JP2012143389A - Ultrasonic diagnostic equipment and program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide ultrasonic diagnostic equipment capable of improving visibility of a puncture needle in a test environment using the standard ultrasonic diagnostic equipment, and a program.SOLUTION: In this ultrasonic image diagnostic equipment 1, a strain computing section computes a strain on a subject's tissue drawn on an ultrasonic image in each predetermined area of the ultrasonic image. An amount-of-characteristic computing section determines whether the strain computed in each predetermined area by the strain computing section exceeds a predetermined threshold. A control section makes puncture needle indicating information displayed in a position in the area where the amount-of-characteristic computing section determines that the strain exceeds the predetermined threshold.

Description

  Embodiments described herein relate generally to an ultrasonic diagnostic apparatus and a program.

  2. Description of the Related Art Conventionally, since an ultrasonic diagnostic apparatus can display an ultrasonic image in real time, it is often used when punctures such as biological tissue examination and radiofrequency ablation (RFA) are performed. For example, when performing tissue collection for a biological tissue examination, a doctor punctures the body with a puncture needle while confirming a target lesion with an ultrasonic image in real time, and performs tissue collection. In addition, when performing RFA, a doctor punctures a puncture needle to a lesion site while confirming a target lesion with an ultrasonic image in real time, and then radiates radio waves from the puncture needle.

  By the way, in the puncture using such an ultrasonic diagnostic apparatus, the puncture needle is not clearly depicted on the ultrasonic image, and it may be difficult to grasp how far the puncture needle has entered. It was. Therefore, in recent years, several techniques for improving the visibility of the puncture needle have been developed. In such a case, the visibility of the puncture needle is improved using dedicated hardware.

  However, in the prior art, dedicated hardware is necessary, and the available environment is limited.

JP 2008-178589 A

  The problem to be solved by the present invention is to provide an ultrasonic diagnostic apparatus and a program capable of improving the visibility of a puncture needle in an examination environment using a standard ultrasonic diagnostic apparatus.

  The ultrasonic diagnostic imaging apparatus according to the embodiment includes a calculation unit, a determination unit, and a display control unit. The calculation means calculates the distortion of the tissue of the subject depicted in the ultrasonic image for each predetermined area of the ultrasonic image. The determination unit determines whether the distortion calculated for each predetermined region by the calculation unit exceeds a predetermined threshold value. The display control means displays information indicating the puncture needle at the position of the determination area where the determination means determines that the strain has exceeded a predetermined threshold.

FIG. 1 is a diagram for explaining the overall configuration of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a diagram for explaining an example of the configuration of the image data control unit according to the first embodiment. FIG. 3 is a view for explaining the strain of the tissue accompanying the puncture needle entry. FIG. 4 is a diagram for explaining processing by the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 5 is a diagram for explaining a state where the entry of the puncture needle is stopped. FIG. 6 is a diagram for explaining processing of the image data generation unit when the entry of the puncture needle is stopped. FIG. 7 is a diagram for explaining processing of the image data generation unit 150 when the puncture needle is removed. FIG. 8 is a flowchart illustrating a processing procedure performed by the ultrasound diagnostic apparatus 1 according to the first embodiment. FIG. 9 is a diagram for explaining a modification of a region for calculating distortion.

(First embodiment)
First, the overall configuration of the ultrasonic diagnostic apparatus according to the first embodiment will be described with reference to FIG. FIG. 1 is a diagram for explaining the overall configuration of an ultrasonic diagnostic apparatus 1 according to the first embodiment. As shown in FIG. 1, the ultrasonic diagnostic apparatus 1 according to the first embodiment includes an ultrasonic probe 11, an input apparatus 12, a monitor 13, and an apparatus main body 100, and is connected to a network. .

  The ultrasonic probe 11 has a plurality of piezoelectric vibrators, and the plurality of piezoelectric vibrators generate ultrasonic waves based on a drive signal supplied from a transmission / reception unit 110 included in the apparatus main body 100 to be described later. A reflected wave from the specimen P is received and converted into an electric signal. The ultrasonic probe 11 includes a matching layer provided in the piezoelectric vibrator, a backing material that prevents propagation of ultrasonic waves from the piezoelectric vibrator to the rear, and the like.

  When ultrasonic waves are transmitted from the ultrasonic probe 11 to the subject P, the transmitted ultrasonic waves are reflected one after another at the discontinuous surface of the acoustic impedance in the body tissue of the subject P, and the ultrasonic probe is used as a reflected wave signal. 11 is received by a plurality of piezoelectric vibrators. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance at the discontinuous surface where the ultrasonic wave is reflected. The reflected wave signal when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface of the heart wall depends on the velocity component of the moving object in the ultrasonic transmission direction due to the Doppler effect. , Subject to frequency shift.

  A puncture adapter 11a is attached to the ultrasonic probe 11 according to the first embodiment so that a doctor performs punctures such as a biopsy and radiofrequency ablation treatment while referring to an ultrasonic image. A puncture needle 11b is attached to the puncture adapter 11a. The doctor inserts the puncture needle 11b attached to the puncture adapter 11a up to the target site of the subject P while referring to the ultrasonic image.

  In this embodiment, even when the subject P is scanned two-dimensionally by the ultrasonic probe 11 which is a one-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged in a row, the one-dimensional ultrasonic wave is used. A subject P is detected by an ultrasonic probe 11 that mechanically swings a plurality of piezoelectric vibrators of the probe or an ultrasonic probe 11 that is a two-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are two-dimensionally arranged in a grid. Even when scanning in three dimensions, it is applicable.

  The input device 12 includes a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, and the like, receives various setting requests from an operator of the ultrasonic diagnostic apparatus 1, and Transfer the received various setting requests.

  The monitor 13 displays a GUI (Graphical User Interface) for an operator of the ultrasonic diagnostic apparatus 1 to input various setting requests using the input device 12, and displays an ultrasonic image generated in the apparatus main body 100. Or display. For example, the monitor 13 displays an ultrasonic image indicating the position of the puncture needle pierced by the subject P.

  The apparatus main body 100 is an apparatus that generates an ultrasonic image based on the reflected wave received by the ultrasonic probe 11, and as shown in FIG. 1, the transmission / reception unit 110, the B-mode processing unit 120, and the Doppler processing unit 130. An image data control unit 140, an image data generation unit 150, an image memory 160, a control unit 170, and an internal storage unit 180.

  The transmission / reception unit 110 includes a trigger generation circuit, a delay circuit, a pulsar circuit, and the like, and supplies a drive signal to the ultrasonic probe 11. The pulsar circuit repeatedly generates rate pulses for forming transmission ultrasonic waves at a predetermined rate frequency. The delay circuit also sets the delay time for each piezoelectric vibrator necessary for determining the transmission directivity by focusing the ultrasonic wave generated from the ultrasonic probe 11 into a beam shape, and for each rate pulse generated by the pulser circuit. Give to. The trigger generation circuit applies a drive signal (drive pulse) to the ultrasonic probe 11 at a timing based on the rate pulse. In other words, the delay circuit arbitrarily adjusts the transmission direction from the piezoelectric vibrator surface by changing the delay time given to each rate pulse.

  The transmission / reception unit 110 includes an amplifier circuit, an A / D converter, an adder, and the like, and performs various processes on the reflected wave signal received by the ultrasonic probe 1 to generate reflected wave data. The amplifier circuit amplifies the reflected wave signal for each channel and performs gain correction processing, and the A / D converter is necessary for A / D converting the gain-corrected reflected wave signal to determine the reception directivity. The adder performs an addition process of the reflected wave signal processed by the A / D converter to generate reflected wave data. By the addition processing of the adder, the reflection component from the direction corresponding to the reception directivity of the reflected wave signal is emphasized.

  As described above, the transmission / reception unit 110 controls transmission directivity and reception directivity in ultrasonic transmission / reception. The transmission / reception unit 110 has a function capable of instantaneously changing delay information, a transmission frequency, a transmission drive voltage, the number of aperture elements, and the like under the control of the control unit 160 described later. In particular, the change of the transmission drive voltage is realized by a linear amplifier type oscillation circuit capable of instantaneously switching values or a mechanism for electrically switching a plurality of power supply units. Further, the transmission / reception unit 110 can transmit and receive different waveforms for each frame or rate.

  The B-mode processing unit 120 receives reflected wave data, which is a processed reflected wave signal subjected to gain correction processing, A / D conversion processing, and addition processing, from the transmission / reception unit 110, and performs logarithmic amplification, envelope detection processing, and the like. As a result, data (B mode data) in which the signal intensity is expressed by brightness is generated.

  Here, the B-mode processing unit 120 can change the frequency band to be visualized by changing the detection frequency. Further, the B-mode processing unit 120 can perform detection processing with two detection frequencies in parallel on one reception data.

  By using the function of the B-mode processing unit 120, the ultrasonic contrast agent (microbubbles, bubbles) flowing in the region of interest is detected from one received data in the region of interest of the subject P into which the ultrasound contrast agent has been injected. The reflected wave data used as the reflection source can be separated from the reflected wave data using the tissue existing in the region of interest as the reflection source, and the image data generation unit 150 described later visualizes the flowing bubbles with high sensitivity. In order to observe the contrast image and the morphology, a tissue image obtained by imaging the tissue can be generated.

  The Doppler processing unit 130 performs frequency analysis on velocity information from the reflected wave data received from the transmission / reception unit 110, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and moving body information such as average velocity, dispersion, and power. Is generated for multiple points (Doppler data).

  More specifically, the Doppler processing unit 130 is a processing unit capable of executing a tissue Doppler imaging (TDI: Tissue Doppler Imaging) and a color Doppler method. That is, the Doppler processing unit 130 is a processing unit that acquires tissue motion information (tissue motion information) within a scanning range and generates tissue Doppler data for generating a tissue Doppler image indicating the tissue dynamics. . In addition, the Doppler processing unit 130 obtains blood flow motion information (blood flow motion information) within the scanning range and generates color Doppler data for generating a color Doppler image indicating the blood flow dynamics. Part.

  The image data control unit 140 executes various controls for generating an image for display from the B mode data generated by the B mode processing unit 120 and the Doppler data generated by the Doppler processing unit 130. For example, the image data control unit 140 calculates a feature amount used for highlighting the puncture needle 11b based on the Doppler data. The feature amount will be described in detail later.

  The image data generation unit 150 generates an ultrasound image from the B mode data generated by the B mode processing unit 120 and the Doppler data generated by the Doppler processing unit 130. Specifically, the image data generation unit 150 converts (scan converts) a scanning line signal sequence of ultrasonic scanning into a scanning line signal sequence of a video format typified by a television or the like, so that B-mode data or Doppler is obtained. An ultrasonic image (B-mode image or Doppler image) for display is generated from the data. Further, the image data generation unit 150 generates an ultrasonic image for display in which the puncture needle 11b stabbed in the subject P is highlighted using the processing result of the image data control unit 140. The image data generation unit 150 stores the generated ultrasonic image for display in the image memory 160. The generation of the display image in which the puncture needle 11b is highlighted by the image data generation unit will be described in detail later.

  The image memory 160 stores the Raw data (B mode data and Doppler data) generated by the B mode processing unit 120 and the Doppler processing unit 130, and the display ultrasonic image generated by the image data generation unit 150. Further, the image memory 160 stores a processing result by the image data control unit 140. Furthermore, the image memory 160 stores an output signal (RF: Radio Frequency) immediately after passing through the transmission / reception unit 110, an image luminance signal, various raw data, and the like as necessary.

  The control unit 170 controls the entire processing in the ultrasonic diagnostic apparatus 1. Specifically, the control unit 170 is based on various setting requests input from the operator via the input device 12 and various control programs and various setting information read from the internal storage unit 180. Control processing of the mode processing unit 120, the Doppler processing unit 130, the image data control unit 140, and the image data generation unit 150, or control so that an ultrasonic image stored in the image memory 160 is displayed on the monitor 13. To do.

  The internal storage unit 180 stores a control program for performing ultrasonic transmission / reception, image processing, and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), and various data such as a diagnostic protocol. The internal storage unit 180 is also used for storing images stored in the image memory 160 as necessary.

  The overall configuration of the ultrasonic diagnostic apparatus according to the first embodiment has been described above. With this configuration, the ultrasonic diagnostic apparatus 1 according to the first embodiment is a puncture needle in an examination environment using a standard ultrasonic diagnostic apparatus by the processing of the image data control unit 140 described in detail below. It is comprised so that the visibility of can be improved.

  Hereinafter, the processing of the image data control unit 140 according to the first embodiment will be described in detail with reference to FIG. In the first embodiment, processing after the operator starts a puncture using the puncture needle 11b will be described.

  FIG. 2 is a diagram for explaining an example of the configuration of the image data control unit 140 according to the first embodiment. As shown in FIG. 2, the image data control unit 140 includes a black and white image data processing unit 141 and a color image data processing unit 142, and an image data generation unit 150 and an image memory 160 via a bus (not shown). Connected.

  The black and white image data processing unit 141 executes various processes related to the generation of a black and white image. As shown in FIG. 2, the color image data processing unit 142 includes a speed average extraction unit 142a, a distortion calculation unit 142b, and a feature amount calculation unit 142c, and uses tissue Doppler data generated by the tissue Doppler method. Various processes for improving the visibility of the puncture needle are executed.

  Specifically, in the color image data processing unit 142, the velocity average extraction unit 142a, the strain calculation unit 142b, and the feature amount calculation unit 142c are configured to remove the puncture needle from the body surface based on the velocity component included in the tissue Doppler data. The strain of the tissue caused by the puncture is calculated, and the position of the puncture needle is specified from the calculated strain.

  FIG. 3 is a view for explaining the strain of the tissue accompanying the puncture needle entry. FIG. 3 shows a case where the puncture with the puncture needle 11b is executed while the ultrasonic probe 11 is applied to the body surface 30 of the subject P. FIG. 3 shows the case where the position of the puncture needle 11b is specified using the tissue Doppler method. Moreover, the arrow 21 shown in FIG. 3 shows the advancing direction of the puncture needle 11b. Moreover, the arrow 22 shown in FIG. 3 shows the force with which the puncture needle 11b presses a tissue. An arrow 23 shown in FIG. 3 indicates the direction of the ultrasonic beam transmitted by the raster ultrasonic probe 11. A circle 24 shown in FIG. 3 indicates the sampling position of the tissue Doppler data.

  For example, as shown in FIG. 3, when the puncture needle 11b enters from the body surface 30 in the direction of the arrow 21, a force 22 is generated to push the surrounding tissue around the puncture needle 11b. That is, as the puncture needle 11b enters, distortion occurs in the tissue around the puncture needle 11b. In the scan using the tissue Doppler method, the velocity component is included in the tissue Doppler data collected at the sampling position 24 or the like. The ultrasonic diagnostic apparatus 1 according to the first embodiment specifies the position of the puncture needle by calculating the strain generated in the tissue around the puncture needle 11b based on the velocity component included in the tissue Doppler data.

  Returning to FIG. 2, the velocity average extraction unit 142 a extracts the velocity average for each predetermined region of the ultrasonic image based on the velocity component included in the Doppler data at the position corresponding to the predetermined region. For example, the velocity average extraction unit 142a extracts the velocity average for each pixel of the ultrasonic image based on the velocity component included in the Doppler data at the position corresponding to the pixel. For example, the speed average extraction unit 142a extracts a speed average for each sample of a scan using the tissue Doppler method.

  FIG. 4 is a diagram for explaining processing by the ultrasonic diagnostic apparatus 1 according to the first embodiment. FIG. 4A is a diagram schematically illustrating processing by the speed average extraction unit 142a. 4B and 4C are diagrams illustrating processing of the image data generation unit 150 to be described later. Note that (B) and (C) in FIG. 4 will be described in detail later.

  For example, as shown in FIG. 4A, the speed average extraction unit 142 a determines the speed of “raster: 1, sample: 1” from the speed component, dispersion component, and power component of “raster: 1, sample: 1”. Extract the average. Then, the velocity average extraction unit 142a calculates the coordinates (phase Cos, phase Sin) of the sample at a predetermined phase using the extracted dispersion component and power component.

  After that, the speed average extraction unit 142a sets a value obtained by multiplying each calculated coordinate by the variance component as a smoothing value. Then, the velocity average extraction unit 142a calculates a value obtained by taking the quotient of the total number of pixels of the ultrasonic image from the smoothing value as the velocity average value. That is, as shown in FIG. 3, since the puncture needle 11b enters obliquely with respect to the raster direction, the speed average extraction unit 142a extracts the speed average as coordinates in order to consider the vector. Then, the speed average extraction unit 142 a stores the extracted speed average data of “raster: 1, sample: 1” in the image memory 160. Similarly, the speed average extraction unit 142a performs the above-described processing on all raster samples, extracts the speed average for each sample, and stores the average in the image memory 160. Then, the speed average extraction unit 142a sequentially extracts the speed averages of the samples in the scanned frame and stores them in the image memory 160.

  Returning to FIG. 2, the strain calculation unit 142b calculates the strain of the tissue of the subject depicted in the ultrasound image for each predetermined region of the ultrasound image. Specifically, the strain calculation unit 142b calculates the strain using the speed average extracted by the speed average extraction unit 142a. For example, the distortion calculation unit 142b calculates the distortion at the position of each sample using the average speed for each sample stored in the image memory 160.

  For example, the distortion calculation unit 142b reads the speed average for each sample stored in the image memory 160, and takes the reciprocal of the arc tangent of the read speed average. Then, the distortion calculation unit 142b integrates a value obtained by integrating the result of taking the quotient of the circumference from the time interval of the scanning line and 128 that converts a negative value into a positive value, to the reciprocal value. Is calculated as distortion. Then, the distortion calculation unit 142b stores the calculated distortion information in the image memory 160. Similarly, the distortion calculation unit 142b calculates the distortion at the position of each sample using all the velocity averages stored in the image memory 160. Then, the distortion calculation unit 142b sequentially calculates the distortion of each sample in the scanned frame and stores it in the image memory 160.

  The feature amount calculation unit 142c determines whether or not the distortion calculated for each predetermined region by the distortion calculation unit 142b exceeds a predetermined threshold. For example, the feature amount calculation unit 142c sequentially determines whether or not the distortion of the position of each sample stored in the image memory 160 exceeds a predetermined threshold for the scanned frames. Then, the feature amount calculation unit 142c sequentially stores the determination result in association with the ultrasonic image of the determined frame in the image memory 160.

  Here, the feature amount calculation unit 142c further determines whether or not the strain calculated by the strain calculation unit 142b is a strain caused by the movement of the puncture needle, and determines that the strain is caused by the movement of the puncture needle. In such a case, it is determined whether or not the distortion exceeds a predetermined threshold value. Specifically, the feature amount calculation unit 142c determines whether or not the distortion exceeds a predetermined threshold when the position where the distortion occurs, the manner of distortion, and the like are caused by the movement of the puncture needle. For example, when the calculated distortion is a distortion caused by the movement of the subject P, the feature amount calculation unit 142c does not determine whether the distortion exceeds a predetermined threshold. In other words, the feature amount calculation unit 142c performs a determination process on the distortion caused by the movement of the puncture needle. In addition, as information for determining whether or not the distortion is caused by the movement of the puncture needle, for example, a position where the distortion is generated, a degree of the distortion, a part that moves spontaneously, and the like are used.

  The image data generation unit 150 generates an image depicting information indicating the puncture needle at the position of the determination area where the distortion is determined to have exceeded the predetermined threshold by the feature amount calculation unit 142c. For example, the image data generation unit 150 generates an image in which the position of the sample whose distortion exceeds a predetermined threshold in the ultrasonic image stored in the image memory 160 is the tip of the puncture needle. That is, the image data generation unit 150 sequentially generates an image using a sample position where distortion exceeds a predetermined threshold in a plurality of time-sequential ultrasonic images as the tip of the puncture needle. At this time, an image is generated in which the puncture needle drawn in the immediately preceding image is continuously drawn.

  For example, the image data generation unit 150 generates an enhanced image in which the position of the determination region is enhanced as information indicating the puncture needle. As an example of the display, the image data generation unit 150 sequentially draws information indicating the puncture needle at each strain position of a plurality of time-sequential ultrasonic images, for example, ( As shown in B), an image in which the position of the puncture needle is emphasized is generated.

  Further, the image data generation unit 150 enhances the position of the determination region and generates a transmission image through which the tissue drawn in the determination region is transmitted. As an example of display, the image data generation unit 150 sequentially superimposes transparency information on the distortion positions of each of a plurality of time-sequential ultrasonic images, for example, in FIG. As shown, a transmission image in which the tissue depicted in the ultrasonic image is transmitted is generated. That is, the control unit 170 displays information indicating the puncture needle at the position of the determination pixel where the distortion is determined to have exceeded the predetermined threshold by the feature amount calculation unit 142c. In addition, as information indicating the puncture needle, the control unit 170 enhances the position of the determination pixel, or a transmission image that enhances the position of the determination pixel and transmits the tissue drawn on the determination pixel. Will be displayed.

  Here, a case where the entry of the puncture needle is stopped will be described. FIG. 5 is a diagram for explaining a state where the entry of the puncture needle is stopped. For example, as shown in FIG. 5A, when the puncture needle 11b has entered in the direction of the arrow 21, a force 22 for pressing the tissue is generated on the puncture needle 11b. That is, since the tissue is distorted, the position of the puncture needle cannot be specified, and information indicating the puncture needle can be displayed as shown in (A) of 5.

  On the other hand, for example, as shown in FIG. 5B, when the approach in the direction of the arrow 21 is stopped and the force 22 for pushing the tissue is not generated, the position of the tip of the puncture needle is not known. That is, as shown in FIG. 5B, when the puncture needle is stopped, information indicating the puncture needle is not drawn.

  Therefore, immediately after generating the image depicting the puncture needle, the image data generation unit 150 displays the current value when the feature amount calculation unit 142c determines that all distortions do not exceed the predetermined threshold. A moving image in which information indicating the puncture needle is drawn is continuously generated. Specifically, the image data generation unit 150 continuously generates the image generated immediately before when the puncture needle is stopped.

  FIG. 6 is a diagram for explaining processing of the image data generation unit 150 when the entry of the puncture needle is stopped. For example, as illustrated in FIG. 6, when the entry of the puncture needle 11 b in the direction of the arrow 21 is stopped, the image data generation unit 150 acquires the distortion position from the past image and acquires the acquired distortion. An image depicting information indicating the puncture needle at a position is generated.

  Next, a case where the puncture needle is removed will be described. When the puncture needle is withdrawn, the puncture needle is temporarily stopped, and then a force opposite to the approach is generated. That is, a force opposite to the force pushed from the puncture needle is applied to the tissue, and the average speed is a negative value. Therefore, after the image data generation unit 150 continuously generates information indicating the puncture needles displayed in the past, the feature amount calculation unit 142c determines that the distortion in a direction different from the distortion at the time of entry exceeds a predetermined threshold value. If it is determined, an image in which a part of the information indicating the puncture needle displayed at the present time is deleted is generated based on the movement amount of the puncture needle and the feature of the image.

  FIG. 7 is a diagram for explaining processing of the image data generation unit 150 when the puncture needle is removed. For example, as shown in FIG. 7, when the puncture needle 11b is pulled out with a force 25 that is pulled out in the direction of the body surface 30, as shown in FIG. 7, the image data generation unit 150 calculates the area extracted by speed averaging and pattern matching. An image from which the information on the puncture needle corresponding to the calculated area is deleted is generated.

  As described above, the color image data processing unit 142 calculates the strain of the tissue based on the velocity component, the dispersion component, and the power component included in the tissue Doppler data, and sets the calculated strain position as the tip of the puncture needle. Thus, the ultrasonic diagnostic apparatus 1 according to the first embodiment makes it possible to improve the visibility of the puncture needle in an examination environment using a standard ultrasonic diagnostic apparatus. Note that the calculation of the speed average and distortion executed in the ultrasonic diagnostic apparatus 1 according to the first embodiment described above may be realized using various known methods.

  Next, processing of the ultrasonic diagnostic apparatus 1 according to the first embodiment will be described with reference to FIG. Note that FIG. 8 shows processing when a puncture operation using a puncture needle is performed.

  FIG. 8 is a flowchart illustrating a processing procedure performed by the ultrasound diagnostic apparatus 1 according to the first embodiment. As shown in FIG. 8, in the ultrasonic diagnostic apparatus 1 according to the first embodiment, when the function for improving the visibility of the puncture needle is activated (Yes in step S101), the velocity average extraction unit 142a The velocity, variance, and power for each sample are extracted from the Doppler data (step S102). Then, the speed average extraction unit 142a calculates a speed average (step S103).

  Thereafter, the strain calculation unit 142b calculates the strain of all samples (step S104), and determines the region where the strain is maximum as the tip of the puncture needle (step S105). Then, the image data generation unit 150 generates an image that connects the tip regions of the puncture needle in each frame, and the control unit 170 displays the image as a puncture needle (step S106).

  Then, the strain calculation unit 142b determines whether or not a speed average is calculated (step S107). Here, when the speed average is not calculated (No in step S107), the image data generation unit 150 determines that the movement of the puncture needle has stopped, and renders information indicating the puncture needle at the position of the latest puncture needle. The generated image is generated, and the control unit 170 displays the generated image (step S108).

  Thereafter, the strain calculation unit 142b determines whether or not the speed average shows a negative value (step S109). Here, when the speed average shows a negative value (Yes at Step S109), the image data generation unit 150 determines that the puncture needle has been removed, and the area where the puncture needle has been removed by the speed average and pattern matching is determined. An image is generated by calculating and deleting the puncture needle in the calculated area, and the control unit 170 displays the generated image (step S110).

  Thereafter, the strain calculation unit 142b determines whether or not a speed average is calculated (step S111). Here, when the average speed is calculated (Yes at Step S111), the image data generation unit 150 returns to Step S110 and continues the processing. On the other hand, when the speed average is not calculated (No at Step S111), the ultrasonic diagnostic apparatus 1 according to the first embodiment determines that the puncture needle has been completely removed (Step S112), and ends the process.

  As described above, according to the first embodiment, the strain calculation unit 142b calculates the strain of the tissue of the subject depicted in the ultrasound image for each pixel of the ultrasound image. Then, the feature amount calculation unit 142c determines whether the distortion calculated for each pixel by the distortion calculation unit 142b exceeds a predetermined threshold value. Then, the control unit 170 generates an image for displaying information indicating the puncture needle at the position of the determination pixel where the distortion is determined to have exceeded the predetermined threshold by the feature amount calculation unit 142c. Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment makes it possible to improve the visibility of the puncture needle in an examination environment using a standard ultrasonic diagnostic apparatus.

  In addition, according to the first embodiment, the control unit 170 emphasizes the position of the determination pixel as the information indicating the puncture needle, or emphasizes the position of the determination pixel and is rendered on the determination pixel. A transmission image through which the tissue is transmitted is displayed. Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment makes it possible to display the puncture needle without hiding the portion depicted in the ultrasonic image.

  Further, according to the first embodiment, the control unit 170 immediately after displaying the information indicating the puncture needle, when the feature amount calculation unit 142c determines that all distortions do not exceed the predetermined threshold value. Continuously displays information indicating the puncture needle currently displayed. Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment makes it possible to provide the operator with positional information of the puncture needle even when the entry of the puncture needle is stopped.

  Further, according to the first embodiment, the feature amount calculation unit 142c further determines whether or not the strain calculated by the strain calculation unit 142b is a strain caused by the movement of the puncture needle, and moves the puncture needle. When it is determined that the distortion is caused by the above, it is determined whether the distortion exceeds a predetermined threshold. Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment makes it possible to efficiently specify the position of the puncture needle.

  In addition, according to the first embodiment, the control unit 170 continuously displays information indicating the puncture needle that has been displayed in the past, and then the feature amount calculation unit 142c applies a predetermined distortion in a direction different from the distortion. If it is determined that the threshold value is exceeded, the display of the information indicating the puncture needle that is currently displayed is terminated based on the amount of movement of the puncture needle and the characteristics of the image. Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment makes it possible to provide the operator with positional information of the puncture needle even when the puncture needle is removed.

(Second Embodiment)
Although the first embodiment has been described so far, the present invention may be implemented in various different forms other than the first embodiment described above.

(1) Range for calculating distortion In the first embodiment described above, the case of calculating the distortion of all samples in a frame has been described. However, the disclosed technique is not limited to this, and may be, for example, a case where the distortion of a sample within a range specified by the operator is calculated.

  Specifically, the strain calculation unit 142b calculates the strain of the tissue depicted in the predetermined region for each predetermined region included in an arbitrary range of the ultrasonic image. FIG. 9 is a diagram for explaining a modification of a region for calculating distortion. For example, as shown in FIG. 9, the strain calculation unit 142b calculates the strain of the tissue depicted in the pixels included in the region 11d between the puncture guides 11c. Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment makes it possible to reduce the processing load for specifying the position of the puncture needle.

(2) Area for which distortion is to be calculated In the first embodiment described above, the case where distortion is calculated for each pixel has been described. However, the disclosed technique is not limited to this, and for example, the distortion may be calculated for each arbitrary region of the ultrasonic image.

  As described above, according to the first embodiment and the second embodiment, the ultrasonic diagnostic apparatus of the present embodiment improves the visibility of the puncture needle in an examination environment using a standard ultrasonic diagnostic apparatus. Make it possible.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus 11 Ultrasonic probe 11a Puncture adapter 11b Puncture needle 12 Input apparatus 13 Monitor 100 Apparatus main body 142a Speed average extraction part 142b Strain calculation part 142c Feature-value calculation part 170 Control part

Claims (8)

Calculation means for calculating the distortion of the tissue of the subject depicted in the ultrasonic image for each predetermined region of the ultrasonic image;
Determining means for determining whether or not the distortion calculated for each predetermined region by the calculating means exceeds a predetermined threshold;
Display control means for displaying information indicating a puncture needle at a position of a determination area where the determination means determines that the strain has exceeded a predetermined threshold;
An ultrasonic diagnostic apparatus comprising:   The display control means, as information indicating the puncture needle, is an enhanced image in which the position of the determination region is emphasized, or transmission through which the tissue drawn in the determination region is transmitted while enhancing the position of the determination region The ultrasonic diagnostic apparatus according to claim 1, wherein an image is displayed.   The ultrasonic diagnostic apparatus according to claim 1, wherein the calculation unit calculates the distortion using one of a tissue Doppler method and a feature comparison of the ultrasonic image.   If the display control means determines that all the distortions do not exceed the predetermined threshold immediately after displaying the information indicating the puncture needle, the display control means displays the puncture needle currently displayed. The ultrasonic diagnostic apparatus according to claim 1, wherein the information to be displayed is continuously displayed.   The determination unit further determines whether or not the strain calculated by the calculation unit is a strain caused by the movement of the puncture needle, and determines that the strain is caused by the movement of the puncture needle. The ultrasonic diagnostic apparatus according to claim 1, wherein a determination is made as to whether or not the threshold value exceeds a predetermined threshold value.   When the display control means continuously displays information indicating the puncture needle that has been displayed in the past, and the determination means determines that a strain in a direction different from the strain has exceeded the predetermined threshold value, 5 ends the display of information indicating the puncture needle currently displayed based on the amount of movement of the puncture needle and the characteristics of the image. Ultrasound diagnostic equipment.   The said calculation means calculates the distortion | strain of the structure | tissue of the subject imaged by the said predetermined area | region for every said predetermined area | region included in the arbitrary ranges of the said ultrasonic image. The ultrasonic diagnostic apparatus according to any one of the above. For each predetermined region of the ultrasound image, a calculation procedure for calculating the distortion of the tissue of the subject depicted in the ultrasound image;
A determination procedure for determining whether or not the strain calculated for each predetermined region by the calculation procedure exceeds a predetermined threshold;
A display control procedure for displaying information indicating a puncture needle at a position of a determination region in which distortion is determined to have exceeded a predetermined threshold by the determination procedure;
A display control program for causing a computer to execute the above.

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