JP2013055984A - Ultrasonic diagnostic apparatus and program for ultrasonic diagnostic - Google Patents

Abstract

PROBLEM TO BE SOLVED: To acquire data indicating the position of a focus of ultrasonic waves for subject treatment by a simple configuration.SOLUTION: In a focus observation mode, tomographic image processing using a convex probe 26 for observation and reflection distribution image processing using the convex probe 26 for the observation and a plurality of HIFU (High Intensity Focused Ultrasound) vibrators 28 are executed. The tomographic image processing is the processing of acquiring tomographic images by an operation similar to a B mode. The reflection distribution image processing is the processing of transmitting ultrasonic waves from the plurality of HIFU vibrators 28, receiving the ultrasonic waves reflected inside the subject, and acquiring reflection distribution images on the basis of the received ultrasonic waves further. The reflection distribution image indicates reflection intensity distribution of the ultrasonic waves transmitted from the plurality of HIFU vibrators 28, and by the display of the image, the position of the focus F of the HIFU vibrators 28 is recognized by a practitioner.

Description

  The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to an improvement of an apparatus for transmitting ultrasonic waves for subject treatment.

  Treatment devices using high-intensity focused ultrasound therapy are widely used. This treatment apparatus is called a HIFU irradiation apparatus (High Intensity Focused Ultrasound), and the treatment site is irradiated with ultrasonic waves to cause necrosis of the tissue.

  Some HIFU irradiation apparatuses include a plurality of ultrasonic transducers. The plurality of ultrasonic transducers are fixed to the housing so that ultrasonic waves emitted from the respective ultrasonic transducers are irradiated to one point to form a focal point. During the treatment, the position of the focal point is adjusted to the treatment site and ultrasonic waves are irradiated. For confirmation of the irradiation position, for example, a magnetic resonance image display device (MRI) that displays an ultrasonic irradiation position on an image based on a temperature rise is used. In this case, the practitioner confirms the irradiation position on the MRI image, that is, the ablation site where the temperature has risen, after irradiating a strong ultrasonic wave for treatment. However, in such an operation, since it is difficult to confirm the position of the focal point in advance, a shift is likely to occur between the actual ablation site and the site to be treated.

  As described above, there is an apparatus that represents a focal point on an ultrasonic image in addition to an apparatus that represents an ablation site on a magnetic resonance image. For example, Patent Document 1 below describes an ultrasonic therapy apparatus that observes the position of a focal point using an ultrasonic diagnostic apparatus that displays a tomographic image. In this apparatus, a weak level ultrasonic wave that does not affect the tissue is emitted from the ultrasonic transducer for treatment, and a tomographic image is displayed by transmission / reception of the ultrasonic wave by the ultrasonic imaging probe. Since the acoustic characteristics of the tissue of the subject change according to the temperature change of the tissue, the position of the focal point is indicated by the change in luminance in the tomographic image.

  Patent Document 2 describes an ultrasonic thermotherapy device. This apparatus detects a component reflected by a heating part by a heating ultrasonic probe from an output signal of the imaging ultrasonic probe, and displays information indicating the position of the heating part on a tomographic image. The component detected from the output signal of the imaging ultrasonic probe is a higher-order harmonic component generated at the heating site. Cited Document 3 describes an ultrasonic irradiation apparatus that performs ultrasonic beam scanning for imaging independently of the transmission probe for irradiation. In this apparatus, an ultrasonic wave having a frequency twice or more the frequency of the ultrasonic wave for irradiation is received as an ultrasonic wave for imaging.

JP-A-8-71069 JP-A-61-13554 JP-A-62-87150

  In the HIFU irradiation apparatus, the position of the focal point of the ultrasonic wave emitted from each ultrasonic transducer is constant when the propagation speed of the ultrasonic wave in the subject is uniform. However, some tissues in the subject have different ultrasonic propagation speeds from other tissues. In this case, the propagation speed of the ultrasonic wave in the subject becomes non-uniform, and the positional relationship between the focus position and each ultrasonic transducer changes according to the non-uniformity of the propagation speed. Therefore, in the treatment, it is preferable to use a device that acquires data indicating the position of the focal point and displays the focal point position.

  An object of this invention is to acquire the data which show the position of the focus of the ultrasonic wave for a subject treatment by simple structure.

  The present invention includes a therapeutic transmitter that transmits ultrasonic waves toward a focal point located within a subject, and a reception beam that scans the ultrasonic waves that are transmitted from the therapeutic transmitter and reflected within the subject. And a reflection distribution data generation unit that generates ultrasonic reflection distribution data on the scanning plane of the reception beam based on the ultrasonic waves received by the reception unit.

  The ultrasonic reflection distribution data generated in the present invention indicates the intensity of the ultrasonic wave transmitted from the treatment transmitter and reflected at each point on the scanning plane in the subject. The intensity of the ultrasonic wave reflected at the focus position of the treatment transmitter is larger than the intensity of the ultrasonic wave reflected at another position. Therefore, the focal position is indicated by the ultrasonic reflection distribution data.

  The ultrasonic diagnostic apparatus according to the present invention preferably includes a focus search unit that obtains focus search image data representing the position of the focus based on the ultrasonic reflection distribution data, and the focus search unit includes the focus search unit Based on the ultrasonic reflection distribution data, for each region of interest when the scanning plane is divided into a plurality of regions of interest, a statistical value calculation means for obtaining a statistical value of the pixel value, and a pixel value in each region of interest Search image data obtaining means for obtaining the focus search image data by setting the pixel value according to the statistical value obtained for the region.

  In the present invention, the statistical value obtained for each region of interest includes, for example, an average value of pixel values in each region of interest. As other statistical values, the median, median, minimum, and maximum pixel values within each region of interest, values obtained by multiplying these values by a predetermined constant, and adding or subtracting a predetermined constant to these values A value or the like may be used. These statistics show a tendency of the size of the pixel values in the region of interest.

  The ultrasonic diagnostic apparatus according to the present invention preferably includes a focus search unit that obtains focus search image data representing the position of the focus based on the ultrasonic reflection distribution data, and the focus search unit includes the focus search unit Fourier transform means for each region of interest formed by dividing the scanning plane into a plurality of regions to ultrasonic reflection distribution data, and obtaining a spatial frequency distribution for each region of interest, and pixels in each region of interest Search image data obtaining means for obtaining the focus search image data by setting the value to a pixel value corresponding to the spatial frequency distribution obtained for each region of interest.

  The region of interest including the focus of the treatment transmitter includes a high spatial frequency component. Therefore, the spatial frequency distribution obtained for a region of interest indicates whether the region of interest contains a focus. In the present invention, based on such a principle, the pixel value in each region of interest is set to a pixel value corresponding to the spatial frequency distribution obtained for each region of interest, and focus search image data representing the position of the focal point is obtained. It is done.

  Also, in the ultrasonic diagnostic apparatus according to the present invention, preferably, the therapeutic transmission unit includes a plurality of ultrasonic transducers, and the ultrasonic diagnostic apparatus according to the present invention is further based on the focus search image data. A focal position determination unit for determining the focal position, and a delay time of a signal applied to each ultrasonic transducer based on a difference between the focal position and the target focal position obtained by the focal position determination unit. And a focal position control unit that brings the focal position closer to the target focal position.

  The positional relationship between the plurality of ultrasonic transducers and the focal point provided in the treatment transmitter is constant when the propagation speed in the subject is uniform. However, when the propagation speed in the subject is non-uniform, this positional relationship changes according to the non-uniformity of the propagation speed. Therefore, the ultrasonic diagnostic apparatus according to the present invention makes the focus position close to the target focus position by the focus position determination unit and the focus position control unit, and facilitates the operation during the treatment.

  In addition, the ultrasonic diagnostic apparatus according to the present invention preferably includes an observation transmission unit that transmits the observation ultrasonic wave toward the subject and scans the transmission beam of the observation ultrasonic wave in the scanning plane. The reception unit forms a reception beam having the same direction as the transmission beam of the observation ultrasonic wave, receives the observation ultrasonic wave transmitted from the observation transmission unit and reflected within the subject, and the present invention The ultrasonic diagnostic apparatus according to the present invention further includes a tomographic image data generating unit that generates tomographic image data of the subject on the scanning plane based on the observation ultrasonic waves received by the receiving unit, and the tomographic image data And an image display unit that displays an image based on the focus search image data so as to overlap the image based on the image.

  In addition, the ultrasonic diagnostic apparatus according to the present invention preferably includes an observation transmission unit that transmits the observation ultrasonic wave toward the subject and scans the transmission beam of the observation ultrasonic wave in the scanning plane. The reception unit forms a reception beam having the same direction as the transmission beam of the observation ultrasonic wave, receives the observation ultrasonic wave transmitted from the observation transmission unit and reflected within the subject, and the present invention The ultrasonic diagnostic apparatus according to the present invention further includes a tomographic image data generating unit that generates tomographic image data of the subject on the scanning plane based on the observation ultrasonic waves received by the receiving unit, and the tomographic image data And an image display unit that displays an image based on the ultrasonic reflection distribution data, overlaid on the image based on the above.

  The ultrasonic reflection distribution data in the present invention indicates the position of the focal point of the treatment transmitter. The image display unit in the present invention displays an image indicating the position of the focus on the image based on the tomographic image data. This facilitates the operation of focusing the treatment transmitter on the treatment site of the subject.

  In addition, the ultrasonic diagnostic apparatus according to the present invention preferably includes a focus search unit that obtains focus search data representing the position of the focus based on the ultrasonic reflection distribution data, and the focus search unit includes the ultrasonic search unit. Based on the sound wave reflection distribution data, a statistical value calculation means for obtaining a statistical value for each region of interest when the scanning plane is divided into a plurality of regions of interest, and a value corresponding to each region of interest can be obtained for each region of interest. And a focus search data obtaining means for obtaining the focus search data by setting the value according to the statistical value.

  In addition, the ultrasonic diagnostic apparatus according to the present invention preferably includes a focus search unit that obtains focus search data representing the position of the focus based on the ultrasonic reflection distribution data, and the focus search unit includes the ultrasonic search unit. Fourier transform means for each region of interest formed by dividing the scanning plane into a plurality of regions to the sound wave reflection distribution data, and a Fourier transform means for obtaining a spatial frequency distribution for each region of interest, and corresponding to each region of interest Focus search data obtaining means for obtaining the focus search data by setting the value to a value corresponding to the spatial frequency distribution obtained for each region of interest.

  In the ultrasonic diagnostic apparatus according to the present invention, preferably, the therapeutic transmission unit includes a plurality of ultrasonic transducers, and the ultrasonic diagnostic apparatus according to the present invention is further based on the focus search data. Controlling a delay time of a signal to be given to each ultrasonic transducer based on a difference between a focal position and a target focal position obtained by the focal position determining unit that obtains the focal position and the focal position determining unit; A focal position control unit that brings the focal position closer to the target focal position.

  In the ultrasonic diagnostic apparatus according to the present invention, the focal position determination unit obtains the focal position based on the focal point search data. The focal position control unit controls the delay time of the signal to be given to each ultrasonic transducer based on the difference between the focal position and the target focal position obtained by the focal position determining unit. The focus search data is data representing the position of the focus of the treatment transmitter, and is not necessarily image data for performing image display.

  In the ultrasonic diagnostic apparatus according to the present invention, preferably, the reflection distribution data generation unit is configured to detect an ultrasonic wave on the scanning plane of the received beam based on a higher-order harmonic component of the ultrasonic wave received by the receiving unit. Sound wave reflection distribution data is generated.

  In general, the reception beam for the higher-order harmonic component is sharper than the reception beam for the fundamental wave component, and the size of the side lobe is small. Therefore, the accuracy of the focus position indicated by the ultrasonic reflection distribution data can be improved by using the higher-order harmonic component.

  The present invention also provides a therapeutic transmitter that transmits ultrasonic waves toward a focal point located within the subject, and an ultrasonic wave that is transmitted from the therapeutic transmitter and reflected within the subject. An ultrasound diagnostic program that is read into an ultrasound diagnostic apparatus comprising: a receiving unit that receives while scanning; and a processor that performs arithmetic processing on the ultrasound received by the receiving unit, wherein the processor includes the processor A process of generating ultrasonic reflection distribution data on the scanning plane of the received beam is executed based on the ultrasonic wave received by the receiving unit.

  According to the present invention, it is possible to acquire data indicating the position of the focal point of ultrasonic waves for subject treatment with a simple configuration.

It is a figure which shows the structure of the ultrasonic diagnosing device which concerns on 1st Embodiment. It is a figure which shows the one-dimensional scanning plane, the transmitted pulsed ultrasonic wave, the receiving beam, and the received pulsed ultrasonic wave. It is a figure which shows a reflection distribution image notionally. It is a figure which shows notionally a mode that the reflection distribution image was divided | segmented into the some region of interest. It is a figure which shows notionally the two-dimensional Fourier transform performed with respect to a region of interest. It is a figure which shows the structure of the three-dimensional ultrasonic diagnosing device which concerns on 2nd Embodiment.

1. Ultrasonic Diagnostic Device (1) Configuration of Ultrasonic Diagnostic Device FIG. 1 shows the configuration of an ultrasonic diagnostic device according to the first embodiment of the present invention. This ultrasonic diagnostic apparatus is a B mode for displaying a tomographic image of a subject, a focus observation mode for displaying an image showing the focus of a therapeutic ultrasonic wave on a tomographic image, or a tissue irradiated with ultrasonic waves on a treatment site. Operate in any mode of treatment mode to destroy. That is, in this ultrasonic diagnostic apparatus, it is possible to perform a diagnosis by a tomographic image and a treatment by high-density focused ultrasound therapy.

  The configuration of the ultrasonic diagnostic apparatus will be described. The ultrasonic diagnostic apparatus includes a treatment observation probe 10, a signal processing unit 12, a central processing unit 14, a processing memory 16, a frame memory 18, a monitor 20, and an operation panel 22. The treatment observation probe 10 includes an observation convex probe 26 and a plurality of HIFU transducers 28. The observation convex probe 26 includes a plurality of ultrasonic transducers arranged on a curved surface through which ultrasonic waves are transmitted and received. As the observation convex probe 26, for example, a probe in which a plurality of ultrasonic transducers are arranged in a row, a probe in which a plurality of ultrasonic transducers are arranged in a plurality of rows, or the like is used.

  Each HIFU transducer 28 may be a concave transducer that transmits ultrasonic waves toward the focal point. The HIFU transducers 28 are arranged so that the positions of the respective focal points coincide. FIG. 1 shows an example in which two HIFU transducers 28 are arranged. However, three or more HIFU transducers 28 are annularly enclosed around the ultrasonic transmission / reception surface of the observation convex probe 26. The arranged configuration may be adopted. Further, if the intensity of the ultrasonic wave transmitted from the HIFU transducer 28 is sufficient, a configuration in which one HIFU transducer 28 is used may be used. The observation convex probe 26 and each HIFU transducer 28 are connected to the signal processing unit 12.

  The signal processing unit 12 includes an observation transmission unit 30, an observation reception unit 32, a treatment transmission unit 34, a timing control unit 36, and an image data generation unit 38. The timing control unit 36 includes a timing at which the observation transmission unit 30 outputs a signal to the observation convex probe 26, a timing at which the treatment transmission unit 34 outputs a signal to each HIFU transducer 28, and an observation reception unit 32. The timing for acquiring a signal from the observation convex probe 26 is controlled. Other components included in the signal processing unit 12 will be described later.

  The signal processing unit 12, central processing unit 14, processing memory 16, frame memory 18, monitor 20, and operation panel 22 are connected via a bus line 24. The central processing unit 14 includes a processor that executes arithmetic processing according to a program, and executes processing according to the program stored in the processing memory 16. In addition, a part or all of the observation transmission unit 30, the observation reception unit 32, the treatment transmission unit 34, the timing control unit 36, and the image data generation unit 38 included in the signal processing unit 12 is configured by a processor. Processing corresponding to the program stored in the processing memory 16 is executed.

  The central processing unit 14 controls the signal processing unit 12 according to the operation setting on the operation panel 22. For example, any one of the B mode, the focus observation mode, and the treatment mode is selected on the operation panel 22, and the central processing unit 14 executes control according to the selection of the operation mode on the operation panel 22.

  In addition, the central processing unit 14 exchanges data with the signal processing unit 12, and stores the data in the processing memory 16 as appropriate in the course of processing executed by the signal processing unit 12, or from the processing memory 16. Read data. Further, the central processing unit 14 stores and reads the image data obtained by the signal processing unit 12 in the frame memory 18 and displays an image on the monitor 20 based on the image data stored in the frame memory 18. Let

(2) Operation in B Mode In the B mode, the observation convex probe 26 is used among the observation convex probe 26 and the plurality of HIFU transducers 28 included in the treatment observation probe 10. A one-dimensional scanning plane 40 of the transmission / reception beam by the observation convex probe 26 becomes an observation plane, and a tomographic image on the observation plane is displayed on the monitor 20. Therefore, the treatment / observation probe 10 is supported in a posture in which the one-dimensional scanning surface 40 of the observation convex probe 26 coincides with the observation surface of the subject.

  The operation in the B mode is executed by performing a B mode setting operation on the operation panel 22. The observation transmitter 30 outputs the pulse-modulated electrical signal (pulse modulation signal) to the observation convex probe 26. The observation convex probe 26 generates pulsed ultrasonic waves based on the pulse modulation signal output from the observation transmission unit 30. At this time, the observation transmitter 30 functions as a beamformer for the transmitted pulsed ultrasonic waves. That is, the observation transmission unit 30 selects a transducer group that contributes to transmission of ultrasonic waves from a plurality of ultrasonic transducers included in the observation convex probe 26. Then, the transmission beam is formed by controlling the delay time of the signal output to each ultrasonic transducer forming the transducer group. Further, the observation transmission unit 30 switches the transducer group selected from the plurality of ultrasonic transducers and performs one-dimensional scanning with the transmission beam.

  The observation convex probe 26 receives pulsed ultrasonic waves reflected in the subject. Then, an electric signal is generated based on the received pulse ultrasonic wave, and the electric signal is output to the observation receiving unit 32. The observation receiving unit 32 functions as a beam former of received pulsed ultrasonic waves. That is, the observation receiving unit 32 forms a received beam by phasing and adding a plurality of electrical signals output from the same transducer group as that selected for transmission of pulsed ultrasonic waves. Since the transducer group that contributes to the transmission of the pulsed ultrasonic wave is the same as the transducer group that contributes to the reception of the pulsed ultrasonic wave, the received beam is scanned one-dimensionally in the same direction as the transmission beam. FIG. 1 shows a state in which a transmission beam 42 and a reception beam 44 are formed and these beams are one-dimensionally scanned on the one-dimensional scanning plane 40.

  The observation receiving unit 32 generates beam data corresponding to the received pulsed ultrasound. This beam data is data representing on the time axis the intensity of the reflected wave generated at each distance from the observation convex probe 26 in a specific transmission / reception beam direction. The observation receiving unit 32 outputs the beam data generated in this way to the image data generating unit 38.

  The observation transmission unit 30 and the observation reception unit 32 repeatedly perform one-dimensional scanning of transmission / reception beams on the subject. The image data generation unit 38 generates tomographic image data for each one-dimensional scan based on a beam data group obtained for each one-dimensional scan. Then, the tomographic image data sequentially generated by the one-dimensional scanning that is repeatedly performed is stored in the frame memory 18 under the control of the central processing unit 14. The central processing unit 14 operates as an image display unit that displays an image on the monitor 20 and causes the monitor 20 to sequentially display tomographic images based on the tomographic image data stored in the frame memory 18.

(3) Operation in Focus Observation Mode (3-1) Outline of Focus Observation Mode The operation in the focus observation mode is executed by performing a focus observation mode setting operation on the operation panel 22. In the focus observation mode, tomographic image processing using the observation convex probe 26 and reflection distribution image processing using the observation convex probe 26 and the plurality of HIFU transducers 28 are executed.

  The tomographic image processing is processing for acquiring a tomographic image by the same operation as in the B mode. The reflection distribution image processing is processing for transmitting ultrasonic waves from a plurality of HIFU transducers 28, receiving ultrasonic waves reflected in the subject, and acquiring a reflection distribution image based on the received ultrasonic waves. This reflection distribution image shows the reflection intensity distribution of ultrasonic waves transmitted from a plurality of HIFU transducers 28, and this image is displayed so that the focus F of the HIFU transducer 28 (hereinafter referred to as HIFU focus F). ) Is recognized by the practitioner.

  The tomographic image processing and the reflection distribution image processing are executed in a time division manner. That is, the reflection distribution image processing is executed between the time when each tomographic image is acquired in the tomographic image processing. For example, the reflection distribution image processing is executed in a time period after the tomographic image is acquired based on the previous one-dimensional scan until the tomographic image is acquired based on the next one-dimensional scan.

(3-2) Reflection Distribution Image Processing The reflection distribution image processing will be described. The therapeutic transmitter 34 repeatedly outputs a pulse modulation signal for focus observation to each HIFU transducer 28 at a predetermined period. As a result, each HIFU transducer 28 repeatedly transmits pulse ultrasonic waves for focus observation to the HIFU focus F at a predetermined cycle. This ultrasonic wave for focus observation is an ultrasonic wave having an intensity that does not cause necrosis of the tissue of the subject. In other words, the intensity of the pulse modulation signal for focus observation output from the treatment transmitter 34 is set so that the intensity of the pulse ultrasound for focus observation does not cause the tissue of the subject to become necrotic. Has been.

  The observation convex probe 26 receives pulse ultrasonic waves for focus observation reflected in the subject. Then, an electric signal is generated based on the received pulse ultrasonic wave, and the electric signal is output to the observation receiving unit 32.

  Similarly to the operation in the B mode, in the reflection distribution image processing in the focus observation mode, the observation receiving unit 32 functions as a beam former of the received pulsed ultrasonic wave and performs one-dimensional scanning of the received beam. As shown in FIG. 2, in one-dimensional scanning of the reception beam 48, the reception beam 48 is directed in one specific direction with respect to one pulse ultrasonic wave 46 transmitted from each HIFU transducer 28. That is, the observation receiving unit 32 changes the direction of the reception beam 48 at a predetermined step angle every time one pulse ultrasonic wave 50 transmitted from each HIFU transducer 28 and reflected in the subject is received.

  The observation receiving unit 32 generates beam data corresponding to the second harmonic component of the received pulsed ultrasonic wave. The second harmonic beam data is data representing the intensity of the second harmonic component of the reflected wave generated on each distance from the observation convex probe 26 on the time axis in a specific reception beam direction. The observation receiving unit 32 outputs the second harmonic beam data generated in this way to the image data generating unit 38.

  The image data generation unit 38 generates reflection distribution image data based on the second harmonic beam data group obtained for each one-dimensional scan. Then, the reflection distribution image data sequentially generated by the repeated one-dimensional scanning is stored in the frame memory 18 under the control of the central processing unit 14. The central processing unit 14 sequentially displays the reflection distribution image based on the reflection distribution image data stored in the frame memory 18 for each one-dimensional scan on the tomographic image on the monitor 20.

  FIG. 3 conceptually shows the reflection distribution image. In this figure, darker colors are given to portions with higher luminance. Since the intensity of the ultrasonic wave reflected at the HIFU focal point F is higher than the intensity of the ultrasonic wave reflected at the other position, the position of the HIFU focal point F has higher brightness than the other position. By displaying the reflection distribution image on the monitor 20 so as to be superimposed on the tomographic image, the practitioner can grasp the degree of convergence of the ultrasonic waves transmitted from the plurality of HIFU transducers 28 and the position of the HIFU focal point F. .

  The reflection distribution image data generated based on such processing has significance as image data, and the intensity of ultrasonic waves transmitted from a plurality of HIFU transducers 28 and reflected at each point on the one-dimensional scanning plane 40. It has significance as ultrasonic reflection distribution data showing.

  In the focus observation mode according to the present embodiment, reflection distribution image data is acquired based on the second harmonic component of the received pulsed ultrasonic wave. In general, the reception beam for the higher-order harmonic component is sharper than the reception beam for the fundamental wave component, and the size of the side lobe is small. Therefore, the effect that the resolution of the reflection distribution image can be improved by using the higher-order harmonic component and the effect that the artifact can be suppressed can be obtained. In the above description, the processing using the second harmonic component of the received pulse ultrasonic wave has been described. However, the processing using the third or higher order higher harmonic component of the received pulse ultrasonic wave may be executed.

  The central processing unit 14 may execute a process of displaying only the reflection distribution image on the monitor 20 instead of displaying the reflection distribution image on the tomographic image on the monitor 20. Which mode is used for image display is set by operating the operation panel 22.

  Also, in the above, as an example when performing tomographic image processing and reflection distribution image processing in a time-sharing manner, a tomographic image based on the next one-dimensional scan is obtained after the tomographic image is acquired based on the previous one-dimensional scan. An example in which a reflection distribution image is acquired during a time period until acquisition of the above is taken up. In addition to performing time division in this way, the transmission / reception beam for tomographic image processing and the reception beam for reflection distribution image processing are one-dimensionally scanned in the same direction, and these beams are directed in a specific direction. Further, transmission / reception of pulse ultrasonic waves in reflection distribution image processing may be performed following transmission / reception of pulse ultrasonic waves in tomographic image processing.

  In addition to displaying the reflection distribution image, the ultrasonic diagnostic apparatus may display a focus search image described below. The focus search image is an image obtained by replacing the pixel value of a pixel having a low possibility of showing a focus with 0 in the original reflection distribution image. The focus search image includes a focus search image based on a luminance average value and a focus search image based on spatial frequency analysis. The focus search image data representing the focus search image is generated by a focus search unit 38A included in the image data generation unit 38.

(3-3) Display of Focus Search Image Based on Average Brightness Value A focus search image based on the average brightness value will be described. The focus search unit 38A obtains an average value of luminance values, that is, an average value of pixel values, for each region of interest when the reflection distribution image is divided into a plurality of regions of interest. FIG. 4 conceptually shows a state in which the reflection distribution image is divided into a plurality of regions of interest ROI. The division of each region of interest ROI with respect to the reflection distribution image may be finer or coarser than that shown in FIG.

  The focus search unit 38A performs a filtering process based on the average value of the pixel values on the reflection distribution image data obtained as described above to obtain focus search image data. This filtering process maintains the pixel value as it is for the region of interest ROI in which the average value of the pixel values exceeds the predetermined threshold Th, and for the region of interest ROI in which the average value of the pixel values is equal to or less than the predetermined threshold Th. This is a process of replacing the pixel value with 0.

  The focus search unit 38A performs a filtering process based on the average value on the reflection distribution image data obtained for each one-dimensional scan of the received beam to obtain focus search image data. Then, the obtained focus search image data is stored in the frame memory 18. The central processing unit 14 sequentially displays the focus search image based on the focus search image data stored in the frame memory 18 for each one-dimensional scan on the tomographic image on the monitor 20.

  Note that filter processing based on other statistical values may be employed instead of the filter processing based on the average value of the pixel values. For example, the median value, median, minimum value, maximum value of a pixel value within one region of interest ROI, a value obtained by multiplying these values by a predetermined constant, a value obtained by adding or subtracting a predetermined constant to these values, etc. Is a statistical value. This statistical value is a value indicating a tendency of the size of the pixel value in the region of interest ROI. In the filtering process, the pixel value is maintained as it is for the region of interest ROI whose statistical value exceeds the predetermined threshold Th1, and the pixel value is determined for the region of interest ROI whose statistical value of the pixel value is equal to or smaller than the predetermined threshold Th1. The process of replacing with 0 is executed.

  Further, the filtering process increases the pixel value by a constant multiple for the region of interest ROI in which the statistical value of the pixel value exceeds the predetermined threshold Th1, and the region of interest ROI in which the statistical value of the pixel value is equal to or less than the predetermined threshold Th1. As for, the pixel value may be replaced with the predetermined value B. In addition, for a region of interest ROI in which the statistical value of the pixel value exceeds the predetermined threshold Th1, the pixel value is replaced with the predetermined value A, and for the region of interest ROI in which the statistical value of the pixel value is equal to or less than the predetermined threshold Th1, the pixel value A process of replacing with a predetermined value B may be executed. Further, when a color image is displayed on the monitor 20, for a region of interest ROI in which the statistical value of the pixel value exceeds a predetermined threshold Th1, a process for setting a pixel value of a color different from that of the other region of interest ROI is performed. May be executed.

(3-4) Display of Focus Search Image Based on Spatial Frequency Analysis Next, the focus search image based on the spatial frequency analysis will be described. The focus search unit 38A performs a filtering process based on spatial frequency analysis on the reflection distribution image data obtained as described above to obtain focus search image data. This filtering process is executed as follows.

  The focus search unit 38A performs a two-dimensional Fourier transform on each region of interest ROI. Here, when the pixel value in the region of interest ROI is expressed as g (x, y), the absolute value of the result of performing the two-dimensional Fourier transform F [] on g (x, y) is represented by q (ξ , F). That is, q (ξ, f) = | F [g (x, y)] |.

  Here, (x, y) represents position coordinates in the region of interest ROI, (ξ, f) represents a two-dimensional spatial frequency component, and Fourier transform value q (ξ, f) represents a spatial frequency distribution.

  The focal point search unit 38A obtains the maximum point (ξm, fm) at which the spatial frequency distribution q (ξ, f) obtained for the region of interest ROI has the maximum value. When the spatial frequency ξm is equal to or higher than the predetermined threshold ξt and the spatial frequency fm is equal to or higher than the predetermined threshold ft, the pixel value in the region of interest ROI is maintained as it is. On the other hand, when the spatial frequency ξm is less than the predetermined threshold ξt or the spatial frequency fm is less than the predetermined threshold ft, the pixel value in the region of interest ROI is replaced with 0.

  According to the filter processing based on such spatial frequency analysis, the pixel value is maintained for the region of interest ROI in which the maximum point (ξm, fm) is in the region satisfying ξ ≧ ξt and f ≧ ft, and the maximum point For a region of interest ROI in which (ξm, fm) is in a region satisfying ξ <ξt or f <ft, focus search image data having a pixel value of 0 is obtained.

  According to this focus search image data, the pixel value of a pixel having a low possibility of showing a HIFU focus is 0 based on the principle described later. Thereby, the focus search image becomes an image representing the focus.

  The focus search unit 38A performs a filtering process based on spatial frequency analysis on the reflection distribution image data obtained for each one-dimensional scan of the received beam to obtain focus search image data. Then, the obtained focus search image data is stored in the frame memory 18. The central processing unit 14 sequentially displays the focus search image based on the focus search image data stored in the frame memory 18 for each one-dimensional scan on the tomographic image on the monitor 20.

  The principle by which focus search image data is obtained by such filter processing will be described. FIG. 5 conceptually shows a two-dimensional Fourier transform performed on the region of interest ROI. FIG. 5A shows the pixel value g (x, y) of the region of interest ROI not including the HIFU focal point on the (x, y) plane. FIG. 5B shows a spatial frequency distribution q (ξ, f) obtained by performing a two-dimensional Fourier transform on the region of interest ROI in FIG. 5A on the (ξ, f) plane. . However, for the (ξ, f) plane, a region where ξ ≧ 0 and f ≧ 0 is satisfied is shown. In FIGS. 5 (a) and 5 (b), darker colors are given as g (x, y) and q (ξ, f) are larger.

  FIG. 5C shows the pixel value g (x, y) of the region of interest ROI including the HIFU focus on the (x, y) plane. FIG. 5D shows the spatial frequency distribution q (ξ, f) obtained by performing the two-dimensional Fourier transform on the region of interest ROI in FIG. 5C on the (ξ, f) plane. .

  When there is a large region in which the pixel value protrudes in the region of interest, the region of interest includes a high spatial frequency component. Therefore, the spatial frequency distribution has a maximum value in the upper right region of the two-dimensional frequency plane (ξ, f). On the other hand, when the pixel value is flat in the region of interest, the region of interest contains a low spatial frequency component. Therefore, the spatial frequency distribution has a maximum value in the lower left region of the two-dimensional frequency plane (ξ, f).

  The HIFU focus is expressed as a large area with a large pixel value. Accordingly, the spatial frequency distribution of the region of interest including the HIFU focus is a distribution having a maximum value in the upper right region of the two-dimensional frequency plane (ξ, f) as shown in FIG. On the other hand, the spatial frequency distribution of the region of interest not including the focal position is a distribution having a maximum value in the lower left region of the two-dimensional frequency plane (ξ, f) as shown in FIG.

  Therefore, the focal point search unit 38A includes a HIFU focal point for a region of interest (focal region) in which the maximum point (ξm, fm) is in a region satisfying ξ ≧ ξt and f ≧ ft. Maintain pixel values. For a region of interest (non-focal region) where the maximum point (ξm, fm) is in a region satisfying ξ <ξt or f <ft, the HIFU focus is not included, and the pixel value of the region of interest is 0. Thereby, focus search image data in which the pixel value of the pixel indicating the HIFU focus is maintained and the other pixel values are set to 0 is obtained.

  The filtering process based on the spatial frequency analysis may be a process of increasing the pixel value by a constant multiple for the focal region and replacing the pixel value with the predetermined value B for the non-focal region. Further, a process of replacing the pixel value with the predetermined value A for the focal region and replacing the pixel value with the predetermined value B for the non-focal region may be executed. Furthermore, when a color image is displayed on the monitor 20, a process for setting pixel values of colors different from those in the non-focus area may be executed for the focus area.

  Also, which of the reflection distribution image, the focus search image based on the average brightness value, or the focus search image based on the spatial frequency analysis is displayed on the tomographic image is determined based on the selection operation on the operation panel 22. May be.

(4) Treatment Mode In the treatment mode, each HIFU transducer 28 transmits a therapeutic ultrasonic wave and irradiates the therapeutic site with the therapeutic ultrasonic wave. The therapeutic ultrasonic wave is an ultrasonic wave having an intensity that causes the subject tissue to become necrotic. The operation in the treatment mode is executed by performing a treatment mode setting operation on the operation panel 22. The treatment transmitter 34 outputs a continuous wave signal for treatment to each HIFU transducer 28 based on the control of the central processing unit 14. Thus, each HIFU transducer 28 transmits a continuous wave ultrasonic wave for treatment.

  In the treatment, the practitioner may operate the ultrasonic diagnostic apparatus as follows. The practitioner first sets the operation mode to the focus observation mode using the operation panel 22. Then, while referring to the position of the HIFU focus F on the monitor 20, the position and posture of the treatment observation probe 10 are adjusted so that the treatment site and the position of the HIFU focus F coincide with each other. The practitioner supports the treatment observation probe 10 in this state, and sets the operation mode to the treatment mode using the operation panel 22. As a result, therapeutic ultrasonic waves are transmitted from each HIFU transducer 28, and the ultrasonic waves are irradiated to the treatment site.

2. Three-dimensional ultrasonic diagnostic apparatus (1) Configuration of three-dimensional ultrasonic diagnostic apparatus Fig. 6 shows a configuration of a three-dimensional ultrasonic diagnostic apparatus according to the second embodiment. The same components as those shown in FIG. 1 are denoted by the same reference numerals and description thereof is omitted. The three-dimensional ultrasonic diagnostic apparatus operates in any one of the three-dimensional B mode, the three-dimensional focus observation mode, and the treatment mode, and can process the three-dimensional space in the subject. As in the ultrasonic diagnostic apparatus according to the first embodiment, the operation in each mode is executed by performing a setting operation for each mode on the operation panel 22.

  Each operation in the three-dimensional B mode and the three-dimensional focus observation mode is obtained by extending each operation in the B mode and the focus observation mode in the first embodiment from two dimensions to three dimensions. In the three-dimensional B mode, a plurality of tomographic image data is acquired over a three-dimensional space in the subject, and volume data including a plurality of tomographic image data is acquired. The monitor 20 displays one tomographic image or a stereoscopic image based on volume data.

  In the three-dimensional focus observation mode, a plurality of tomographic image data is acquired over a three-dimensional space in the subject, and volume data including a plurality of tomographic image data is acquired. Further, a plurality of reflection distribution image data is acquired over a three-dimensional space in the subject, and focal volume data including the plurality of reflection distribution image data is acquired. On the monitor 20, the reflection distribution image is displayed superimposed on one tomographic image. Alternatively, the stereoscopic image obtained from the volume data and the stereoscopic image obtained from the focal volume data are displayed on the monitor 20 in an overlapping manner.

  Next, the configuration of the three-dimensional ultrasonic diagnostic apparatus will be described. The three-dimensional ultrasonic diagnostic apparatus includes a HIFU head unit 52, a three-dimensional signal processing unit 66, a central processing unit 14, a processing memory 16, a frame memory 18, a monitor 20, and an operation panel 22.

  The HIFU head unit 52 includes a head housing 54, an observation three-dimensional probe 56, and a HIFU transducer array 58. The head housing 54 is formed in a bowl shape. A probe hole is formed in the bottom of the head casing 54. The observation three-dimensional probe 56 is fixed to the head casing 54 so that the surface on which ultrasonic waves are transmitted and received faces the opening side of the head casing 54 from the probe hole. The observation three-dimensional probe 56 includes a plurality of ultrasonic transducers arranged on a surface on which ultrasonic waves are transmitted and received. As the observation three-dimensional probe 56, for example, a plurality of ultrasonic transducers arranged in a plurality of rows (two-dimensional arrangement) is used.

  In addition, a transducer hole for arranging a plurality of HIFU transducers 60 forming the HIFU transducer array 58 is formed in the side surface of the head casing 54. Each HIFU vibrator 60 is fixed to the vibrator hole so that the positions of the respective focal points coincide. The observation three-dimensional probe 56 and each HIFU transducer 60 are connected to a three-dimensional signal processing unit 66.

  The three-dimensional signal processing unit 66 includes a 3D observation transmission unit 68, a 3D observation reception unit 70, an image data generation unit 38, a timing control unit 36, a focal position determination unit 74, a focal position control unit 76, and a 3D treatment transmission unit. 72. Here, “3D” means “3 Dimension”, that is, 3D. The timing control unit 36 is a timing at which the 3D observation transmitter 68 outputs a signal to the observation three-dimensional probe 56, a timing at which the 3D treatment transmitter 72 outputs a signal to each HIFU transducer 60, and a 3D observation The receiving unit 70 controls the timing at which a signal is acquired from the observation three-dimensional probe 56. Other components included in the three-dimensional signal processing unit 66 will be described later.

(2) Three-dimensional B mode In the three-dimensional B mode, the observation three-dimensional probe 56 is used among the observation three-dimensional probe 56 and the HIFU transducer array 58 provided in the HIFU head unit 52. In the three-dimensional B mode, for each repeated one-dimensional scan, the swing angle of the scanning surface is changed by a predetermined step angle, and a plurality of tomographic image data is acquired over the three-dimensional space in the subject. Here, the swing angle is a rotation angle of the one-dimensional scanning plane 40 with the swing axis 62 defined in the observation three-dimensional probe 56 as the central axis.

  In the three-dimensional ultrasonic diagnostic apparatus, the fluctuation range of the one-dimensional scanning surface 40 of the transmission / reception beam by the observation three-dimensional probe 56 becomes an observation region, and one tomographic image or three-dimensional image in the observation region is displayed on the monitor 20. . Therefore, the HIFU head unit 52 is supported in a posture in which the swing range of the one-dimensional scanning surface 40 of the observation three-dimensional probe 56 is located in the subject.

  The 3D observation transmission unit 68 outputs the pulse modulation signal to each ultrasonic transducer of the observation three-dimensional probe 56. Each ultrasonic transducer generates a pulsed ultrasonic wave based on the pulse modulation signal output from the 3D observation transmission unit 68. At this time, the 3D observation transmission unit 68 functions as a beam former of the transmitted pulsed ultrasonic waves. That is, the 3D observation transmission unit 68 controls the delay time of the signal output to each ultrasonic transducer to form a transmission beam, and performs one-dimensional scanning of the transmission beam.

  Each ultrasonic transducer of the observation three-dimensional probe 56 receives pulsed ultrasonic waves reflected in the subject. Each ultrasonic transducer generates an electric signal based on the received pulsed ultrasonic wave, and outputs the electric signal to the 3D observation receiving unit 70. The 3D observation receiving unit 70 functions as a beam former of the received pulsed ultrasonic wave. That is, the 3D observation reception unit 70 forms a reception beam by phasing and adding a plurality of electrical signals output from a plurality of ultrasonic transducers, and makes the reception beam one-dimensionally in the same direction as the transmission beam. Scan. The 3D observation receiving unit 70 generates beam data corresponding to the received pulsed ultrasound, and outputs the generated beam data to the image data generating unit 38.

  The 3D observation transmission unit 68 and the 3D observation reception unit 70 repeatedly perform one-dimensional scanning of the transmission and reception beams on the subject while changing the swing angle for each one-dimensional scanning. The image data generation unit 38 generates tomographic image data for each one-dimensional scan based on the beam data group obtained for each one-dimensional scan, and stores the tomographic image data in the frame memory 18 under the control of the central processing unit 14. To do. A plurality of tomographic image data obtained by one-dimensional scanning repeatedly performed while changing the swing angle is stored in the frame memory 18 as volume data. As a result, a plurality of tomographic image data obtained over the three-dimensional space in the subject is stored in the frame memory 18 as volume data.

  The central processing unit 14 reads one tomographic image from the volume data in accordance with an operation on the operation panel 22 and causes the monitor 20 to display a tomographic image based on the tomographic image data. Further, the central processing unit 14 generates stereoscopic image data based on the volume data in accordance with an operation on the operation panel 22 and displays the stereoscopic image on the monitor 20.

  When displaying a stereoscopic image, a volume rendering method is preferably employed. Volume rendering method refers to each pixel in the depth direction on each line of sight (ray) extending from the viewpoint, obtains information indicating opacity by a predetermined pixel calculation, and obtains the final pixel calculation result Is a known rendering processing method in which the pixel value of the pixel corresponding to is used. According to the volume rendering method, the tissue located in the depth direction from the viewpoint is displayed three-dimensionally with brightness intensity.

(3) Three-dimensional focus observation mode In the three-dimensional focus observation mode, tomographic image processing for acquiring a plurality of tomographic images by the same operation as the three-dimensional B mode and a plurality of reflections over a three-dimensional space in the subject. Reflection distribution image processing for acquiring a distribution image is performed in a time division manner. The tomographic image data and the reflection distribution image data acquired in the focus observation mode are stored in the frame memory 18.

  The reflection distribution image processing will be described. The 3D therapy transmitter 72 repeatedly outputs a pulse modulation signal for focus observation to each HIFU transducer 60 at a predetermined period. Thereby, each HIFU transducer 60 repeatedly transmits pulse ultrasonic waves for focus observation at a predetermined cycle toward the respective focal points. At this time, as will be described later, the 3D treatment transmitter 72 determines the delay time of the pulse modulated wave for focus observation output to each HIFU transducer 60 based on the control vector output from the focus position controller 76. Adjust and control the position of the HIFU focus F.

  The observation three-dimensional probe 56 receives the focus observation pulse ultrasonic wave reflected in the subject. The observation three-dimensional probe 56 generates an electric signal based on the received pulse ultrasonic wave and outputs the electric signal to the 3D observation receiving unit 70. Similar to the operation in the three-dimensional B mode, also in the reflection distribution image processing in the three-dimensional focus observation mode, the 3D observation receiving unit 70 functions as a beam former of the received pulsed ultrasonic wave and performs one-dimensional scanning of the received beam. .

  The 3D observation receiving unit 70 generates beam data corresponding to the second harmonic component of the received pulsed ultrasonic wave, and outputs the second harmonic beam data to the image data generating unit 38. The 3D observation receiving unit 70 changes the direction of the received beam at a predetermined step angle every time one pulse ultrasonic wave transmitted from each HIFU transducer 60 and reflected in the subject is received. As a result, second harmonic beam data is generated in the direction of each received beam on the one-dimensional scanning plane 40.

  The 3D observation receiving unit 70 repeatedly performs one-dimensional scanning of the received beam on the subject by changing the swing angle for each one-dimensional scanning at a predetermined step angle. The image data generation unit 38 generates reflection distribution image data for each one-dimensional scan based on the second harmonic beam data group obtained for each one-dimensional scan, and the reflection distribution image data is stored in the central processing unit 14. It is stored in the frame memory 18 according to the control. A plurality of reflection distribution image data obtained by one-dimensional scanning repeatedly performed while changing the swing angle is stored in the frame memory 18 as focal volume data. As a result, a plurality of reflection distribution image data obtained over the three-dimensional space in the subject is stored in the frame memory 18 as the focus volume data.

  The central processing unit 14 refers to the frame memory 18 and selects and reads one tomographic image data from the volume data according to an operation on the operation panel 22, and further reflects from the focal volume data corresponding to the tomographic image. Select and read distribution image data. Then, the reflection distribution image is superimposed on the tomographic image and displayed on the monitor 20. In addition, the central processing unit 14 generates respective stereoscopic image data based on the volume data and the focal volume data in accordance with an operation on the operation panel 22 and displays each stereoscopic image on the monitor 20 in a superimposed manner.

  According to such processing, the reflection distribution image can be displayed so as to be superimposed on the tomographic image of the subject. By selecting an image including the image of the HIFU focal point F as the reflection distribution image, the state of the HIFU focal point F is displayed superimposed on the tomographic image. In addition, a stereoscopic image inside the subject and a stereoscopic image showing the HIFU focus F can be displayed in an overlapping manner. Thereby, the position of the HIFU focal point F is three-dimensionally shown.

  In the above description, the processing using the second harmonic component of the received pulsed ultrasonic wave has been described. However, even if the processing using the third-order or higher harmonic component of the received pulsed ultrasonic wave is executed, Good.

(4) Position control of HIFU focus The positional relationship between each HIFU transducer 60 and the HIFU focus F is constant when the propagation speed in the subject is uniform. However, when there is a discontinuous medium tissue in which the propagation speed of ultrasonic waves is different from that of other tissues, the ultrasonic waves are refracted at the boundary between the discontinuous medium tissue and the other tissues, and each HIFU transducer 60 and HIFU focal point F The positional relationship of changes. In this case, it may be difficult to adjust the HIFU focus F to the treatment site. Therefore, the three-dimensional ultrasonic diagnostic apparatus according to the present embodiment executes control for adjusting the position of the HIFU focus F to the target position.

  A process in which the ultrasonic diagnostic apparatus controls the position of the HIFU focus F will be described. The focus search unit 38A obtains focus search image data for each of a plurality of reflection distribution image data forming the focus volume data stored in the frame memory 18. The focus search image data may be focus search image data based on an average luminance value or focus search image data based on spatial frequency analysis. The focus search unit 38A stores a plurality of focus search image data obtained for the plurality of reflection distribution image data in the frame memory 18.

  Here, the plurality of focus search image data stored in the frame memory 18 do not necessarily have to be used as image data for monitor display. That is, the plurality of focus search image data may be used as focus search data for detecting the position of the HIFU focus F in the position control of the HIFU focus F.

  The focal position determination unit 74 refers to the plurality of focal point search image data stored in the frame memory 18 and obtains the position coordinate value of the HIFU focal point F. For example, the centroid of the pixel whose pixel value is not 0 among all the pixels indicated by the plurality of focus search image data is obtained as the position coordinate value of the HIFU focus F. The focal position determination unit 74 outputs the position coordinate value of the HIFU focal point F to the focal position control unit 76.

  The focal position control unit 76 acquires and holds a target coordinate value for the position of the HIFU focal point F in advance. This target coordinate value may be input to the focal position control unit 76 by an operation on the operation panel 22.

  The focal position control unit 76 obtains a control vector obtained by subtracting the position coordinate value of the HIFU focal point F from the target coordinate value, and outputs the control vector to the 3D treatment transmission unit 72. The 3D treatment transmitter 72 controls the delay time of the pulse modulation signal output to each HIFU transducer 60 so that the HIFU focus F moves in the direction and distance indicated by the control vector.

  According to such processing, the position of the HIFU focal point F can be adjusted to the position indicated by the target coordinate value without performing a mechanical operation on the HIFU head unit 52. Further, the target coordinate value can be input from the panel operation unit, and the position of the HIFU focus F can be adjusted. This facilitates the operation of adjusting the HIFU focus F to the treatment site.

  In addition to the process of controlling the position of the HIFU focus F, a process of displaying a plurality of focus search image data stored in the frame memory 18 on the monitor 20 may be executed. In this case, the central processing unit 14 refers to the frame memory 18, selects and reads one tomographic image data from the volume data, and further selects and reads the focus search image data corresponding to the tomographic image. Then, the focus search image is superimposed on the tomographic image and displayed on the monitor 20. Further, the central processing unit 14 generates stereo image data and focus stereo image data in the subject based on the volume data and the plurality of focus search image data, and causes the monitor 20 to superimpose and display the stereo images. May be executed.

  10 treatment observation probe, 12 signal processing unit, 14 central processing unit, 16 processing memory, 18 frame memory, 20 monitor, 22 operation panel, 24 bus line, 26 observation convex probe, 28, 60 HIFU transducer, 30 Observation transmission unit, 32 Observation reception unit, 34 Treatment transmission unit, 36 Timing control unit, 38 Image data generation unit, 38A Focus search unit, 40 One-dimensional scanning plane, 42 Transmission beam, 44, 48 Reception beam, 46 , 50 pulse ultrasound, 52 HIFU head unit, 54 head housing, 56 three-dimensional probe for observation, 58 HIFU transducer array, 62 rocking axis, 66 three-dimensional signal processing unit, 68 3D observation transmission unit, 70 3D Observation receiver, 72 3D therapy transmitter, 74 focal position determination unit, 76 focal position controller, F HIFU focus, ROI region of interest.

Claims (11)

A treatment transmitter for transmitting ultrasonic waves toward a focal point located in the subject;
A receiver that receives ultrasonic waves transmitted from the therapeutic transmitter and reflected in the subject while scanning a reception beam;
A reflection distribution data generation unit that generates ultrasonic reflection distribution data on the scanning plane of the reception beam based on the ultrasonic waves received by the reception unit;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to claim 1,
A focus search unit for obtaining focus search image data representing the position of the focus based on the ultrasonic reflection distribution data;
The focus search unit
Statistical value calculation means for obtaining a statistical value of a pixel value for each region of interest when the scanning plane is divided into a plurality of regions of interest based on the ultrasonic reflection distribution data;
Search image data acquisition means for setting the pixel value in each region of interest to a pixel value corresponding to the statistical value obtained for each region of interest and obtaining the focus search image data;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to claim 1,
A focus search unit for obtaining focus search image data representing the position of the focus based on the ultrasonic reflection distribution data;
The focus search unit
Fourier transform means for each region of interest formed by dividing the scanning plane into a plurality of regions for the ultrasonic reflection distribution data, and Fourier transform means for obtaining a spatial frequency distribution for each region of interest;
Search image data acquisition means for setting the pixel value in each region of interest to a pixel value corresponding to the spatial frequency distribution obtained for each region of interest and obtaining the focus search image data;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to claim 2 or 3,
The therapeutic transmitter includes a plurality of ultrasonic transducers,
The ultrasonic diagnostic apparatus further includes:
A focus position determination unit for determining the position of the focus based on the focus search image data;
A focal point for controlling the delay time of a signal applied to each ultrasonic transducer based on the difference between the focal position and the target focal position obtained by the focal position determining unit, and bringing the focal position closer to the target focal position. A position control unit;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to any one of claims 2 to 4,
An observation ultrasonic wave is transmitted toward the subject, and an observation transmission unit that scans the transmission beam of the observation ultrasonic wave in the scanning plane is provided.
The receiver is
Forming a reception beam having the same direction as the transmission beam of the observation ultrasonic wave, receiving the observation ultrasonic wave transmitted from the observation transmission unit and reflected in the subject,
The ultrasonic diagnostic apparatus further includes:
A tomographic image data generating unit that generates tomographic image data of the subject on the scanning plane based on the observation ultrasound received by the receiving unit;
An image display unit that displays an image based on the focus search image data, overlaid on the image based on the tomographic image data;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to any one of claims 1 to 4,
An observation ultrasonic wave is transmitted toward the subject, and an observation transmission unit that scans the transmission beam of the observation ultrasonic wave in the scanning plane is provided.
The receiver is
Forming a reception beam having the same direction as the transmission beam of the observation ultrasonic wave, receiving the observation ultrasonic wave transmitted from the observation transmission unit and reflected in the subject,
The ultrasonic diagnostic apparatus further includes:
A tomographic image data generating unit that generates tomographic image data of the subject on the scanning plane based on the observation ultrasound received by the receiving unit;
An image display unit for displaying an image based on the ultrasonic reflection distribution data, overlaid on the image based on the tomographic image data;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to claim 1,
A focus search unit that obtains focus search data representing the position of the focus based on the ultrasonic reflection distribution data;
The focus search unit
Statistical value calculation means for obtaining a statistical value for each region of interest when the scanning plane is divided into a plurality of regions of interest based on the ultrasonic reflection distribution data;
A focus search data acquisition means for obtaining the focus search data by setting a value corresponding to each region of interest to a value corresponding to the statistical value obtained for each region of interest;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to claim 1,
A focus search unit that obtains focus search data representing the position of the focus based on the ultrasonic reflection distribution data;
The focus search unit
Fourier transform means for each region of interest formed by dividing the scanning plane into a plurality of regions for the ultrasonic reflection distribution data, and Fourier transform means for obtaining a spatial frequency distribution for each region of interest;
A focus search data obtaining means for setting the value corresponding to each region of interest to a value corresponding to the spatial frequency distribution obtained for each region of interest and obtaining the focus search data;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to claim 7 or 8,
The therapeutic transmitter includes a plurality of ultrasonic transducers,
The ultrasonic diagnostic apparatus further includes:
A focal position determination unit for determining the focal position based on the focal point search data;
A focal point for controlling the delay time of a signal applied to each ultrasonic transducer based on the difference between the focal position and the target focal position obtained by the focal position determining unit, and bringing the focal position closer to the target focal position. A position control unit;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to any one of claims 1 to 9,
The ultrasound distribution distribution generating unit generates ultrasound reflection distribution data on a scanning plane of the received beam based on a higher-order harmonic component of the ultrasound received by the receiving unit. apparatus. A treatment transmitter for transmitting ultrasonic waves toward a focal point located in the subject;
A receiver that receives ultrasonic waves transmitted from the therapeutic transmitter and reflected in the subject while scanning a reception beam;
A processor that executes arithmetic processing on the ultrasonic waves received by the receiving unit;
An ultrasonic diagnostic program loaded into an ultrasonic diagnostic apparatus comprising:
In the processor,
An ultrasonic diagnostic program that executes processing for generating ultrasonic reflection distribution data on a scanning plane of the reception beam based on ultrasonic waves received by the receiving unit.