unit 36. .

  In step S30, the pulse repetition frequency changing unit 36 acquires the residual multiple echo virtual image generation suppression pulse repetition frequency data supplied from the residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 35, and acquires the acquired residual multiple echo virtual image generation. Based on the suppression pulse repetition frequency data, the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed to the residual multiple echo virtual image generation suppression pulse repetition frequency.

  When it is determined in step S26 that the difference image does not have a luminance difference portion larger than a predetermined reference value set in advance, the residual multiple echo virtual image generation determination unit 33 determines in step S31 a predetermined diagnosis currently diagnosed by the operator. It is determined that a virtual image due to residual multiple echo has not occurred in the part, and based on the determination result, an instruction that a virtual image due to residual multiple echo has not occurred in a predetermined part currently diagnosed by the operator is repeatedly pulsed This is supplied to the frequency changing unit 36.

  In step S32, the pulse repetition frequency changing unit 36 is stored in the data storage unit 25 in accordance with the instruction that the virtual image due to the residual multiple echo generated from the residual multiple echo virtual image generation determination unit 33 is not generated. Reads the maximum pulse repetition frequency data corresponding to the display depth input by operating the input unit 13, and based on the read maximum pulse repetition frequency data, determines the pulse repetition frequency when ultrasonic waves are transmitted and received. Change to the highest pulse repetition frequency. Thereby, when the virtual image by a residual multiple echo does not generate | occur | produce, the pulse repetition frequency when transmitting / receiving an ultrasonic wave can be changed to the highest pulse repetition frequency in setting display depth. Therefore, an unnecessary decrease in the frame rate can be suppressed, and the frame rate can be changed to a suitable frame rate depending on whether or not the virtual image is generated by the residual multiple echo.

  In addition, when a virtual image due to residual multiple echo does not occur, the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed to the maximum pulse repetition frequency at the set display depth, but of course at a frequency lower than the maximum pulse repetition frequency. Therefore, the frequency may be changed to a frequency higher than the repetition frequency of the residual multiple echo virtual image generation suppression pulse.

  In step S <b> 33, the pulse repetition frequency changing unit 36 supplies pulse repetition frequency data, which is data of the set pulse repetition frequency, to the data storage unit 25 and the control unit 21. The data storage unit 25 acquires the pulse repetition frequency data supplied from the pulse repetition frequency changing unit 36 and stores the acquired pulse repetition frequency data.

  In step S <b> 34, the control unit 21 generates a pulse repetition frequency change control signal based on the pulse repetition frequency data supplied from the pulse repetition frequency change unit 36 and supplies the pulse repetition frequency change control signal to the transmission unit 22.

  Thereafter, in the rate pulse generator (not shown) of the transmission / reception unit 22, the pulse repetition frequency of the ultrasonic pulse incident on the inside of the subject is determined based on the pulse repetition frequency change control signal supplied from the control unit 21. The rate pulse that is determined to be the residual multiple echo virtual image generation suppression pulse repetition frequency (maximum pulse repetition frequency when no virtual image due to residual multiple echo has occurred) that suppresses the generation of virtual images due to residual multiple echoes at the site requested by the operator. Generated.

  After this change processing, the operator fixes the tip of the ultrasonic probe 12 (ultrasonic transmission / reception surface) to a predetermined position on the body surface of the subject, and changes the residual multiple echo virtual image generation suppression pulse repetition frequency (residual multiple echo). If no virtual image is generated, ultrasonic waves can be transmitted and received at the highest pulse repetition frequency. Accordingly, the frame rate can be changed to a suitable frame rate depending on whether or not the virtual image is generated by the residual multiple echo while suppressing the generation of the virtual image by the residual multiple echo.

  In the ultrasonic diagnostic apparatus 1 shown in the embodiment of the present invention, a virtual image due to a residual multiple echo has already occurred in the generated image data, or an operator is likely to generate a virtual image due to a residual multiple echo. When it is predicted, the operator starts the operation by operating the residual multiple echo virtual image generation suppression button. Thus, the operator can not only start the residual multiple echo virtual image generation suppressing process so as to suit the diagnosis, but also, for example, when the ultrasonic probe 12 is frequently moved to scan a wide range (that is, the scanning target is clearly shown). When scanning a range from a different liver to the kidney or bladder, the frame rate changes intermittently and improperly due to a virtual image due to a residual multiple echo suddenly generated by body movement of the subject. This can be suppressed. Of course, the residual multiple echo virtual image generation suppression processing may be performed constantly.

  By the way, in the residual multiple echo virtual image generation suppression processing described with reference to the flowcharts of FIGS. 4 and 5, the virtual image due to the residual multiple echo can be reliably suppressed, but the frame rate may be extremely reduced. . Therefore, only the scanning line related to the region determined to have a virtual image due to the residual multiple echo in the difference image (FIG. 7) is changed to the residual multiple echo virtual image generation suppression pulse repetition frequency when transmitting and receiving ultrasonic waves, and the other regions are related. In the scanning line, the maximum pulse repetition frequency may be changed as the pulse repetition frequency when transmitting and receiving ultrasonic waves. The residual multiple echo virtual image generation suppression processing in this case is shown in the flowcharts of FIGS.

  With reference to the flowcharts of FIGS. 9 and 10, another residual multiple echo virtual image generation suppression process in the ultrasonic diagnostic apparatus of FIG. 2 will be described. 9 and 10 are the same as steps S11 to S29 and steps S31 to S34 in FIGS. 4 and 5, and the description thereof will be repeated. It will be omitted.

  In step S60, the residual multiple echo virtual image generation depth / region calculation unit 34 is a region where a virtual image due to the residual multiple echo is generated based on the acquired difference image between the first B-mode image data and the second B-mode image data. A certain residual multiple echo virtual image generation region is calculated. In the case of the example in FIG. 7, the tomographic image n and the tomographic image m corresponding to the virtual image by the residual multiple echo exist in the residual multiple echo virtual image generation region M.

  The residual multiple echo virtual image generation depth / region calculation unit 34 supplies the residual multiple echo virtual image generation region data, which is data of the calculated residual multiple echo virtual image generation region, to the pulse repetition frequency changing unit 36.

  In step S <b> 61, the pulse repetition frequency changing unit 36 supplies the residual multiple echo virtual image generation region data supplied from the residual multiple echo virtual image generation depth / region calculation unit 34 and the residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 35. The residual multiple echo virtual image generation suppression pulse repetition frequency data is acquired, and based on the acquired residual multiple echo virtual image generation area data and residual multiple echo virtual image generation suppression pulse repetition frequency data, a virtual image is generated by the residual multiple echo. In the scanning line related to the region where the ultrasonic wave is transmitted and received, the pulse repetition frequency is changed to the residual multiple echo virtual image generation suppression pulse repetition frequency, and in the scanning line not related to the region where the virtual image due to the residual multiple echo is generated, The pulse repetition frequency when transmitting and receiving sound waves To change the maximum pulse repetition frequency.

  Specifically, as shown in FIG. 11, in the scanning line related to the residual multiple echo virtual image generation region M, the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed to the residual multiple echo virtual image generation suppression pulse repetition frequency. In the scanning line related to the region other than the residual multiple echo virtual image generation region M, the pulse repetition frequency when transmitting / receiving ultrasonic waves is changed to the maximum pulse repetition frequency.

  As a result, when it is determined that a virtual image due to residual multiple echo is generated, it is possible to suppress a decrease in the frame rate as compared with changing to the residual multiple echo virtual image generation suppression pulse repetition frequency for the scanning lines for the entire region. . Accordingly, it is possible to further change the frame rate to a suitable frame rate depending on whether or not the region is a region where the residual multiple echo virtual image is generated while suppressing the generation of the virtual image due to the residual multiple echo.

  In the ultrasonic diagnostic apparatus 1 shown in the embodiment of the present invention, when it is determined that a virtual image due to residual multiple echo is generated, the pulse repetition frequency when transmitting and receiving ultrasonic waves is set as the residual multiple echo. Although the virtual image generation suppression pulse repetition frequency is changed, the area occupied by the virtual image due to the residual multiple echo is calculated in the entire display screen to be displayed, and the area occupied by the calculated virtual image due to the residual multiple echo is calculated from a predetermined ratio. Only when the residual multiple echo virtual image generation suppression pulse repetition frequency is calculated, and the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed to the calculated residual multiple echo virtual image generation suppression pulse repetition frequency. Good. The residual multiple echo virtual image generation suppression processing in this case is shown in FIGS.

  With reference to the flowcharts of FIGS. 12 and 13, another residual multiple echo virtual image generation suppression process in the ultrasonic diagnostic apparatus 1 of FIG. 2 will be described. 13 are the same as steps S11 to S26 and steps S27 to S34 in FIGS. 4 and 5, and the description thereof is repeated. Omitted.

  When it is determined in step S89 that the difference image has a portion having a luminance difference larger than a predetermined reference value set in advance, the residual multiple echo virtual image generation depth / region calculation unit 35 generates a virtual image due to the generated residual multiple echo. Calculates the area ratio of the residual multiple echo virtual image generation area, which is the ratio of the area of the entire display image (difference image). In the case of the example in FIG. 7, the residual multiple echo virtual image generation region area ratio that is the ratio of the area area occupied by the tomographic image n and the tomographic image m is calculated in the entire difference image.

  In step S89, the residual multiple echo virtual image generation depth / region calculation unit 35 determines whether or not the calculated residual multiple echo virtual image generation region area ratio is greater than a predetermined reference value.

  If it is determined that the residual multiple echo virtual image generation area area ratio calculated in step S89 is larger than a predetermined reference value set in advance, the process proceeds to step S91, and the residual multiple echo virtual image generation suppression pulse repetition frequency is calculated. The

  When it is determined that the area ratio of the residual multiple echo virtual image generation area calculated in step S89 is not larger than a predetermined reference value set in advance (that is, the area occupied by the generated virtual image due to the residual multiple echo in the entire display image When it is determined that the area ratio is smaller than the predetermined reference value), the pulse repetition frequency changing unit 36 is the residual multiple echo virtual image generation area area ratio supplied from the residual multiple echo depth / area calculation unit 34 in step S97. The maximum pulse repetition frequency data stored in the data storage unit 25 is read in accordance with an instruction indicating that is not greater than a predetermined reference value set in advance, and based on the read maximum pulse repetition frequency data, The pulse repetition frequency when transmitting and receiving sound waves is changed to the highest pulse repetition frequency.

  As a result, even if a virtual image due to the residual multiple echo is generated, the virtual image due to the residual multiple echo generated is very small. If there is no significant problem (if there is no need for residual multiple echo virtual image generation suppression processing), the pulse repetition frequency when transmitting and receiving ultrasonic waves is set to the residual multiple echo virtual image generation suppression pulse that suppresses the generation of virtual images due to residual multiple echoes. Since the frequency is not changed to the repetition frequency, it is possible to suppress the frame rate from being lowered unnecessarily.

  If it is determined that the calculated residual multiple echo virtual image generation area area ratio is not greater than a predetermined reference value set in advance, the residual multiple echo virtual image generation suppression process may be canceled.

  Moreover, in the ultrasonic diagnostic apparatus 1 shown in the embodiment of the present invention, whether or not a virtual image due to residual multiple echoes has occurred is determined based on a predetermined reference value in which a luminance difference is set in advance based on the difference image. For example, the average luminance information of the difference image is calculated, and the generated virtual image is distinguished from the other images based on the calculated average luminance information of the difference image. The predetermined reference value that can be changed may be changed. In addition, the predetermined reference value that can distinguish the generated virtual image from the other images is changed based on the luminance dispersion information in the difference image, and is greatly increased based on the luminance dispersion information in the difference image. It may be determined whether or not a virtual image due to residual multiple echo is generated depending on whether or not there is a part that is off. Of course, other methods may be used to determine whether or not a virtual image due to residual multiple echo has occurred based on a difference image or the like.

  Furthermore, in the ultrasonic diagnostic apparatus 1 shown in the embodiment of the present invention, the two-dimensional tomographic image is used. However, for example, the ultrasonic diagnostic apparatus 1 may be used for a three-dimensional tomographic image.

  In the ultrasonic diagnostic apparatus 1 shown in the embodiment of the present invention, the B-mode tomographic image display mode is applied. However, the ultrasonic diagnostic apparatus 1 is also applied to, for example, a simultaneous mode with a color Doppler mode or a pulse Doppler mode. be able to.

  Furthermore, in the ultrasonic diagnostic apparatus 1 shown in the embodiment of the present invention, based on the calculated residual multiple echo virtual image generation suppression pulse repetition frequency, the pulse repetition frequency when transmitting and receiving ultrasonic waves is determined as the residual multiple echo. The virtual image generation suppression pulse repetition frequency is changed to, for example, the calculated residual multiple echo virtual image generation suppression pulse repetition frequency is displayed on the display unit 14 and the displayed residual multiple echo virtual image generation suppression pulse repetition frequency is displayed. Based on the above, the operator inputs a predetermined pulse repetition frequency by operating the input unit 13, and changes the pulse repetition frequency when transmitting / receiving ultrasonic waves to the input predetermined pulse repetition frequency. Also good. As a result, the frame rate can be changed to a more suitable frame for the user depending on whether or not the virtual image is generated.

  In the embodiment of the present invention, the steps of the flowchart show examples of processing performed in time series in the described order. However, even if they are not necessarily processed in time series, they are performed in parallel or individually. The process to be executed is also included.

The conceptual diagram explaining the concept of generation | occurrence | production of the virtual image by a residual multiple echo. The block diagram which shows the internal structure of the ultrasonic diagnosing device to which this invention is applied. The flowchart explaining the pulse repetition frequency setting process before a residual multiple echo virtual image generation suppression process in the ultrasonic diagnosing device of FIG. The flowchart explaining the residual multiple echo virtual image generation suppression process in the ultrasonic diagnosing device of FIG. The flowchart explaining the residual multiple echo virtual image generation suppression process in the ultrasonic diagnosing device of FIG. The figure which shows two B mode tomographic images produced | generated by transmission / reception of the ultrasonic wave of a different pulse repetition frequency. The figure which shows the difference image of two B mode tomographic images of FIG. The figure explaining the calculation method of the residual multiple echo virtual image generation suppression pulse repetition frequency in step S29 of FIG. The flowchart explaining the other residual multiple echo virtual image generation | occurrence | production suppression processing in the ultrasonic diagnosing device of FIG. The flowchart explaining the other residual multiple echo virtual image generation | occurrence | production suppression processing in the ultrasonic diagnosing device of FIG. The figure explaining the change method of the pulse repetition frequency in step S61 of FIG. The flowchart explaining the other residual multiple echo virtual image generation | occurrence | production suppression processing in the ultrasonic diagnosing device of FIG. The flowchart explaining the other residual multiple echo virtual image generation | occurrence | production suppression processing in the ultrasonic diagnosing device of FIG.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus 11 Main body 12 Ultrasonic probe 13 Input part 14 Display part 21 Control part 22 Transmission part 23 Reception part 24 Image data generation part 25 Data storage part 26 Calculation part 27 Residual multiple echo virtual image generation suppression part 28 DSC
31 B mode processing unit 32 Doppler mode processing unit 33 Residual multiple echo virtual image generation determination unit 34 Residual multiple echo virtual image generation depth / region calculation unit 35 Residual multiple echo virtual image generation suppression pulse repetition frequency calculation unit 36 Pulse repetition frequency change unit

Claims (9)

Image data generating means for transmitting and receiving ultrasonic waves of a predetermined pulse repetition frequency and generating ultrasonic image data from received signals;
Virtual image generation determination means for determining whether or not a virtual image due to residual multiple echo is generated based on a plurality of image data generated by the image data generation means by transmission and reception of ultrasonic waves having a plurality of different pulse repetition frequencies;
A residual multiple echo virtual image generation depth calculation means for calculating a depth at which a virtual image due to residual multiple echo is generated; and
Residual multiple echo virtual image generation suppression that is a pulse repetition frequency that suppresses virtual image generation due to residual multiple echo based on the depth at which the virtual image due to residual multiple echo is generated, calculated by the residual multiple echo virtual image generation depth calculation means A residual multiple echo virtual image generation suppression pulse repetition frequency calculating means for calculating a pulse repetition frequency;
An ultrasonic diagnostic apparatus comprising: pulse repetition frequency changing means for changing a pulse repetition frequency when transmitting and receiving ultrasonic waves. The pulse repetition frequency changing means is
If it is determined by the residual multiple echo virtual image generation determination means that a virtual image due to residual multiple echo has occurred, the pulse repetition frequency when transmitting and receiving ultrasound is changed to the residual multiple echo virtual image generation suppression pulse repetition frequency,
When it is determined by the residual multiple echo virtual image generation determination means that a virtual image due to residual multiple echo is not generated, a pulse repetition frequency when transmitting / receiving ultrasonic waves is higher than the residual multiple echo virtual image generation suppression pulse repetition frequency The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic diagnostic apparatus is changed to a frequency. When it is determined by the virtual image generation determination means that a virtual image due to residual multiple echo has occurred, the virtual image generation determination means further comprises a residual multiple echo virtual image generation area calculation means for calculating a region where a virtual image due to residual multiple echo is generated,
The pulse repetition frequency changing means is
In the scanning line related to the region where the virtual image due to the residual multiple echo is generated, the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed to the residual multiple echo virtual image generation suppression pulse repetition frequency,
In a scanning line not related to a region where a virtual image due to residual multiple echo is generated, the pulse repetition frequency when transmitting and receiving ultrasonic waves is changed to a frequency higher than the residual multiple echo virtual image generation suppression pulse repetition frequency. The ultrasonic diagnostic apparatus according to claim 1. The virtual image occurrence determination means is
Based on the difference image of the plurality of image data generated by the image data generation means by transmission / reception of ultrasonic waves having a plurality of different pulse repetition frequencies, a luminance difference larger than a predetermined reference value set in advance in the difference image A luminance determination means for determining whether or not there is a part,
The residual multiple echo virtual image generation determination means generates a virtual image due to residual multiple echo when the luminance determination means determines that there is a portion having a luminance difference larger than a predetermined reference value set in advance in the difference image. When it is determined by the luminance determination means that there is no portion having a luminance difference larger than a predetermined reference value set in advance in the difference image, it is determined that a virtual image due to residual multiple echo has not occurred. The ultrasonic diagnostic apparatus according to claim 1. A residual multiple echo virtual image generation region area ratio calculating means for calculating a residual multiple echo virtual image generation region area ratio that is a ratio of a region area occupied by a virtual image generated by the residual multiple echo in the entire display screen;
Residual multiple echo virtual image generation region area ratio determining means for determining whether the residual multiple echo virtual image generation region area ratio is larger than a predetermined reference value based on the residual multiple echo virtual image generation region area ratio; Prepared,
The pulse repetition frequency changing means is
When the residual multiple echo virtual image generation region area ratio determining unit determines that the residual multiple echo virtual image generation region area ratio is larger than a predetermined reference value set in advance, a pulse repetition frequency when transmitting and receiving ultrasonic waves is set to Change to multiple echo virtual image generation suppression pulse repetition frequency,
When the residual multiple echo virtual image generation region area ratio determination unit determines that the residual multiple echo virtual image generation region area ratio is smaller than a predetermined reference value set in advance, the pulse repetition frequency when transmitting and receiving ultrasonic waves, The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic diagnostic apparatus is changed to a frequency higher than a pul repetition frequency for suppressing residual multi-echo virtual image generation. The image data generating means transmits / receives ultrasonic waves having the changed pulse repetition frequency after the pulse repetition frequency when the ultrasonic waves are transmitted / received by the pulse repetition frequency changing means, and receives ultrasonic image data from the received signal. The ultrasonic diagnostic apparatus according to claim 1, wherein: Display control means for displaying data relating to the residual multiple echo virtual image generation suppression pulse repetition frequency;
Input means for inputting data of a predetermined pulse repetition frequency when transmitting and receiving ultrasonic waves,
The pulse repetition frequency changing unit is configured to change a pulse repetition frequency when transmitting / receiving ultrasonic waves to the predetermined pulse repetition frequency based on the data of the predetermined pulse repetition frequency input by the input unit. The ultrasonic diagnostic apparatus according to claim 1, wherein the apparatus is an ultrasonic diagnostic apparatus. A residual multiple echo virtual image generation determination step for determining whether or not a virtual image due to residual multiple echo is generated based on a plurality of image data generated by scanning ultrasonic waves of a plurality of different pulse repetition frequencies;
A residual multiple echo virtual image generation depth calculation step for calculating a depth at which a virtual image due to residual multiple echo is generated; and
Residual multiple echo virtual image that is a pulse repetition frequency that suppresses the generation of a virtual image due to the residual multiple echo based on the depth at which the virtual image due to the residual multiple echo is calculated by the processing of the residual multiple echo virtual image generation depth calculation step A residual multiple echo virtual image generation suppression pulse repetition frequency calculating step for calculating a generation suppression pulse repetition frequency;
An image processing method for an ultrasonic diagnostic apparatus, comprising: a pulse repetition frequency changing step for changing a pulse repetition frequency when transmitting and receiving ultrasonic waves. A residual multiple echo virtual image generation determination step for determining whether or not a virtual image due to residual multiple echo is generated based on a plurality of image data generated by scanning ultrasonic waves of a plurality of different pulse repetition frequencies;
A residual multiple echo virtual image generation depth calculation step for calculating a depth at which a virtual image due to residual multiple echo is generated; and
Residual multiple echo virtual image that is a pulse repetition frequency that suppresses the generation of a virtual image due to the residual multiple echo based on the depth at which the virtual image due to the residual multiple echo is calculated by the processing of the residual multiple echo virtual image generation depth calculation step A residual multiple echo virtual image generation suppression pulse repetition frequency calculating step for calculating a generation suppression pulse repetition frequency;
An image processing program for an ultrasonic diagnostic apparatus, which causes a computer to execute a pulse repetition frequency changing step for changing a pulse repetition frequency when transmitting and receiving ultrasonic waves.

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