JP2008012150A - Ultrasonic diagnostic equipment and control program of ultrasonic diagnostic equipment - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide ultrasonic diagnostic equipment generating three-dimensional images allowing an easy view of a puncture needle, and three-dimensional images facilitating to understand the spatial positional relationship between the puncture needle and a tissue. <P>SOLUTION: A transceiver section 3 allows an ultrasonic probe 2 to transmit ultrasonic waves of relatively high transmission frequency to acquire first volume data, and allows the ultrasonic probe 2 to transmit ultrasonic waves of relatively low transmission frequency to acquire second volume data. An image generation section 6 composes the first volume data and the second volume data to generate composed data and generates three-dimensional image data from the composed data, as for the first volume data, in compliance with image generation conditions fitted to the display of the tissue and, as for the second volume data, in compliance with image generation conditions fitted to the display of an electrode needle. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus that generates three-dimensional image data, and a control program for the ultrasonic diagnostic apparatus, and in particular, an ultrasonic diagnostic apparatus for supporting radio frequency ablation (RFA), and The present invention relates to a control program for an ultrasonic diagnostic apparatus.

  In recent years, radiofrequency ablation therapy has been increasingly used as one of the treatment methods particularly for liver cancer. Radiofrequency ablation therapy is a treatment in which a thin electrode needle is inserted into a cancer tissue and the cancer tissue is cauterized by the heat generated by flowing a radio wave having a relatively low frequency, thereby necrotizing the cancer tissue. is there.

  An ultrasonic diagnostic apparatus is often used when an electrode needle (hereinafter referred to as “puncture needle”) is inserted into a cancer tissue. That is, by using the ultrasonic diagnostic apparatus, the puncture needle and the cancer tissue are simultaneously visualized as an ultrasonic image, and the puncture needle is inserted into the cancer tissue while referring to the ultrasonic image. Ultrasonic imaging is also used for confirming the state during cauterization and the cautery range after cauterization.

  By the way, there are a plurality of types of puncture needles used for radiofrequency ablation therapy. FIG. 15 shows an example of a puncture needle. FIG. 15 is a perspective view showing a puncture needle. A puncture needle 600 shown in FIG. 15 is an unfolded puncture needle, and a plurality of electrode needles 602 come out from a slightly thicker needle (outer needle) 601 so as to be opened like a trumpet as a whole. . The plurality of electrode needles 602 are bent as they are inserted into the cancer tissue. Even when a straight puncture needle is used, the puncture needle may bend in the tissue.

  The reflection of ultrasonic waves from the puncture needle depends on the angle between the transmission direction of the ultrasonic waves and the direction of the reflecting surface of the puncture needle. Depending on this angle, the reflection of ultrasonic waves from the puncture needle cannot be observed. In some cases, the puncture needle cannot be displayed on the ultrasonic image. For example, since the puncture needle is curved in the tissue as described above, the reflection of the ultrasonic wave from the puncture needle cannot be observed depending on the angle of the curve, and the puncture needle may not be displayed on the ultrasonic image. In addition, a problem that it is difficult to see the tip of the puncture needle has been known. Various proposals for solving these problems have been made.

  For example, there is known an ultrasonic diagnostic apparatus that generates a color flow image by detecting a Doppler frequency shift signal, adjusts the gain of the color flow image, and superimposes and displays the color flow image on a B-mode image. (For example, Patent Document 1).

  There is also known an ultrasonic diagnostic apparatus that extracts a high luminance part and a part where the luminance is greatly changed, and colors the part and superimposes it on a tomographic image (for example, Patent Document 2). Since it is considered that the portion where the luminance is greatly changed corresponds to the puncture needle, the portion is extracted and superimposed on the ultrasonic image.

  Also, the difference between the tomographic image data acquired before the insertion of the puncture needle and the tomographic image data acquired after the insertion is obtained, and the difference is added to the tomographic image data acquired after the insertion and displayed. An ultrasonic diagnostic apparatus is known (for example, Patent Document 3).

  There is also known an ultrasonic diagnostic apparatus that irradiates an ultrasonic beam from a direction perpendicular to the puncture needle by deflecting the ultrasonic beam according to the insertion angle of the puncture needle (for example, Patent Document 4).

  The above-described ultrasonic diagnostic apparatus according to the related art is an apparatus that acquires two-dimensional image data (tomographic image data) representing a two-dimensional cross section. In the case of using a two-dimensional image, when the puncture needle is deviated from a two-dimensional surface (hereinafter, sometimes referred to as “scanning surface”) formed by the ultrasonic beam, that is, the puncture needle moves across the scanning surface. When penetrating, there is a problem that imaging of the puncture needle becomes difficult. In particular, in radiofrequency ablation therapy, when a plurality of curved puncture needles are used as described above, it is difficult to observe the puncture needle using only a two-dimensional image. The surgeon who performs treatment determines whether or not the puncture needle is inserted into the cancer tissue by grasping the spatial positional relationship between the cancer tissue and the puncture needle. It is difficult to grasp the spatial positional relationship.

  Incidentally, in recent years, an ultrasonic transducer is provided with a one-dimensional ultrasonic probe arranged in a predetermined direction (scanning direction), and the ultrasonic transducer is mechanically oscillated in a direction orthogonal to the scanning direction (oscillation direction). Thus, a mechanical ultrasonic diagnostic apparatus capable of acquiring data three-dimensionally is known. This mechanical ultrasonic diagnostic apparatus acquires a plurality of two-dimensional image data while mechanically reciprocating an ultrasonic transducer, generates three-dimensional volume data based on the plurality of two-dimensional image data, Three-dimensional image data is generated.

  There is also known a three-dimensional ultrasonic diagnostic apparatus that includes a two-dimensional ultrasonic probe in which ultrasonic transducers are arranged in a lattice shape (matrix shape) and can acquire three-dimensional volume data.

  Since the mechanical ultrasonic diagnostic apparatus and the three-dimensional ultrasonic diagnostic apparatus can use the three-dimensional image data, it is possible to overcome the problems in the case where only the two-dimensional image is used. It was.

  For example, when an ultrasonic image is acquired with a plurality of scanning planes, a high-intensity region is extracted from the ultrasonic image and regarded as a puncture needle part, and the high-intensity region (puncture needle) is displaced from a predetermined reference plane An ultrasonic diagnostic apparatus that issues a warning when it is determined is known (for example, Patent Document 5). There is also known an ultrasonic diagnostic apparatus that estimates the position of a puncture needle from three-dimensional image data and determines the cross-sectional position in the three-dimensional image using the estimation result (for example, Patent Document 6).

Japanese Patent Laid-Open No. 7-275248 JP 2000-107178 A JP 2001-269339 A JP 2004-208859 A JP 2005-342128 A JP 2000-185041 A

  As described above, various proposals have been made in the past. However, the problem that the puncture needle may be difficult to see even if the puncture needle is included in the imaging region is solved only by using three-dimensional image data. There is still room for improvement in making the puncture needle easier to see.

  Moreover, in the ultrasonic diagnostic apparatus according to the conventional technique, it is difficult to grasp the spatial positional relationship between the cancer tissue and the puncture needle. This is because it is difficult to see the puncture needle itself, and there is not always a great difference in the luminance value of the ultrasonic image between the puncture needle and the cancer tissue. If there is no significant difference in the luminance value of the ultrasound image, it is difficult to distinguish between the puncture needle and the cancer tissue on the ultrasound image, so it is possible to grasp the spatial positional relationship between the cancer tissue and the puncture needle. It becomes difficult. As a result, it becomes difficult to determine whether or not the puncture needle is inserted into the cancer tissue.

  The present invention solves the above-described problem, and an ultrasonic diagnostic apparatus capable of generating an image that makes it easy to see the puncture needle and that allows easy understanding of the spatial positional relationship between the puncture needle and tissue, and an ultrasonic wave An object is to provide a control program for a diagnostic apparatus.

  In the first aspect of the present invention, the first volume data is acquired by transmitting an ultrasonic wave to the subject at the first transmission frequency, and the second transmission frequency is lower than the first transmission frequency. An acquisition means for acquiring the second volume data by transmitting an ultrasonic wave to the subject, a combining means for generating the combined data by combining the first volume data and the second volume data; An ultrasonic diagnostic apparatus comprising: image generation means for generating three-dimensional image data based on the synthesized data.

  The invention according to claim 11 transmits ultrasonic waves in a first direction, acquires first volume data in the first direction, and transmits ultrasonic waves in a plurality of directions including the first direction. By transmitting, the acquisition means for acquiring the volume data for each direction, and the data constituting each volume data acquired for each direction, the data below a predetermined threshold is relatively Threshold processing means for converting to a lower voxel value, addition means for adding the volume data in each direction subjected to the threshold processing, and combining the first volume data and the volume data after the addition An ultrasonic diagnostic apparatus comprising: a synthesizing unit that generates; and an image generating unit that generates three-dimensional image data based on the synthesized data.

  The invention according to claim 12 causes the computer to acquire the first volume data by transmitting an ultrasonic wave to the subject at the first transmission frequency, and the second is lower in frequency than the first transmission frequency. An acquisition function for acquiring the second volume data by transmitting an ultrasonic wave to the subject at a transmission frequency of, and a combination for generating the combined data by combining the first volume data and the second volume data A control program for an ultrasonic diagnostic apparatus, which executes a function and an image generation function for generating three-dimensional image data based on the synthesized data.

  According to the present invention, by scanning with ultrasonic waves having a relatively high transmission frequency (first transmission frequency), a three-dimensional image that allows easy viewing of the tissue is obtained, and a relatively low transmission frequency (second transmission frequency). By scanning with the ultrasonic wave, a three-dimensional image in which the puncture needle is easy to see is obtained. Then, the first volume data obtained with ultrasonic waves with a relatively high transmission frequency and the second volume data obtained with ultrasonic waves with a relatively low transmission frequency are synthesized, and based on the synthesized data By generating the three-dimensional image data, a three-dimensional image in which the spatial positional relationship between the tissue and the puncture needle can be easily grasped is obtained.

[First Embodiment]
The configuration of the ultrasonic diagnostic apparatus according to the first embodiment of the present invention will be described with reference to FIG. FIG. 1 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus according to the first embodiment of the present invention.

  The ultrasonic diagnostic apparatus 1 according to the first embodiment uses the first volume data obtained by scanning with ultrasonic waves having a relatively high transmission frequency (first transmission frequency) and relatively low transmission. The second volume data obtained by scanning with ultrasonic waves of the frequency (second transmission frequency) is synthesized, and three-dimensional image data is generated based on the synthesized volume data. By scanning with ultrasonic waves with a relatively high transmission frequency, a three-dimensional image easy to see the tissue can be obtained, and by scanning with ultrasonic waves with a relatively low transmission frequency, a three-dimensional image easy to see the puncture needle can be obtained. . Therefore, according to the three-dimensional image data generated based on the volume data obtained by combining the first volume data and the second volume data, it is possible to easily grasp the spatial positional relationship between the tissue and the puncture needle. It becomes possible. Hereinafter, each part of the ultrasonic diagnostic apparatus 1 will be described.

  The ultrasonic probe 2 is a one-dimensional ultrasonic probe in which a plurality of ultrasonic transducers 21 are arranged in a line in a predetermined direction (scanning direction), and ultrasonic waves are generated in a direction orthogonal to the scanning direction (swing direction). This is a one-dimensional ultrasonic probe capable of mechanically oscillating the vibrator 21. That is, the ultrasonic transducer 21 moves like a pendulum. The ultrasonic vibrator 21 is mechanically oscillated by a movable mechanism 22. The movable mechanism 22 is operated by a motor 23, and the operation speed changes depending on the rotation speed of the motor 23. The rotational speed of the motor 23 and other controls are performed based on control signals from the control unit 8. Note that the ultrasonic transducer 21 may be reciprocated linearly.

  The transmission / reception unit 3 includes a transmission unit and a reception unit, and supplies transmission pulses at a timing when a predetermined delay is given to each ultrasonic transducer 21 based on control from the control unit 8. Thereby, the ultrasonic transducer | vibrator 21 generate | occur | produces an ultrasonic wave, and scans the two-dimensional cross section (scanning surface) according to the arrangement | sequence. When an ultrasonic wave generated from the ultrasonic vibrator 21 is irradiated on the subject, it is reflected by a tissue such as an organ in the subject and received by the ultrasonic vibrator 21 as a reflected signal (echo signal). The transmission / reception unit 3 receives the reflected signal (echo signal) received by the ultrasonic transducer 21. The ultrasonic transmission frequency can be changed by control from the control unit 8. Then, the transmission / reception unit 3 gives a predetermined delay or the like to the reflected signal (echo signal) and then outputs it to the signal processing unit 4.

  The control unit 8 alternately switches between a high transmission frequency and a low transmission frequency for the transmission frequency of the ultrasonic wave every time scanning of one two-dimensional ultrasonic image (one frame) is completed with respect to the transmission / reception unit 3. To instruct. The high transmission frequency is, for example, 4.5 [MHz], and the low transmission frequency is, for example, 2.5 [MHz].

  The transmission / reception unit 3 alternately switches between a high transmission frequency and a low transmission frequency every time scanning of one two-dimensional ultrasonic image (one frame) is completed under the control of the control unit 8. An ultrasonic wave is transmitted to the probe 2. In the first embodiment, under the control of the control unit 8, an ultrasonic wave is transmitted while the ultrasonic transducer 21 is swung to scan a predetermined three-dimensional region. That is, the transmission / reception unit 3 scans a three-dimensional region by transmitting ultrasonic waves to the ultrasonic probe 2 while alternately switching between a high transmission frequency and a low transmission frequency for each two-dimensional ultrasonic image (one frame). To do.

  A specific configuration of the transmission unit will be described. The transmission unit includes a clock generation circuit, a transmission delay circuit, and a pulsar circuit (not shown). The clock generation circuit is a circuit that generates a clock signal that determines the transmission timing and transmission frequency of the ultrasonic signal. The transmission delay circuit is a circuit that performs transmission focus with a delay when transmitting ultrasonic waves. The pulsar circuit incorporates pulsars corresponding to the number of individual paths (channels) corresponding to each ultrasonic transducer, generates a drive pulse at a delayed transmission timing, and each ultrasonic transducer of the ultrasonic probe 2 21 is supplied.

  The reception unit in the transmission / reception unit 3 includes a preamplifier circuit, an A / D conversion circuit, and a reception delay / addition circuit (not shown). The preamplifier circuit amplifies the echo signal output from each ultrasonic transducer of the ultrasonic probe 2 for each reception channel. The A / D converter circuit A / D converts the amplified echo signal. The reception delay / adder circuit gives a delay time necessary for determining the reception directivity to the echo signal after A / D conversion, and adds the delay time. By the addition, the reflection component from the direction according to the reception directivity is emphasized.

  The signal processing unit 4 generates two-dimensional ultrasonic image data (two-dimensional B-mode image data) corresponding to the scanning plane by performing a known B-mode process on the signal output from the transmission / reception unit 3, The two-dimensional ultrasonic image data is stored in the image storage unit 5. This two-dimensional ultrasonic image data includes information indicating the position of the image in the space. When the ultrasonic transducer 21 performs a pendulum motion (oscillation), an angle value from a state in which the ultrasonic transducer 21 is at the center position of the motion is included. Further, when the ultrasonic transducer 21 performs a linear reciprocating motion, the distance value from the state where the ultrasonic transducer 21 is at the center position of the motion is included. The ultrasonic probe 2, the transmission / reception unit 3, and the signal processing unit 4 correspond to the “acquisition unit” of the present invention.

  The image storage unit 5 stores the two-dimensional ultrasonic image data output from the signal processing unit 4. The configuration of the ultrasound image data stored in the image storage unit 5 will be described with reference to FIG. FIG. 2 is a conceptual diagram showing a configuration of ultrasonic image data stored in the image storage unit.

  As illustrated in FIG. 2, the image storage unit 5 includes, for example, two series of two-dimensional ultrasound images, a first series of two-dimensional ultrasound image data group 100 and a second series of two-dimensional ultrasound image data group 200. A sound image data group is stored. Each series of two-dimensional ultrasonic image data groups includes a plurality of two-dimensional ultrasonic image data. A plurality of two-dimensional ultrasound image data included in the two-dimensional ultrasound image data group of each series constitutes separate volume data.

  The first series of two-dimensional ultrasound image data group 100 is composed of a plurality of two-dimensional ultrasound image data acquired with ultrasound having a relatively high transmission frequency. The second series of two-dimensional ultrasound image data 200 is composed of a plurality of two-dimensional ultrasound image data acquired with ultrasound having a relatively low transmission frequency.

  The first series of two-dimensional ultrasonic image data group 100 includes two-dimensional ultrasonic image data 101, two-dimensional ultrasonic image data 102,..., Two-dimensional ultrasonic image data 10N. One volume data is constituted by the dimensional ultrasonic image data. The second series of two-dimensional ultrasonic image data group 200 includes two-dimensional ultrasonic image data 201, two-dimensional ultrasonic image data 202,..., Two-dimensional ultrasonic image data 20N. One volume data is composed of the two-dimensional ultrasonic image data.

  Here, the volume data composed of the first series of two-dimensional ultrasound image data group 100 is referred to as “first volume data”, and the volume data composed of the second series of two-dimensional ultrasound image data group 200. Will be referred to as “second volume data”.

  The image storage unit 5 outputs the two-dimensional ultrasound image data designated by the control unit 8 to the image generation unit 6 under the control of the control unit 8.

  When the image storage unit 5 stores the two-dimensional ultrasound image data 10N and the two-dimensional ultrasound image data 20N, it overwrites the areas of the first two-dimensional ultrasound image data 101 and the two-dimensional ultrasound image data 201. And use it.

  The image generation unit 6 includes a composition unit 61 and a projection unit 62. Upon receiving the two series of two-dimensional ultrasonic image data groups (volume data) output from the image storage unit 5, the combining unit 61 combines the two volume data. The projection unit 62 generates three-dimensional image data based on the combined volume data. For example, the projection unit 62 generates three-dimensional image data by performing volume rendering processing on the combined volume data. Then, the image generation unit 6 outputs the generated three-dimensional image data to the display unit 71.

  Here, conditions for image generation by the projection unit 62 will be described. The control unit 8 gives conditions (image generation conditions) for image generation to the image generation unit 6. The image generation conditions include opacity (opacity) and color used for volume rendering. In the first embodiment, three-dimensional image data is generated using different image forming conditions for the two-dimensional ultrasonic image data groups (volume data) of each series. As for the opacity, an empirically appropriate value is stored in advance in a storage unit (not shown), and the projection unit 62 generates three-dimensional image data using the opacity. For example, as the first image formation condition (opacity) for the first series of volume data, an image formation condition (opacity) suitable for displaying a tissue such as cancer tissue is used, and for the second series of volume data. As the second image forming condition (opacity), an image forming condition (opacity) suitable for displaying the puncture needle is used. Also for the color condition, different conditions are used for each volume data.

  The projection unit 62 generates three-dimensional image data by performing volume rendering on the combined volume data according to the first image forming condition and the second image forming condition. At this time, the projection unit 62 uses the first image forming condition for the first volume data among the data constituting the combined volume data, and the second volume data for the second volume data. Three-dimensional image data is generated using the image forming conditions of 2.

  Here, an example of the opacity used for each volume data will be described with reference to FIG. FIG. 3 is a graph showing an example of the opacity set for the luminance value (voxel value) of the volume data. FIG. 3A shows a luminance value histogram 310 of the first volume data, and FIG. 3B shows a luminance value histogram 320 of the second volume data.

  As shown in FIG. 3A, in the first volume data, the difference between the luminance value range 311 of the cancer tissue and the luminance value range 313 of the electrode needle is small. That is, in the first volume data obtained by the ultrasonic wave having a relatively high transmission frequency, the difference between the luminance value of the cancer tissue and the luminance value of the electrode needle becomes small, Is difficult to distinguish on a three-dimensional image.

  On the other hand, as shown in FIG. 3B, in the second volume data, the difference between the luminance value range 321 of the cancer tissue and the luminance value range 322 of the electrode needle becomes large. In other words, in the second volume data obtained with ultrasonic waves having a relatively low transmission frequency, the luminance value of the electrode needle is relatively higher than the luminance value of the cancer tissue, The difference from the brightness value of the cancer tissue becomes relatively large.

  As described above, by transmitting ultrasonic waves at different transmission frequencies, the difference between the luminance value of the cancer tissue and the luminance value of the electrode needle in the volume data becomes larger than when transmitting ultrasonic waves at the same transmission frequency. . Thus, since the difference between the luminance value of the cancer tissue and the luminance value of the electrode needle becomes relatively large, the cancer tissue and the electrode needle can be distinguished on the three-dimensional image.

  In addition, as shown in FIG. 3 (a), a first opacity curve (suitable for displaying cancer tissue) (first volume data acquired with ultrasonic waves having a relatively high transmission frequency) is used. Opacity distribution with respect to luminance value) is used. That is, the first opacity curve 312 in which the opacity is increased is used in accordance with the luminance value range 311 of the cancer tissue. In addition, as shown in FIG. 3B, for the second volume data acquired with ultrasonic waves having a relatively low transmission frequency, a second opacity curve (brightness) suitable for displaying electrode needles is used. Distribution of opacity to value). That is, the second opacity curve 323 in which the opacity is increased is used in accordance with the range 322 of the luminance value of the electrode needle. The second opacity curve 323 is defined on the relatively higher luminance value side than the first opacity curve 312. The first opacity curve 312 corresponds to the “first opacity function” of the present invention, and the second opacity curve 323 corresponds to the “second opacity function” of the present invention.

  As described above, since the volume data is acquired by transmitting ultrasonic waves having different transmission frequencies, the difference between the luminance value of the cancer tissue and the luminance value of the electrode needle in the volume data is expanded. Makes it easy to distinguish between cancer tissue and electrode needles. Specifically, since the luminance value of the electrode needle becomes relatively high by scanning with ultrasonic waves of a relatively low transmission frequency, the cancer tissue and the electrode needle are distinguished on a three-dimensional image. Will be ready. This facilitates grasping the spatial positional relationship between the puncture needle and the cancer tissue.

  Here, a three-dimensional image obtained by the ultrasonic diagnostic apparatus 1 according to the first embodiment will be described with reference to FIG. FIG. 4 is a diagram showing a three-dimensional image of the puncture needle and the tissue. As shown in FIG. 4, since the brightness values of the outer needle 410 and the electrode needle 411 are higher than those of the cancer tissue 400, the cancer tissue 400 and the puncture needle (the outer needle 410 and the electrode needle) are displayed on the three-dimensional image. 411) can be distinguished. This facilitates grasping the spatial positional relationship between the cancer tissue and the puncture needle. In addition, since the luminance value of the electrode needle 411 is relatively high, the position of the tip portion of the electrode needle 411 is easily grasped.

  Furthermore, an opacity curve that makes the cancer tissue opaque is applied to the first volume data, and an opacity curve that makes the electrode needle opaque is applied to the second volume data. It becomes easy to distinguish the cancer tissue from the puncture needle.

  In addition, by appropriately changing the opacity, the cancer tissue can be displayed semi-transparently and the puncture needle can be displayed substantially opaque. By changing the opacity as appropriate and displaying the cancer tissue translucently, it is possible to observe how the electrode needle advances into the cancer tissue. This will be described with reference to FIG. FIG. 5 is a diagram showing a three-dimensional image of the puncture needle and the tissue, and shows how the electrode needle is inserted.

  As time passes, the three-dimensional image 420, the three-dimensional image 430, and the three-dimensional image 440 are acquired and displayed on the display unit 71. First, the electrode needle 423 starts to come out from the outer needle 422, and the inside of the cancer tissue 421 A three-dimensional image 420 in a state of starting to enter is obtained. The image of the cancer tissue 421 is displayed translucently. Then, when time elapses, a three-dimensional image 430 in which the electrode needle 433 has further entered the cancer tissue 421 is obtained. When the time further elapses, a three-dimensional image 440 in which the electrode needle 443 further enters the cancer tissue 421 is obtained. In this way, by appropriately changing the opacity with respect to the first volume data, the cancer tissue can be displayed semi-transparently, and the state where the electrode needle enters the cancer tissue is observed. Can do.

  The image generation unit 6 generates three-dimensional image data, MPR image data in an arbitrary cross section, and the like by performing image processing such as surface rendering and MPR processing (Multi Planar Reconstruction) on the volume data. Also good.

  Further, the image generating unit 6 may color the tip of the electrode needle in the image data and display it on the display unit 71. Thereby, the position of the front-end | tip part of an electrode needle can be grasped | ascertained easily on a screen.

  Note that the function of the image generation unit 6 may be realized by hardware or software. When realized by software, the image generating unit 6 is configured by a CPU, and the functions of the combining unit 61 and the projecting unit 62 are executed by executing a medical image processing program stored in a storage unit (not shown). Further, the control unit 8 may be configured by a CPU, and a control function for the transmission / reception unit 3 may be executed by executing a control program of an ultrasonic diagnostic apparatus stored in a storage unit (not shown).

  The user interface (UI) 7 includes a display unit 71 and an input unit 72. The display unit 71 includes a monitor such as a CRT or a liquid crystal display, and a tomographic image, a three-dimensional image, blood flow information, or the like is displayed on the monitor screen.

  The input unit 72 includes an operation panel on which various buttons are arranged, a pressure-sensitive liquid crystal panel, and the like, and receives input from the operator. Here, an operation panel as an example of the input unit will be described with reference to FIG. FIG. 6 is a top view showing a part of the operation panel. An imaging button 77 on the operation panel 73 is a button for instructing start and stop of ultrasonic imaging. Every time the imaging button 77 is pressed, the imaging is started and stopped alternately. The 4D button 74 is a button for continuously acquiring and displaying 3D image data. Each time the 4D button 74 is pressed, acquisition and display of 3D image data and display are alternately performed. When the 4D button 74 is pressed, the ultrasonic transducer 21 starts to oscillate, and when it ends, the oscillation of the ultrasonic transducer 21 stops. The 3D button 75 is a button for acquiring only one 3D image data and displaying it on the display unit 71. Each time the 3D button 75 is pressed, 3D image data is acquired. After acquisition, the oscillation of the ultrasonic transducer 21 stops. When the imaging is completed, a three-dimensional image is displayed on the display unit 71. The automatic frequency switching button 76 is a button for executing a mode in which a relatively high transmission frequency and a low transmission frequency are alternately repeated. Each time the automatic frequency switching button 76 is pressed, the mode is started and ended alternately.

(Operation)
Next, a series of operations by the supersonic cutting device according to the first embodiment of the present invention will be described with reference to FIG. FIG. 7 is a flowchart showing a series of operations by the ultrasonic diagnostic apparatus according to the first embodiment of the present invention. In the first embodiment, a case where an unfolded puncture needle is used will be described.

(Step S01)
First, a puncture needle is inserted into a subject while performing ultrasonic imaging, and is advanced to the front of cancer tissue. In this process, the process according to this embodiment can be performed. Here, a case where the process is performed after that will be described.

(Step S02)
Next, in a state where the imaging button 77 of the operation panel 73 shown in FIG. 6 is turned on (started), the operator presses the automatic frequency switching button 76 and the 4D button 74 so that both are turned on. .

  Then, while viewing the three-dimensional image continuously displayed on the display unit 71, the electrode needle is developed from the outer needle and the electrode needle is inserted into the cancer tissue. The operation of the ultrasonic diagnostic apparatus 1 during this time is as follows.

(Step S03)
When the 4D button 74 of the operation panel 73 is turned on, the control unit 8 receives a pressing signal of the 4D button 74 and starts scanning with ultrasonic waves. That is, under the control of the control unit 8, the ultrasonic transducer 21 starts a reciprocating swinging motion by driving the motor 23 of the ultrasonic probe 2. Since the automatic frequency switching button 76 is in the ON state, the control unit 8 causes the transmission / reception unit 3 to transmit the ultrasonic wave every time one two-dimensional ultrasonic image (one frame) is scanned. The transmission frequency is instructed to alternately switch between a high transmission frequency and a low transmission frequency. As a result, the transmission / reception unit 3 alternately switches between a high transmission frequency and a low transmission frequency every time scanning of one two-dimensional ultrasonic image (one frame) is completed, and transmits ultrasonic waves to the ultrasonic probe 2. Send it.

(Step S04)
Then, the transmission / reception unit 3 outputs the received signal to the signal processing unit 4. The signal processing unit 4 generates two-dimensional ultrasound image data (B-mode image data) by performing B-mode processing on the signal output from the transmission / reception unit 3. Then, the signal processing unit 4 stores the two-dimensional ultrasonic image data in the image storage unit 5.

  By scanning a predetermined three-dimensional space while oscillating the ultrasonic transducer 21, the image storage unit 5 stores the first acquired with ultrasonic waves having a relatively high transmission frequency as shown in FIG. A series of two-dimensional ultrasound image data group 100 (first volume data) and a second series of two-dimensional ultrasound image data group 200 (second volume data) acquired with ultrasound having a relatively low transmission frequency. ) Is stored.

  Here, the order of acquiring the two-dimensional ultrasonic image data will be described with reference to FIG. FIG. 8 is a diagram for explaining the volume data and the two-dimensional ultrasonic image data constituting the volume data.

  As shown in FIG. 8, the ultrasonic diagnostic apparatus 1 according to the first embodiment repeats a high transmission frequency and a low transmission frequency alternately for each frame while swinging the ultrasonic transducer 21. An ultrasonic wave is transmitted to scan a predetermined three-dimensional area. Specifically, the ultrasound diagnostic apparatus 1 acquires the two-dimensional ultrasound image data 101 with high transmission frequency ultrasound, and then acquires the two-dimensional image data 201 with low transmission frequency ultrasound. In addition, the two-dimensional image data 201 is acquired with an ultrasonic wave having a high transmission frequency, and thereafter, a three-dimensional region is scanned while alternately repeating a high transmission frequency and a low transmission frequency.

  Then, the first volume data is constituted by the two-dimensional ultrasonic image data group obtained at a relatively high transmission frequency, and the second volume data is obtained by the two-dimensional ultrasonic image data group obtained at a relatively low transmission frequency. Configure volume data. For example, when M pieces of two-dimensional ultrasound image data are necessary to form one volume data, the (M + 1) -th piece of two-dimensional ultrasound image data is the first data of the second volume data. Become.

(Step S05)
When the acquisition of the first series of two-dimensional ultrasound image data group 100 (first volume data) and the second series of two-dimensional ultrasound image data group 200 (second volume data) is completed, the controller 8 Instructs the image storage unit 5 to output the volume data to the image generation unit 6. Further, the control unit 8 gives image generation conditions to the image generation unit 6.

(Step S06)
When the composition unit 61 of the image generation unit 6 receives the first volume data and the second volume data from the image storage unit 5, the composition unit 61 synthesizes the first volume data and the second volume data. Then, the projection unit 62 generates three-dimensional image data by performing volume rendering on the combined volume data in accordance with the image generation conditions received from the control unit 8 (projection unit 62). Then, the image generation unit 6 outputs the three-dimensional image data to the display unit 71.

  For the first volume data and the second volume data, three-dimensional image data is generated using different image generation conditions. For example, as shown in FIG. 3A, for the first volume data, an opacity curve 312 having higher opacity is used in accordance with the luminance value range 311 of the cancer tissue. Further, as shown in FIG. 3B, an opacity curve 323 in which the opacity is increased is used for the second volume data in accordance with the brightness value range 322 of the electrode needle.

(Step S07)
When the display unit 71 receives the 3D image data from the image generation unit 6, the display unit 71 displays a 3D image based on the 3D image data.

  As described above, since the luminance value of the electrode needle becomes relatively high by scanning with an ultrasonic wave having a relatively low transmission frequency, it is possible to distinguish the cancer tissue from the electrode needle on the three-dimensional image. This makes it easier to grasp the spatial positional relationship between the electrode needle and the cancer tissue. In addition, by performing volume rendering according to different opacity curves with the first volume data and the second volume data obtained by ultrasonic waves having different transmission frequencies, the cancer tissue and the electrode needle are displayed on the three-dimensional image. And the spatial positional relationship between the electrode needle and the cancer tissue can be easily grasped.

  Note that imaging is repeatedly performed during the above processing, and the two-dimensional ultrasonic image data is continuously stored in the image storage unit 5. When the second volume data is obtained, the three-dimensional image is displayed on the display unit 71 by executing the processing from step S05 to step S07. Thereafter, the processing from step S03 to step S07 is repeatedly executed.

  When the operator observes the three-dimensional image displayed on the display unit 71 and determines that the electrode needle has reached the intended position, the operator presses the 3D button 75 on the operation panel 73 of the input unit 72. To do. When the control unit 8 receives the pressing signal of the 3D button 75, the imaging is performed by changing the transmission frequency of the ultrasonic wave for each frame, and when one set of volume data is acquired, the imaging is automatically stopped. In this case, the movable mechanism 22 causes the ultrasonic transducer 21 to swing relatively slowly under the control of the control unit 8 to acquire a larger number of two-dimensional ultrasonic image data. Thereby, volume data with high spatial resolution can be obtained. When imaging is stopped, the image generation unit 6 generates three-dimensional image data based on the volume data. The display unit 71 displays a three-dimensional image based on the three-dimensional image data. The surgeon observes the three-dimensional image and confirms the spatial positional relationship between the cancer tissue and the puncture needle. In radiofrequency ablation therapy, since the positional relationship between the tip of the electrode needle and the cancer tissue is particularly important, the positional relationship is confirmed with a three-dimensional image with high spatial resolution. After confirming the position, start ablation treatment.

(Modification 1)
Next, Modification 1 of the ultrasonic diagnostic apparatus 1 according to the first embodiment will be described with reference to FIG. FIG. 9 is a diagram for explaining volume data acquired by the ultrasonic diagnostic apparatus according to the first modification and two-dimensional ultrasonic image data constituting the volume data.

  In the first embodiment, as shown in FIG. 8, scanning is performed by switching the ultrasonic transmission frequency for each frame, but the transmission frequency may be switched every time one volume data is acquired. . That is, the transmission / reception unit 3 controls the ultrasonic probe 2 to transmit ultrasonic waves at a relatively high transmission frequency in order to capture a plurality of two-dimensional ultrasonic image data constituting one volume data under the control of the control unit 8. Send it. Further, the transmission / reception unit 3 transmits ultrasonic waves at a relatively low transmission frequency in order to capture a plurality of two-dimensional ultrasonic image data composing another volume data under the control of the control unit 8. 2 to send.

  For example, as shown in FIG. 9, first, the transmission / reception unit 3 scans a predetermined three-dimensional region by transmitting an ultrasonic wave having a relatively high transmission frequency to the ultrasonic probe 2 under the control of the control unit 8. A two-dimensional ultrasonic image data group 100 including two-dimensional ultrasonic image data 101, two-dimensional ultrasonic image data 102,..., Two-dimensional ultrasonic image data 10M is acquired. Next, the transmission / reception unit 3 transmits ultrasonic waves having a relatively low transmission frequency to the ultrasonic probe 2 under the control of the control unit 8, scans a predetermined three-dimensional space, and performs two-dimensional ultrasonic image data 201. A two-dimensional ultrasonic image data group 200 composed of the two-dimensional ultrasonic image data 202,..., The two-dimensional ultrasonic image data 20M is acquired.

  Then, the image generation unit 6 synthesizes the two-dimensional ultrasound image data group 100 (first volume data) and the two-dimensional ultrasound image data group 200 (second volume data), and the synthesized volume data. 3D image data is generated by performing volume rendering on the image. At this time, as in the first embodiment, the image generation unit 6 generates three-dimensional image data using different image forming conditions (opacity and color) for the first volume data and the second volume data. Generate.

  As described above, the same effect as that of the first embodiment can be obtained even when scanning is performed by switching the transmission frequency of the ultrasonic wave every time one volume data is acquired. In addition, since 10 to 20 volume data can be acquired per second, even if the transmission frequency is changed for each volume data, the real time property is not greatly affected.

  In the first modification, one volume data is acquired by transmitting an ultrasonic wave having a relatively high transmission frequency, and then another volume data is acquired by transmitting an ultrasonic wave having a relatively low transmission frequency. However, one volume data may be acquired by transmitting an ultrasonic wave having a low transmission frequency, and then another volume data may be acquired by transmitting an ultrasonic wave having a high transmission frequency.

(Modification 2)
Next, Modification 2 of the ultrasonic diagnostic apparatus 1 according to the first embodiment will be described. In the first embodiment, the one-dimensional ultrasonic probe in which the ultrasonic transducer 21 is mechanically oscillated is used. However, in the second modification, a two-dimensional ultrasonic probe is used. In this two-dimensional ultrasonic probe, a plurality of ultrasonic transducers are arranged in a matrix (lattice), and the ultrasonic waves are transmitted and received three-dimensionally by scanning, and three-dimensional data having a shape spreading radially from the probe surface is obtained. Received as an echo signal.

  In this way, by using a two-dimensional ultrasonic probe, scanning is performed by changing the ultrasonic transmission frequency for each volume data. That is, the transmission / reception unit 3 transmits ultrasonic waves to the ultrasonic probe 2 at a relatively high transmission frequency in order to acquire one volume data under the control of the control unit 8. Furthermore, the transmission / reception unit 3 transmits ultrasonic waves to the ultrasonic probe 2 at a relatively low transmission frequency in order to acquire another piece of volume data under the control of the control unit 8.

  Then, the image generation unit 6 synthesizes the first volume data acquired with ultrasonic waves with a relatively high transmission frequency and the second volume data acquired with ultrasonic waves with a relatively low transmission frequency. Then, three-dimensional image data is generated by performing volume rendering on the combined volume data. At this time, as in the first embodiment, the image generation unit 6 generates three-dimensional image data using different image generation conditions (opacity and color) for the first volume data and the second volume data. Generate.

  As described above, even when a two-dimensional ultrasonic probe is used as the ultrasonic probe 2 and scanning is performed while switching the transmission frequency of the ultrasonic wave for each volume, the same effect as that of the first embodiment can be obtained.

(Modification 3)
Next, Modification 3 of the ultrasonic diagnostic apparatus 1 according to the first embodiment will be described. The ultrasonic diagnostic apparatus 1 according to the first embodiment combines the first volume data and the second volume data, and performs volume rendering according to a predetermined opacity curve on the combined volume data. As a result, three-dimensional image data was generated. On the other hand, in the third modification, a tomographic image or the like is used as an image suitable for tissue observation. For example, the ultrasonic diagnostic apparatus according to Modification 3 generates MPR image data of an arbitrary cross section by performing MPR processing on the first volume data. Thereby, an MPR image is obtained as an image suitable for tissue observation. On the other hand, for the second volume data, three-dimensional image data is generated by performing volume rendering according to an opacity curve suitable for the luminance range of the electrode needle, as in the first embodiment.

  Therefore, in Modification 3, an image suitable for tissue observation is displayed as a tomographic image, and an image suitable for electrode needle observation is displayed as a three-dimensional image. Even in this case, since the second volume data is acquired by ultrasonic waves having a relatively low transmission frequency, the luminance value of the electrode needle is relatively high, and the electrode needle is easily seen in the three-dimensional image. There is an effect.

[Second Embodiment]
A configuration of an ultrasonic diagnostic apparatus according to the second embodiment of the present invention will be described with reference to FIGS. 10 and 11. FIG. 10 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus according to the second embodiment of the present invention. FIG. 11 is a block diagram illustrating a configuration of an image processing unit installed in the ultrasonic diagnostic apparatus according to the second embodiment.

  The ultrasonic diagnostic apparatus 1A according to the second embodiment acquires first volume data by transmitting ultrasonic waves in a first direction, and deflects ultrasonic waves in a plurality of directions including the first direction. By doing so, volume data is acquired for each direction. Then, data corresponding to the electrode needle is extracted from the volume data acquired in each direction and added. The first volume data and the added data are combined and three-dimensional image data is generated based on the combined volume data. By deflecting the ultrasonic waves, it is possible to irradiate the ultrasonic waves from a substantially vertical direction, particularly with respect to the electrode needles constituting the deployable puncture needle. Thereby, since the luminance value of the electrode needle is increased, an image in which the electrode needle is easy to see is obtained. In addition, since the 3D image based on the first volume data includes a tissue image, the spatial positional relationship between the tissue and the puncture needle can be easily grasped according to the 3D image based on the combined volume data. It becomes possible to do. The configuration of the ultrasonic diagnostic apparatus 1A according to the second embodiment will be described below.

  The ultrasonic diagnostic apparatus 1A according to the second embodiment is characterized by a transmission / reception unit 3A and an image processing unit 9. A two-dimensional ultrasonic probe is used as the ultrasonic probe 2A. Since the configuration other than the transmission / reception unit 3A and the image processing unit 9 is the same as that of the ultrasonic diagnostic apparatus 1 according to the first embodiment, here, the configuration and functions of the transmission / reception unit 3A and the image processing unit 9 are mainly described. explain.

  The transmission / reception unit 3A includes a deflection control unit 31 and a parameter storage unit 32. The parameter storage unit 32 stores in advance a deflection parameter (deflection angle) corresponding to the traveling direction of the ultrasonic beam. The parameter storage unit 32 stores a plurality of deflection parameters (deflection angles). Here, it is assumed that three deflection parameters (deflection angles) are stored in the parameter storage unit 32. Of the plurality of deflection parameters (deflection angle), one deflection parameter is a parameter indicating an angle (reference angle) at which the ultrasonic beam is not deflected. For example, an angle indicating a direction immediately below the ultrasonic probe 2 is set to an angle without any deflection (reference angle).

  The deflection control unit 31 takes out the deflection parameters stored in the parameter storage unit 32 and deflects the ultrasonic beam according to the deflection parameters.

  By the way, as shown in FIG. 15, the deployable puncture needle 600 includes a plurality of electrode needles 602, and each electrode needle 602 is curved in a different direction. For this reason, when the ultrasonic beam is deflected in a specific direction, the reflection intensity of the ultrasonic wave is increased in a portion where the electrode needle 602 is provided, but the reflection intensity is decreased in the other portion. In the portion where the reflection intensity is high, the electrode needle is easy to see in the three-dimensional image, but in the portion where the reflection intensity is low, the electrode needle is difficult to see.

  On the other hand, since the ultrasonic diagnostic apparatus 1A according to the second embodiment scans a predetermined three-dimensional region by deflecting the ultrasonic beam in a plurality of directions different from each other, it is curved in different directions. It is possible to irradiate the electrode needle 602 with an ultrasonic beam from a substantially vertical direction. Thereby, in the three-dimensional image, the entire plurality of electrode needles 602 can be more easily seen.

  Here, the deflection direction of the ultrasonic beam will be described with reference to FIG. FIG. 12 is a schematic diagram for explaining the deflection direction of the ultrasonic beam. For example, the deflection control unit 31 deflects the ultrasonic beam to the three-dimensional region 500, the region 501, and the region 502. A region 500 is a three-dimensional region corresponding to an angle (reference angle) at which the ultrasonic beam is not deflected. The region 500 is, for example, a region immediately below the ultrasonic probe 2A, and is a three-dimensional region that is scanned when the ultrasonic beam is not deflected. In the parameter storage unit 32, deflection parameters (deflection angles) indicating the directions of the region 500, the region 501, and the region 502 are stored in advance. Then, the deflection control unit 31 deflects the ultrasonic beam to the region 500, the region 501, and the region 502 according to the deflection parameter (deflection angle) stored in the parameter storage unit 32. Here, the deflection parameter indicating the direction of the region 500 is a first deflection parameter (first deflection angle), and the deflection parameter indicating the direction of the region 501 is a second deflection parameter (second deflection angle). The deflection parameter indicating the direction of the region 502 is a third deflection parameter (third deflection angle).

  When the image processing unit 9 receives volume data acquired by deflecting ultrasonic waves in each deflection direction from the signal processing unit 4, the image processing unit 9 extracts data corresponding to the puncture needle from each volume data and adds the extracted data. To do. Then, the image processing unit 9 outputs the added volume data to the image storage unit 5. Here, the configuration of the image processing unit 9 will be described with reference to FIG. The image processing unit 9 includes a threshold processing unit 91, a processing result storage unit 92, and an addition unit 93.

  The threshold processing unit 91 performs threshold processing on the volume data input from the signal processing unit 4. For example, the threshold value processing unit 91 replaces a luminance value (voxel value) that is equal to or lower than a preset threshold value in the volume data with a preset minimum value. The threshold value is set to a value smaller than the luminance value corresponding to the reflection of the ultrasonic wave from the electrode needle. The minimum value is a value sufficiently smaller than the luminance value corresponding to the reflection of the ultrasonic wave from the electrode needle. This minimum value corresponds to the “relatively low value” of the present invention.

  As a result of this threshold value processing, the luminance value below the threshold value is replaced with the minimum value, so that a portion corresponding to the electrode needle is left in the second volume data after the threshold value processing. As a result, data corresponding to the electrode needle is extracted from the second volume data.

  The threshold processing unit 91 performs threshold processing on the volume data acquired at each deflection angle. In the example illustrated in FIG. 12, the threshold processing unit 91 performs threshold processing on the volume data in the area 500, the volume data in the area 501, and the volume data in the area 502. Then, the threshold processing unit 91 outputs each volume data after the threshold processing to the processing result storage unit 92. As a result, the volume data in which the luminance value other than the portion corresponding to the electrode needle is replaced with the minimum value is stored in the processing result storage unit 92. In the example shown in FIG. 12, since the volume data of the area 500, the area 501, and the area 502 is acquired, the processing result storage unit 92 stores the volume data after the threshold processing for each area.

  The adding unit 93 adds a plurality of volume data after threshold processing stored in the processing result storage unit 92. The adding unit 93 adds, for example, volume data included in a region that overlaps spatially with a region where the ultrasonic beam is not deflected. Further, the adding unit 93 may add volume data included in spatially overlapping areas among a plurality of volume data.

  A specific example of the area to be added will be described with reference to FIG. For example, the adding unit 93 adds data included in an area overlapping the area 500 to be scanned without deflecting the ultrasonic beam among the volume data after the threshold processing. That is, the adder 93 adds data included in an area that overlaps spatially with the first volume data. In the example illustrated in FIG. 12, the adding unit 93 overlaps the area 500 volume data, the volume data included in the area 501 of the volume data of the area 501, and the area 500 of the volume data of the area 502. The volume data contained in the area to be added is added.

  Further, the adding unit 93 may add data included in a region 503 in which the region 500, the region 501, and the region 502 overlap spatially. That is, the adding unit 93 includes the volume data included in the area 503 that overlaps with other areas in the volume data of the area 500 and the volume included in the area 503 that overlaps with other areas among the volume data of the area 501. The data and the volume data included in the area 503 that overlaps with other areas of the volume data in the area 502 may be added.

  In the example illustrated in FIG. 12, the adding unit 93 adds the volume data included in the area where the three areas overlap, but may add volume data included in the area where at least two areas overlap. For example, the adding unit 93 adds the volume data included in the overlapping areas for the areas 500 and 501, and adds the volume data included in the overlapping areas for the areas 500 and 502. Good.

  Further, the image processing unit 9 may not perform threshold processing in accordance with an instruction from the control unit 8. In this case, when receiving the volume data from the signal processing unit 4, the image processing unit 9 outputs the volume data to the image storage unit 5 as it is. For example, the image processing unit 9 outputs the first volume data to the image storage unit 5 without performing threshold processing on the first volume data.

(Operation)
Next, a series of operations by the ultrasonic diagnostic apparatus 1A according to the second embodiment of the present invention will be described with reference to FIG. FIG. 13 is a flowchart showing a series of operations by the ultrasonic diagnostic apparatus according to the second embodiment of the present invention.

(Step S20)
First, under the control of the control unit 8, the transmission / reception unit 3A transmits an ultrasonic wave having a predetermined transmission frequency to the ultrasonic probe 2A, and scans the region 500 where the ultrasonic wave is not deflected. By this scanning, volume data of the area 500 is acquired. Under the control of the control unit 8, the image processing unit 9 outputs the volume data to the image storage unit 5 without performing threshold processing. Volume data obtained by scanning the area 500 will be referred to as “first volume data”.

(Step S21)
Next, the deflection control unit 31 of the transmission / reception unit 3A takes out the first deflection parameter (first deflection angle) from the parameter storage unit 32, deflects the ultrasonic wave according to the first deflection parameter, and scans the region 500. To do. By this scan, volume data of the area 500 is acquired and output to the image processing unit 9.

  Further, the deflection control unit 31 takes out the second deflection parameter (second deflection angle) from the parameter storage unit 32, deflects the ultrasonic wave according to the second deflection parameter, and scans the region 501. By this scanning, volume data of the area 501 is acquired and output to the image processing unit 9.

  Further, the deflection control unit 31 takes out the third deflection parameter (third deflection angle) from the parameter storage unit 32, deflects the ultrasonic wave in accordance with the third deflection parameter, and scans the region 502. By this scanning, volume data of the area 502 is acquired and output to the image processing unit 9.

(Step S22)
When the threshold value processing unit 91 of the image processing unit 9 receives the volume data of each area acquired in step S21, the threshold value processing unit 91 performs threshold processing on each volume data. Thereby, the volume data in which the luminance value below the threshold value (luminance value other than the portion corresponding to the electrode needle) is replaced with the minimum value among the volume data is obtained. The volume data after the threshold processing is stored in the processing result storage unit 92. In this embodiment, the threshold processing unit 91 performs threshold processing on the volume data of the region 500, the region 501, and the region 502, and outputs the volume data after the threshold processing to the processing result storage unit 92. As a result, three volume data are stored in the processing result storage unit 92.

(Step S23)
The addition unit 93 of the image processing unit 9 reads and adds a plurality of volume data after threshold processing stored in the processing result storage unit 92 according to an instruction from the control unit 8. For example, the adding unit 93 adds the volume data included in the area overlapping the area 500 to be scanned without deflecting the ultrasonic beam. Further, the adding unit 93 may add the volume data included in the area 503 that overlaps the area 500, the area 501, and the area 502 among the volume data after the threshold processing. The image processing unit 9 outputs the added volume data to the image storage unit 5.

(Step S24)
The synthesizing unit 61 of the image generating unit 6 receives and synthesizes the first volume data from the image storage unit 5 and the volume data added by the image processing unit 9, and synthesizes the synthesized volume data. Output to.

(Step S25)
The projection unit 62 generates three-dimensional image data by performing volume rendering on the combined volume data in accordance with predetermined image generation conditions (opacity and color). Then, the projection unit 62 outputs the three-dimensional image data to the display unit 71.

(Step S26)
When receiving the three-dimensional image data from the image generation unit 6, the display unit 71 displays a three-dimensional image based on the three-dimensional image data.

  As described above, by deflecting ultrasonic waves in a plurality of directions, it is possible to irradiate a plurality of electrode needles from a substantially vertical direction, so that the luminance value of the electrode needles is increased in a three-dimensional image. be able to. Thereby, a three-dimensional image in which the electrode needle can be easily seen is obtained. Further, by performing threshold processing on the volume data, the volume data corresponding to the electrode needles can be extracted from the volume data. Then, according to the three-dimensional image based on the volume data obtained by synthesizing the volume data after the threshold processing and the first volume data, it is possible to easily grasp the spatial positional relationship between the tissue and the puncture needle. .

(Modification 4)
Next, Modification 4 of the ultrasonic diagnostic apparatus 1A according to the second embodiment will be described. In the second embodiment, the ultrasonic transmission frequency is not switched. In the fourth modification, the ultrasonic transmission frequency is switched as in the first embodiment. That is, the transmission / reception unit 3A switches the transmission frequency of the ultrasonic wave for each volume and transmits the ultrasonic wave to the ultrasonic probe 2A, similarly to the transmission / reception unit 3 according to the first embodiment. Hereinafter, a series of operations by the ultrasonic diagnostic apparatus according to Modification 4 will be described with reference to FIG.

(Step S30)
First, under the control of the control unit 8, the transmission / reception unit 3 </ b> A transmits an ultrasonic wave having a relatively high transmission frequency to the ultrasonic probe 2 </ b> A and scans a region 500 where the ultrasonic wave is not deflected. By this scanning, volume data of the area 500 is acquired. Under the control of the control unit 8, the image processing unit 9 outputs the volume data to the image storage unit 5 without performing threshold processing. Volume data obtained by scanning the area 500 will be referred to as “first volume data”.

(Step S31)
Next, the transmitter / receiver 3 </ b> A causes the ultrasonic probe 2 </ b> A to transmit an ultrasonic wave having a relatively low transmission frequency under the control of the controller 8. Further, the deflection control unit 31 of the transmission / reception unit 3A retrieves the first deflection parameter (first deflection angle) from the parameter storage unit 32, deflects the ultrasonic wave according to the first deflection parameter, and scans the region 500. . That is, the transmitting / receiving unit 3A scans the region 500 with ultrasonic waves having a relatively low transmission frequency. By this scanning, volume data of the area 500 is acquired and output to the image processing unit 9.

  Further, the deflection control unit 31 takes out the second deflection parameter (second deflection angle) from the parameter storage unit 32, deflects the ultrasonic wave according to the second deflection parameter, and scans the region 501. That is, the transmission / reception unit 3A scans the region 501 with ultrasonic waves having a relatively low transmission frequency. By this scanning, volume data of the area 501 is acquired and output to the image processing unit 9.

  Further, the deflection control unit 31 takes out the third deflection parameter (third deflection angle) from the parameter storage unit 32, deflects the ultrasonic wave according to the third deflection parameter, and scans the region 502. That is, the transmission / reception unit 3A scans the region 502 with ultrasonic waves having a relatively low transmission frequency. By this scanning, volume data of the area 502 is acquired and output to the image processing unit 9.

(Step S32)
When the threshold value processing unit 91 of the image processing unit 9 receives the volume data of each area acquired in step S31, the threshold value processing unit 91 performs threshold processing on each volume data. The volume data after the threshold processing is stored in the processing result storage unit 92. At this point, the processing result storage unit 92 stores three volume data. These three volume data are data acquired at a relatively low transmission frequency.

(Step S33)
The addition unit 93 of the image processing unit 9 reads and adds a plurality of volume data after threshold processing stored in the processing result storage unit 92 according to an instruction from the control unit 8. For example, the adding unit 93 adds volume data included in an area overlapping with the area 500. Further, the adding unit 93 may add the volume data included in the area 503 overlapping each area. Then, the image processing unit 9 outputs the added volume data to the image storage unit 5.

(Step S34)
The synthesizing unit 61 of the image generating unit 6 receives and synthesizes the first volume data from the image storage unit 5 and the volume data added by the image processing unit 9, and synthesizes the synthesized volume data. Output to.

(Step S35)
The projection unit 62 generates three-dimensional image data by performing volume rendering on the combined volume data. At this time, as in the first embodiment, an opacity curve suitable for displaying a tissue such as a cancer tissue is applied to the first volume data, and the addition processing is performed on the volume data. Applies an opacity curve suitable for displaying electrode needles. For example, the first opacity curve 312 shown in FIG. 3A is used for the first volume data, and FIG. 3B is used for the volume data subjected to the threshold processing and the addition processing. 3D image data is generated using a second opacity curve 323 shown in FIG. Thereby, it becomes easy to distinguish the cancer tissue and the electrode needle on the three-dimensional image, and the spatial positional relationship between the electrode needle and the cancer tissue is easily grasped.

(Step S36)
When receiving the three-dimensional image data from the image generation unit 6, the display unit 71 displays a three-dimensional image based on the three-dimensional image data.

  According to the ultrasonic diagnostic apparatus according to the modified example 4, in addition to the operation and effect of the ultrasonic diagnostic apparatus according to the second embodiment, since the ultrasonic transmission frequency is switched, the luminance value of the electrode needle is relatively And the electrode needles are easier to see in the three-dimensional image. As a result, in the three-dimensional image, it becomes easy to grasp the spatial positional relationship between the cancer tissue and the electrode needle.

  In the second embodiment and the fourth modification, a two-dimensional ultrasonic probe is used as the ultrasonic probe 2A. However, a three-dimensional region may be scanned using a mechanical one-dimensional ultrasonic probe. Good.

1 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus according to a first embodiment of the present invention. It is a conceptual diagram which shows the structure of the ultrasonic image data memorize | stored in an image memory | storage part. It is a graph which shows an example of the opacity set with respect to the luminance value (voxel value) of volume data. It is a figure which shows the three-dimensional image of a puncture needle and a structure | tissue. It is a figure which shows the three-dimensional image of a puncture needle and a structure | tissue, and is a figure which shows a mode that an electrode needle is punctured. It is a top view which shows a part of operation panel. It is a flowchart which shows a series of operation | movement by the ultrasonic diagnosing device which concerns on 1st Embodiment of this invention. It is a figure for demonstrating volume data and the two-dimensional ultrasonic image data which comprise it. It is a figure for demonstrating the volume data acquired by the ultrasonic diagnosing device which concerns on the modification 1, and the two-dimensional ultrasonic image data which comprise it. It is a block diagram which shows schematic structure of the ultrasonic diagnosing device which concerns on 2nd Embodiment of this invention. It is a block diagram which shows the structure of the image process part installed in the ultrasonic diagnosing device which concerns on 2nd Embodiment. It is a schematic diagram for demonstrating the deflection | deviation direction of an ultrasonic beam. It is a flowchart which shows a series of operation | movement by the ultrasonic diagnosing device which concerns on 2nd Embodiment of this invention. 10 is a flowchart showing a series of operations by an ultrasonic diagnostic apparatus according to Modification 4. It is a perspective view which shows a puncture needle.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1, 1A ultrasonic diagnostic apparatus 2, 2A ultrasonic probe 3, 3A transmission / reception part 4 Signal processing part 5 Image storage part 6 Image generation part 7 User interface (UI)
8 Control Unit 9 Image Processing Unit 31 Deflection Control Unit 32 Parameter Storage Unit 61 Composition Unit 62 Projection Unit 91 Threshold Processing Unit 92 Processing Result Storage Unit 93 Addition Unit

Claims (12)

The first volume data is acquired by transmitting an ultrasonic wave to the subject at a first transmission frequency, and the ultrasonic wave is transmitted to the subject at a second transmission frequency that is lower than the first transmission frequency. Obtaining means for obtaining the second volume data,
Combining means for combining the first volume data and the second volume data to generate combined data;
Image generating means for generating three-dimensional image data based on the synthesized data;
An ultrasonic diagnostic apparatus comprising:   The obtaining means obtains the first volume data and the second volume data by switching between the first transmission frequency and the second transmission frequency every time one piece of volume data is obtained. The ultrasonic diagnostic apparatus according to claim 1, wherein the apparatus is an ultrasonic diagnostic apparatus.   The acquisition means switches a predetermined three-dimensional region by transmitting an ultrasonic wave by switching the first transmission frequency and the second transmission frequency for each of the two-dimensional scanning planes for a plurality of different two-dimensional scanning planes. The ultrasonic diagnostic apparatus according to claim 1, wherein the first volume data and the second volume data are acquired by scanning   The acquisition means generates the first volume data based on a first two-dimensional data group obtained for the plurality of two-dimensional scanning planes by transmitting ultrasonic waves at the first transmission frequency, The second volume data is generated based on a second two-dimensional data group obtained for the plurality of two-dimensional scanning planes by transmitting ultrasonic waves at the second transmission frequency. Item 4. The ultrasonic diagnostic apparatus according to Item 3.   The image generation means is a first image generation condition for the first volume data included in the combined data, and the first image for the second volume data included in the combined data. 5. The ultrasonic diagnostic apparatus according to claim 1, wherein the three-dimensional image data is generated from the composite data in accordance with a second image generation condition different from the generation condition. The first image generation condition includes a first opacity function, and the second image generation condition includes a second opacity function different from the first opacity function;
The image generation means generates the three-dimensional image data by performing volume rendering on the composite data according to the first opacity function and the second opacity function. 5. The ultrasonic diagnostic apparatus according to 5.   The first opacity function and the second opacity function are represented by an opacity distribution with respect to voxel values of volume data, and the second opacity function is more than the first opacity function. The ultrasonic diagnostic apparatus according to claim 6, wherein the ultrasonic diagnostic apparatus is defined on a relatively high luminance value side. A threshold processing means and an adding means;
The acquisition means acquires first volume data by transmitting an ultrasonic wave at the first transmission frequency in a first direction, and the second transmission frequency in a plurality of directions including the first direction. To obtain volume data for each direction by transmitting ultrasound
The threshold processing means is data constituting each volume data acquired for each individual direction, and converts data that is equal to or lower than a predetermined threshold into a relatively low voxel value,
The adding means adds the volume data in each direction subjected to the threshold processing,
The synthesis means includes
The ultrasonic diagnostic apparatus according to claim 1, wherein the synthesized data is generated by synthesizing the first volume data and the volume data after the addition.   The ultrasonic diagnostic apparatus according to claim 8, wherein the adding unit adds volume data included in spatially overlapping areas among the volume data in each direction on which the threshold processing has been performed.   The addition means adds volume data included in an area spatially overlapping with the first volume data among volume data in each direction on which the threshold processing has been performed. The ultrasonic diagnostic apparatus as described. By transmitting ultrasonic waves in a first direction, acquiring first volume data in the first direction, and transmitting ultrasonic waves in a plurality of directions including the first direction, for each direction Acquisition means for acquiring volume data;
Threshold processing means for converting each volume data acquired for each individual direction, which is equal to or lower than a predetermined threshold, into a relatively low voxel value;
Adding means for adding volume data in each direction subjected to the threshold processing;
Combining means for generating combined data by combining the first volume data and the volume data after the addition;
Image generating means for generating three-dimensional image data based on the synthesized data;
An ultrasonic diagnostic apparatus comprising: On the computer,
The first volume data is acquired by transmitting an ultrasonic wave to the subject at the first transmission frequency, and the ultrasonic wave is transmitted to the subject at a second transmission frequency that is lower than the first transmission frequency. An acquisition function for acquiring the second volume data by
A combining function for generating combined data by combining the first volume data and the second volume data;
An image generation function for generating three-dimensional image data based on the synthesized data;
A control program for an ultrasonic diagnostic apparatus, characterized in that

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