JP2006150069A - Ultrasonic diagnostic equipment, and control method therefor - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide ultrasonic diagnostic equipment having a function of enhancing visual recognition property in a centesis needle concerning a centesis operation under the guide of ultrasonic waves, for example. <P>SOLUTION: Three ultrasonic transmissions of positive, negative and negative polarities are executed for each of a plurality of ultrasonic scan lines on the basis of a predetermined rate period. Echo signals generated due to the respective ultrasonic transmissions are received at the same rate. For each scanning line, addition of the echo signal based on the first ultrasound of positive polarity to the echo signal based on the second ultrasound of negative polarity produces a normal mode image. Also for each scanning line, addition of the echo signal based on the first ultrasound of positive polarity to the echo signal based on the third ultrasound of negative polarity produces centesis mode image data. The produced images of normal and centesis modes are displayed in a predetermined manner. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to an improvement in reliability and accuracy of a puncture under an ultrasound guide, for example, and more particularly to an ultrasonic diagnostic apparatus used for improving the visibility of a puncture needle and a control method thereof.

  An ultrasonic diagnostic apparatus is a medical imaging device that noninvasively obtains a tomographic image of soft tissue in a living body from a body surface by an ultrasonic pulse reflection method. Compared to other medical imaging equipment, this ultrasonic diagnostic device has features such as small size, low cost, no exposure to X-rays, high safety, blood flow imaging, etc., and the heart, abdomen, urology, Widely used in obstetrics and gynecology.

  In image diagnosis using this ultrasonic diagnostic device, by extracting and visualizing harmonic components (harmonic components that appear at integer multiples of the fundamental frequency) generated by nonlinear waveform propagation of tissues and nonlinear vibration of contrast agents, As is well known, it is possible to generate a very high quality image with high resolution and little artifact (false image noise). A filter method is a typical method for extracting a nonlinear component such as a harmonic component generated by this nonlinear vibration.

  In addition, a method of extracting a harmonic component by removing a fundamental wave component more effectively than the above filter method is known (see, for example, Patent Document 1). In this method, two types of ultrasonic pulses whose phases are reversed with respect to the same ultrasonic scanning line are alternately transmitted, and two types of received signals corresponding thereto are added. This method is called the phase inversion method, which generates a canceling action for the fundamental wave component, thereby enabling the removal of the fundamental wave component that has entered the harmonic band that can never be removed by the filter method. Moreover, it is a very useful technique that exhibits an additive enhancement effect on the harmonic component.

  On the other hand, the above-described phase inversion method works accurately only when the tissue as the propagation medium is stationary or when the propagation path in the tissue is the same. Therefore, if it is applied to an actual living body where the movement of an organ typified by the heart exists, a displacement occurs in each part between the two-rate received signals due to the influence of the movement. Result in motion artifacts.

  Further, when the interval of transmitting ultrasonic pulses, that is, PRF (Pulse Repetition Frequency) becomes longer, the displacement of each part becomes larger and the influence of motion artifacts becomes larger. This motion artifact hides the part to be seen and at the same time significantly deteriorates the image. Therefore, in the phase inversion method, it is common to devise not to generate motion artifacts such as setting the PRF so as not to be longer than necessary.

By the way, radiofrequency ablation (RFA) as a local treatment method for hepatocellular carcinoma and biopsy for examining hepatocyte tissue, puncture under ultrasound guide is widely performed, and it can be applied accurately to a region of interest such as a tumor. It is important to perform a puncture. For this reason, it is necessary to clearly grasp in the ultrasonic image where the needle has penetrated at the time of puncturing.
“Non-linear propagation of ultrasonic pulse” written by Ariru Satoshi and Kamakura Tomio (Science Technique, US89-23, p53).

  However, in the puncture operation under the ultrasonic guide, in many cases, the ultrasonic image of the needle is buried in the image of the living body. Therefore, there is a problem that it is difficult to grasp how far the needle has entered.

  The present invention has been made in view of the above circumstances, and an object thereof is to provide an ultrasonic diagnostic apparatus having a function capable of improving the visibility of a puncture needle in a puncture under an ultrasonic guide, and a control method therefor. .

  In order to achieve the above object, the present invention takes the following measures.

  A first aspect of the present invention is an ultrasonic diagnostic apparatus that obtains a first image by performing ultrasonic transmission on a subject at a first time interval in order to visualize the inside of the subject, A transmission / reception unit that transmits a plurality of ultrasonic waves to the subject at a second time interval longer than the first time interval, and receives an echo signal corresponding to each transmission ultrasonic wave from the subject; An image generation unit that generates second image data by adding or subtracting the echo signals corresponding to sound waves to each other; a display unit that displays a second image based on the second image data; Is an ultrasonic diagnostic apparatus.

  According to a second aspect of the present invention, there is provided an ultrasonic probe including an ultrasonic transducer that transmits and receives an ultrasonic wave in each of a plurality of ultrasonic scanning directions in a subject in response to an applied drive signal. The drive signal is sent to the ultrasonic transducer so as to perform ultrasonic transmission a plurality of times with a predetermined rate period as a reference and including at least one polarity inversion for each of the ultrasonic scanning directions. A transmission control unit that supplies a plurality of reflected waves based on the plurality of ultrasonic transmissions transmitted on the basis of the predetermined rate period, and among the plurality of reflected waves, the predetermined An image generation unit that generates first image data by performing addition or subtraction processing using two reflected waves that are separated by at least two rates in time in a rate period, and the first image data Based on an ultrasonic diagnostic apparatus comprising a display unit for displaying the first image.

  According to a third aspect of the present invention, there is provided a method for controlling an ultrasonic diagnostic apparatus that obtains a first image by executing ultrasonic transmission to the subject at a first time interval in order to visualize the inside of the subject. A plurality of ultrasonic waves are transmitted to the subject at a second time interval longer than the first time interval, and echo signals corresponding to the respective transmission ultrasonic waves are received from the subject, Ultrasonic diagnosis comprising: adding or subtracting echo signals corresponding to sound waves to each other to generate second image data and displaying the second image based on the second image data It is an apparatus control method.

  According to a fourth aspect of the present invention, for each of a plurality of ultrasonic scanning directions in a subject, a plurality of ultrasonic transmissions including a predetermined rate period and including at least one polarity inversion are performed. And supplying the drive signal to an ultrasonic transducer, receiving a plurality of reflected waves based on the plurality of ultrasonic transmissions transmitted on the basis of the predetermined rate period, and among the plurality of reflected waves, By performing addition or subtraction processing using two reflected waves that are separated at least two rates in time in a predetermined rate period, first image data is generated, and based on the first image data, 1. An ultrasonic diagnostic apparatus control method comprising: displaying one image.

  As described above, according to the present invention, it is possible to realize an ultrasonic diagnostic apparatus having a function capable of improving the visibility of a puncture needle in a puncture under an ultrasonic guide, and a control method therefor.

  Hereinafter, first to fourth embodiments of the present invention will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary.

(First embodiment)
FIG. 1 is a block diagram of the ultrasonic diagnostic apparatus according to this embodiment. As shown in the figure, the ultrasonic diagnostic apparatus includes an ultrasonic probe 1, a storage unit 30, an input unit 7, a monitor 25, and an apparatus main body 50.

  The ultrasonic probe 1 generates an ultrasonic wave and transmits it to a subject, receives a reflected wave reflected in the subject and generates an echo signal, and is acoustic / electrically reversible such as a piezoelectric ceramic. It has a piezoelectric vibrator as a conversion element. A plurality of piezoelectric vibrators are arranged in parallel and are provided at the tip of the ultrasonic probe 1.

  The storage unit 30 stores images visualized in the past, images captured by the apparatus via a network or a removable storage medium, a dedicated program for executing a predetermined imaging sequence, and the like.

  The input unit 7 includes an input device such as a liquid crystal display panel, a keyboard, a trackball, a mouse, and a dedicated I / F for executing a “puncture mode” described later on the operation panel. An operator inputs patient information and transmission / reception conditions such as a rate period Tr or selects an image display mode from the input unit 7.

  The monitor 25 displays in-vivo morphological information and blood flow information as an image based on the video signal received from the apparatus main body 50. The image or the like displayed on the monitor 25 is stored in the storage unit in the apparatus main body 50 in response to a predetermined operation from the input unit 7 or the like.

  The apparatus main body 50 includes an ultrasonic transmission unit 2 that performs transmission control of ultrasonic waves transmitted from the ultrasonic probe 1, an ultrasonic reception unit 3 that performs preprocessing on echo signals received by the ultrasonic probe 1, A harmonic detection unit 4 that detects a harmonic component from the processed echo signal, a signal processing unit 5 that performs predetermined signal processing on the detected harmonic component to generate image data, and an ultrasonic image based on the image data Is generated and displayed, and a control circuit (CPU) 6 is provided.

  The ultrasonic transmission unit 2 includes a rate pulse generator 11, a transmission delay circuit 12, and a pulser 13. The rate pulse generator 11 generates a rate pulse that determines the repetition period (rate period) of the ultrasonic pulse radiated into the subject and supplies the rate pulse to the transmission delay circuit 12. Next, the transmission delay circuit 12 is composed of the same number of M-channel independent delay circuits as the ultrasonic transducers used for transmission, and a focusing delay time for focusing the ultrasonic pulse to a predetermined depth; A deflection delay time for transmitting an ultrasonic pulse in a predetermined direction is given to the received rate pulse, and this rate pulse is supplied to the pulser 13. The pulser 13 has the same number of M-channel independent drive circuits as the transmission delay circuit 12. Each ultrasonic transducer is driven by applying a drive signal generated by each drive circuit to the ultrasonic transducer provided in the ultrasonic probe 1, and radiates an ultrasonic pulse into the subject.

  The ultrasonic receiving unit 3 includes a preamplifier 14, an A / D converter 15, a beam former 16, and an adder 28. The preamplifier 14 is designed to amplify a minute signal converted into an electrical reception signal by the ultrasonic transducer and ensure a sufficient S / N. The preamplifier 14 amplifies the signal to a predetermined size. The fundamental wave component and the harmonic component of the received signal are converted into a digital signal by the A / D converter 15 and sent to the beam former 16. The beam former 16 includes a focusing delay time for focusing an ultrasonic reflected wave from a predetermined depth, and a deflection delay time for scanning the subject by sequentially changing the reception directivity of the ultrasonic reflected wave. Is added to the received signal converted into a digital signal, and the adder 28 performs phasing addition on the outputs from these beam formers 16 (adding the received signals obtained from a predetermined direction in phase).

  The harmonic extraction unit 4 includes a waveform memory 17, an adder / subtractor 18, and a filter circuit 19. The waveform memory 17 temporarily stores a reception signal obtained by the first transmission / reception in a predetermined direction. The adder / subtractor 18 is stored in the waveform memory 17 with a received signal obtained by transmission and reception for the second to nth times in the predetermined direction (n is a natural number of 2 or more, here, n = 4). Add or subtract the received signal. On the other hand, the filter circuit 19 is a filter that reduces a fundamental wave component that could not be eliminated by the phase inversion method due to movement of an organ, body movement, or the like.

  The signal processing unit 5 includes an envelope detector 20, a logarithmic converter 21, and a persistence converter 22. The envelope detector 20 performs an envelope detection operation on the input digital signal, The envelope is detected. The logarithmic converter 21 includes a look-up table for logarithmically converting an input value and outputting it. The logarithmic converter 21 logarithmically converts the amplitude of a received signal to relatively emphasize a weak signal. The persistence converter temporarily stores scanning lines for several frames in a memory and performs a process of averaging the luminance change.

  The image generation unit 8 includes a display image memory 23 and an image generation circuit 24. In the display image memory 23, the image data supplied from the signal processing unit 5 and incidental data such as characters and numbers related to the image data are combined and temporarily stored. The display image memory 23 temporarily stores image data obtained by combining a normal mode image and a puncture mode image, which will be described later, in a predetermined form. The stored image data and incidental data are displayed on the CRT monitor 25 after being subjected to D / A conversion and television format conversion in the image generation circuit 24.

  The control circuit 6 reads the transmission / reception conditions and the dedicated program stored in the storage unit 30 on the basis of instructions such as mode selection and transmission start / end input from the user input unit 7, and in accordance with these, each unit or the entire system is read Is controlled statically or dynamically.

  In particular, in the present embodiment, the control circuit 6 reads out a dedicated program for realizing a puncture mode function described later from the storage unit 30 and develops it on a predetermined memory, and executes control of each unit accordingly. For example, the control circuit 6 sends the drive pulse polarity switching control signal in the pulser 13 to the ultrasonic transmitter 2, and the control signal for determining filter characteristics such as the center frequency and frequency band in the filter circuit 19, The addition / subtraction control signals in the waveform memory 17 and the adder / subtractor 18 are supplied to the harmonic extraction unit 4.

(Puncture mode function)
Next, the puncture mode function of this ultrasonic diagnostic apparatus will be described. This function uses the phase inversion method to visualize the movement of the puncture needle as a motion artifact. In this embodiment, the image condition that is not suitable for diagnosis of a living body image but can improve the visibility of the puncture needle by extending the PRF and actively generating motion artifacts is “puncture mode”. Call it. Further, the image condition that has been used in normal diagnosis or the like so far is referred to as “normal mode”.

FIG. 2 is a conceptual diagram for explaining a scan sequence executed by the puncture mode function. As shown in the figure, in the imaging in the puncture mode, three times are obtained by converting the polarity to positive (time t ₁ ), negative (time t ₂ ), negative (time t ₃ ) for each scanning line. Ultrasonic transmission is performed with a predetermined PRF. Note that SP ₁ , SP ₂ , and SP ₃ in FIG. 2 schematically show the spectrum waveform of the echo signal obtained by the previous ultrasonic transmission.

FIG. 3 is a conceptual diagram for explaining signal processing of an ultrasonic echo signal acquired by the puncture mode function. As shown in the figure, for each scanning line, an echo signal corresponding to the transmission of the _first ultrasonic wave (that is, the ultrasonic wave having positive polarity at time t1 in FIG. 2) and the second ultrasonic wave (that is, , ultrasound with negative polarity at time t ₂ in FIG. 2) by adding the echo signals corresponding to the transmission, the normal mode image to generate an ultrasonic image used for diagnosis (normal mode image) For example, the data is generated in the adder / subtractor 18.

In contrast, adds the echo signals corresponding to the ultrasonic transmission of first, third ultrasound (i.e. ultrasound with negative polarity at time t ₃ in FIG. 2) and the echo signal corresponding to the transmission Thus, for example, the addition / subtraction unit 18 generates puncture mode image data for generating an ultrasonic image (puncture mode image) for grasping the movement of the puncture needle.

  Here, there is the following difference between generation of normal mode image data and generation of puncture mode image data. That is, the normal mode image data is generated using a PRF that is a normal relatively short period. For this reason, it is unlikely that motion artifacts due to body movements between the first ultrasonic transmission and the second ultrasonic transmission will occur, and ultrasonic image data capable of suitably imaging an organ or the like is generated. Can be generated. On the other hand, puncture mode image data is generated using a PRF twice as long as normal mode image data. For this reason, it is possible to generate ultrasonic image data that can preferably visualize motion artifacts caused by body movements and movements of the puncture needle that occur between the first ultrasonic transmission and the third ultrasonic transmission. it can.

  The normal mode image data is subjected to predetermined signal processing in the subsequent filter circuit 19 and the signal processing unit 5 and is displayed on the monitor 5 as a normal mode image. The same processing is performed on the puncture mode image data, and the puncture mode image data is displayed on the monitor 5 as a puncture mode image.

  FIG. 4 is a diagram showing an example of ultrasonic image display executed by the puncture mode function. As shown in the figure, on the monitor 5, for example, a normal mode image and a puncture mode image are simultaneously displayed in parallel. The surgeon can observe the state of the organ with the normal mode image and confirm the treatment while confirming the position of the puncture needle with the puncture mode image. In particular, during the operation, the puncture needle may be slightly moved to generate a luminance change on the ultrasonic image, thereby improving the visibility of the puncture needle. Since the puncture mode image is created using two signals that are separated in time from the normal time, the motion artifact is remarkably expressed as compared with the conventional case. Therefore, the operator can visually recognize the position of the puncture needle more clearly on the ultrasonic image as compared with the conventional case.

  FIG. 5 is a diagram showing another example of ultrasonic image display executed by the puncture mode function. As shown in the figure, the monitor 5 can achieve the same purpose by, for example, displaying a normal mode image and a puncture mode image in a superimposed manner.

  In the puncture mode, in order to improve the visibility of the puncture needle, it is preferable to make image processing such as dynamic range, gain, post process, and persistence different from the normal mode.

  Further, in order to maintain visibility even when the movement of the needle stops, a configuration in which peak hold processing (maximum luminance value holding processing) using images for several frames is separately performed may be employed.

  Furthermore, in order to make it easy to recognize the position of the puncture needle, at least a part of the puncture mode image (for example, a region including the puncture needle) may be displayed in a color different from that of the surrounding mode or the normal mode image.

(Operation)
Next, the operation in the puncture mode of the ultrasonic diagnostic apparatus will be described. FIG. 6 is a flowchart showing the flow of each process executed in the puncture mode. As shown in the figure, first, patient information, a diagnosis site, and the like are input (step S1), and an imaging mode is selected (here, “puncture mode” is selected) (step S2).

  Next, for each of the plurality of ultrasonic scanning lines (scanning direction), ultrasonic transmission is executed three times with positive, negative, and negative polarities based on a predetermined rate cycle (step S3). The reflected waves generated due to each of the transmission ultrasonic waves are received at the same rate (step S4).

  Next, in each scanning line, normal mode image data is generated by adding an echo signal based on the first positive transmission ultrasonic wave and an echo signal based on the second negative transmission ultrasonic wave. . Further, in each scanning line, puncture mode image data is generated by adding the echo signal based on the first positive transmission ultrasonic wave and the echo signal based on the third negative transmission ultrasonic wave (step) S5).

  Next, based on each generated image data, a normal mode image and a puncture mode image are displayed in a predetermined form (step S6).

  According to the configuration described above, the following effects can be obtained.

  According to this ultrasonic diagnostic apparatus, in imaging using the phase inversion method, at least two reflections that are separated in time compared to at least two reflected waves used for a diagnostic image (first image). A second image for actively visualizing motion artifacts is generated using the waves. By using this image, for example, in the treatment using a puncture needle, the first image and the second image displayed in parallel or superimposed are observed, so that the puncture needle can be compared with the conventional case. The position can be grasped more clearly. As a result, it can contribute to the provision of high-quality medical care.

  Further, according to the present ultrasonic diagnostic apparatus, no operation other than selecting the puncture mode first is required to visualize the puncture needle. Therefore, the operator can observe an ultrasonic image in which the puncture needle is clearly visualized without performing a special operation, and can reduce the work load during the operation.

  The puncture mode function realized by the ultrasonic diagnostic apparatus can also be realized by installing a dedicated program for realizing the function in an existing ultrasonic system. Therefore, a safe puncture needle or the like can be realized simply and at low cost.

(Second Embodiment)
Next, a second embodiment of the present invention will be described. In the present embodiment, the rate subtraction method is further used to visualize the puncture needle and the like. Note that the rate subtraction method is a technique for performing imaging using a difference between images having the same phase (or the same polarity), and is described in, for example, Japanese Patent Laid-Open No. 8-336527.

  FIG. 7 is a conceptual diagram for explaining a scan sequence executed by the puncture mode function according to the second embodiment. FIG. 8 is a conceptual diagram for explaining the signal processing of the ultrasonic echo signal executed by the puncture mode function according to the second embodiment.

As shown in FIG. 7, for example, three ultrasonic pulses of a positive polarity, a negative polarity, and a positive polarity with inverted polarities are transmitted to each of a plurality of ultrasonic scanning lines. In the figure, the echo signals obtained by each ultrasonic transmission are shown as spectrum waveforms as SP ₁ , SP ₂ and SP ₃ , respectively.

In the present embodiment, the normal mode image is generated based on image data obtained by adding SP ₁ (positive electrode) and SP ₂ (negative electrode) as in the _first embodiment. On the other hand, the puncture mode image is generated based on image data obtained by subtraction of SP ₁ (positive electrode) and SP ₃ (positive electrode). At this time, in the puncture mode image, a portion where there is no movement between the first ultrasonic transmission and the third ultrasonic transmission is not visualized by the subtraction process. However, when the puncture needle is moving during this time, it is suitably imaged as a motion artifact component remaining due to the difference.

  Even with such a configuration, the same effects as those of the first embodiment can be obtained, and the object can be achieved.

(Third embodiment)
Next, a third embodiment of the present invention will be described. In the present embodiment, imaging for improving the visibility of a puncture needle or the like is performed using a dummy rate. Note that the dummy rate is a rate at which ultrasonic transmission is performed but imaging using a reflected wave obtained by the ultrasonic transmission is not performed, or ultrasonic transmission itself is not performed.

  FIG. 9 is a conceptual diagram for explaining a scan sequence executed by the puncture mode function according to the third embodiment. FIG. 10 is a conceptual diagram for explaining signal processing of an ultrasonic echo signal executed by the puncture mode function according to the third embodiment.

In the present embodiment, for example, as shown in FIG. 9, ultrasonic transmission is performed three times for each of a plurality of ultrasonic scanning lines: a positive electrode, a negative electrode, a dummy rate, and a negative electrode. Further, in this embodiment, as shown in FIG. 10, the normal mode image is obtained by adding the reflected wave SP ₁ (positive electrode) and the reflected wave SP ₂ (negative electrode) as in the first and second embodiments. Generated based on the image data to be generated. On the other hand, the puncture mode image is generated based on image data obtained by adding the _first reflected wave SP ₁ (positive electrode) and the third reflected wave SP ₃ (negative electrode) sandwiching the dummy rate.

  By interposing a dummy rate in this way, the PRF can be made longer by one ultrasonic pulse than in the case of the first or second embodiment. Therefore, more motion artifacts occurring during that time can be visualized, and the visibility of the puncture needle can be improved.

  In the present embodiment, the first and third transmission ultrasonic waves may have the same polarity, and the puncture mode image may be generated by performing the rate subtraction method.

(Fourth embodiment)
Next, a fourth embodiment of the present invention will be described. This embodiment is another example using a dummy rate.

  FIG. 11 is a conceptual diagram for explaining a scan sequence executed by the puncture mode function according to the fourth embodiment. FIG. 12 is a conceptual diagram for explaining the signal processing of the ultrasonic echo signal executed by the puncture mode function according to the fourth embodiment.

  In this embodiment, for example, as shown in FIG. 11, two ultrasonic transmissions of a positive electrode, a dummy rate, and a negative electrode are performed for each of a plurality of ultrasonic scanning lines. The normal mode image is visualized in the B mode without the phase inversion only with the first positive electrode, and the puncture mode image uses the first positive ultrasonic wave and the third negative ultrasonic wave with the dummy rate in between. To visualize.

  By interposing a dummy rate as in the third embodiment, the PRF can be made longer by one ultrasonic pulse. Therefore, more motion artifacts occurring during that time can be visualized, and the visibility of the puncture needle can be improved.

  In the present embodiment, the first and second transmitted ultrasounds may have the same polarity, and the puncture mode image may be generated by performing the rate subtraction method.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. Specific examples of modifications are as follows.

(Fifth embodiment)
Next, a fifth embodiment of the present invention will be described. In each of the first to fourth embodiments, a technique is employed that positively generates motion artifacts by extending the PRF in order to improve the visibility of the puncture needle, although it is not suitable for diagnosis of a living body image. . In contrast, in the present embodiment, in the phase inversion method, for each scanning line, ultrasonic transmission for puncture needle imaging is performed after a desired delay time T has elapsed from the reference ultrasonic transmission, and this is used. An imaging technique that actively generates motion artifacts will be described.

  Hereinafter, in this embodiment, by setting a delay time T and actively generating motion artifacts, an imaging format that is not suitable for diagnosis of a biological image but can improve the visibility of a puncture needle is provided. This is called “puncture manual mode”.

  The block configuration of the ultrasonic diagnostic apparatus 1 according to the present embodiment is substantially the same as that shown in FIG. Hereinafter, only components having functions different from those of the above-described embodiments will be described.

  The storage unit 30 stores a dedicated program for realizing a manual puncture needle imaging mode, which will be described later, and a parameter group used in the manual puncture needle imaging mode.

  The control circuit 6 reads a dedicated program stored in the storage unit 30 and develops it on a memory (not shown) to realize a puncture manual mode function. This will be described in detail later.

  The ultrasonic transmission / reception unit 2 performs ultrasonic transmission / reception in accordance with the set transmission conditions in the puncture manual mode.

  The input unit 7 is an interface for setting a delay time T described later to a desired value.

(Puncture manual mode function)
Next, the puncture manual mode function will be described. In this mode, reference ultrasonic transmission is set. This is selected as the start time of the delay time T. For example, in the case where n times (n is an integer of 3 or more) of ultrasonic transmission including at least one phase inversion is performed on each scanning line, the first ultrasonic transmission or supervision for puncture needle imaging Ultrasonic transmission immediately before the sound wave transmission can be employed.

  In this embodiment, in order to make the description concrete, an example in which the puncture manual mode is applied to the scan sequence according to the first embodiment, that is, three times including one phase inversion for each scanning line. When performing ultrasonic transmission (positive, negative, and negative ultrasonic transmission), the ultrasonic waves for imaging the puncture needle at the third time according to the delay time T set with reference to the first ultrasonic transmission. The transmission shall be executed. However, the present puncture manual mode may be applied to a scan sequence according to any of the second to fourth embodiments, for example.

FIG. 13 is a conceptual diagram for explaining a scan sequence executed by the puncture manual mode function. As shown in the figure, in the imaging in this puncture manual mode, the polarity is changed to positive (time t ₁ ), negative (time t ₂ ), negative (time t ₃ ) for each scanning line three times. Perform ultrasonic transmission. Here, the time interval between time t ₁ and time t ₂ is one rate interval, and the time interval between time t ₁ and time t ₃ is a delay time T. Therefore, the operator can execute ultrasonic transmission for imaging a puncture needle at a time interval not limited by the PRF interval by setting the delay time T to a desired value by a predetermined operation. Artifacts can be actively generated and the puncture needle can be visualized.

FIG. 14 is a conceptual diagram for explaining signal processing of an ultrasonic echo signal acquired by the puncture manual mode function. As shown in the figure, for each scanning line, an echo signal corresponding to the transmission of the _first ultrasonic wave (that is, the ultrasonic wave having positive polarity at time t1 in FIG. 13) and the second ultrasonic wave (that is, , ultrasound with negative polarity at time t ₂ in FIG. 13) by adding the echo signals corresponding to the transmission, the normal mode image to generate an ultrasonic image used for diagnosis (normal mode image) For example, the data is generated in the adder / subtractor 18.

In contrast, the echo signal corresponding to the first transmission ultrasonic wave transmitted at time t ₁ and the third transmission ultrasonic wave after the delay time T has elapsed from time t ₁ (that is, time t in FIG. 13). Image data for generating an ultrasonic image (puncture manual mode image) for grasping the movement of the puncture needle by adding an echo signal corresponding to transmission (ultrasonic wave having negative polarity in ₃ ), For example, it is generated in the addition / subtraction unit 18. The post-stage filter circuit 19 and the signal processing unit 5 perform predetermined signal processing on the generated puncture manual mode image data to generate a puncture manual mode image. The generated puncture manual mode image is displayed on the monitor 5 in the form shown in FIG. 4, for example.

Here, for example, there is the following difference between the generation of the puncture mode image data acquired in the first embodiment and the generation of the puncture manual mode image data acquired in the present embodiment. That is, the puncture mode image data is generated using echo signals corresponding to two transmission ultrasonic waves having a time interval that is a constant multiple of PRF (twice in the first embodiment). On the other hand, the puncture manual mode image data includes an echo signal corresponding to the first ultrasonic wave transmitted at time t ₁ and a third ultrasonic wave transmitted at time t ₃ after the elapse of delay time T from time t _1. Is generated using an echo signal corresponding to. According to the puncture manual mode image data, a motion artifact caused by a motion generated during a desired delay time T, which is not limited by a constant multiple of PRF, can be suitably visualized.

  In the puncture manual mode, as in the case of the puncture mode, in order to improve the visibility of the puncture needle, image processing such as dynamic range, gain, post process, persistence, etc., peak hold processing, at least in the image It is preferable to perform a partial color display or the like.

(Operation)
Next, the operation of the ultrasonic diagnostic apparatus in the puncture manual mode will be described. FIG. 15 is a flowchart showing the flow of each process executed in the puncture manual mode. As shown in the figure, first, patient information, a diagnosis site, and the like are input (step S11), and an imaging mode is selected (here, “puncture manual mode” is selected) (step S12).

  Next, a parameter group related to ultrasonic transmission / reception in the puncture manual mode is input (step S13). Here, the parameter group relating to ultrasonic transmission / reception in the puncture manual mode means a parameter group including at least one of the number n of transmissions per scan line, the PRF, and the delay time T. For the selection of the parameter group, for example, a combination table of a plurality of setting values set in advance may be stored in the storage unit 30, and a desired combination may be selected from the table.

  Next, for each of the plurality of ultrasonic scanning lines (scanning direction), ultrasonic transmission is executed three times with positive, negative, and negative polarities in accordance with a predetermined PRF and delay time T (step S14), the reflected wave generated due to each of the transmission ultrasonic waves is received (step S15).

  Next, in each scanning line, normal mode image data is generated by adding an echo signal based on the first positive transmission ultrasonic wave and an echo signal based on the second negative transmission ultrasonic wave. . Further, in each scanning line, the puncture manual mode image data is generated by adding the echo signal based on the first positive transmission ultrasonic wave and the echo signal based on the third negative transmission ultrasonic wave ( Step S16). Based on the generated image data, the normal mode image and the puncture manual mode image are displayed in a predetermined form (step S17).

  According to the configuration described above, the following effects can be obtained.

  According to the present ultrasonic diagnostic apparatus, when performing ultrasonic transmission n times (n is an integer of 3 or more) including at least one phase inversion for each scanning line, a delay time T from the reference ultrasonic transmission is obtained. After the elapse of time, ultrasonic transmission for imaging the puncture needle is executed. Accordingly, ultrasonic transmission for the puncture needle image can be executed at a timing not limited by a constant multiple of the PRF (that is, after the delay time T has elapsed from the reference ultrasonic transmission), and is generated during the delay time T. Motion artifacts resulting from the movement of the puncture needle can be suitably imaged.

  The delay time T can be set to a value desired by the operator by a predetermined operation. Therefore, the operator can execute ultrasonic transmission for imaging a puncture needle according to a desired delay time T by a predetermined operation, and can use this to actively generate motion artifacts and visualize the puncture needle. it can.

  Further, the puncture manual mode function realized by the ultrasonic diagnostic apparatus can also be realized by installing a dedicated program for realizing the function in an existing ultrasonic system. Therefore, a safe puncture needle or the like can be realized simply and at low cost.

(Sixth embodiment)
Next, a sixth embodiment of the present invention will be described. In the present embodiment, the visibility of the puncture needle on the image is improved.

  FIG. 16 is a block diagram showing the configuration of the ultrasonic diagnostic apparatus according to the present embodiment. As shown in the figure, the ultrasonic diagnostic apparatus 1 according to the present embodiment is different from the configuration shown in FIG. 1 in that an image processing unit 40 and a Doppler processing unit 50 are further provided. Hereinafter, the image processing unit 40 and other components having functions different from those described above will be described.

  The image processing unit 40 includes a variable gain amplifier 41 and an image processor 42. The variable gain amplifier 41 is for increasing or decreasing the gain of the Doppler image signal, and is composed of, for example, a multiplication type D / A converter. The image processor 42 uses the B-mode image signal transmitted from the signal processing unit 5 and the Doppler image signal transmitted from the Doppler processing unit 50 to perform peak hold processing on the signal recognized as the puncture needle, and displays the locus This is an image generation auxiliary unit that has a function of predicting the path through which the puncture needle passes from the obtained trajectory and automatically correcting the guide when it deviates from the puncture guideline line. Here, the image processor 42 changes the gain of the variable gain amplifier 41 to reduce the color sensitivity of the color flow image.

  The transmission circuit 13 transmits an ultrasonic wave by a voltage pulse, a transmission frequency, etc. according to various programmed transmission conditions in a diagnostic sequence to be described later.

  The image generation circuit 24 divides the converted tomographic plane composed of information for each scanning line into pixels, assigns each pixel (pixel) to a memory address, and stores the reflection intensity information of the tomographic plane. Further, in order to draw a puncture guideline indicating a position where the puncture needle is inserted, the dot position of the puncture guideline is stored as data.

  The Doppler processing unit 50 includes a phase detection circuit 51, an analog-digital converter 52, an MTI filter 53, an autocorrelator 54, and a calculation unit 55, and extracts a blood flow component due to the Doppler effect and a moving component of the tip of the puncture needle. Doppler image information such as average speed, variance, and power is obtained for multiple points. The Doppler image information is sent to the monitor 25 via the image generation unit 8, and is displayed in color as an average speed image, a dispersed image, a power image, and a combination image thereof.

  The monitor 25 displays the tip of the puncture needle, the puncture guideline, and the like added and synthesized with the tomographic image in a form to be described later.

(Operation)
Next, the operation of the ultrasonic diagnostic apparatus according to the present invention will be described below with reference to the drawings.

  FIG. 17 is a flowchart showing an operation in the embodiment of the ultrasonic diagnostic apparatus according to the present invention. FIG. 18A is a diagram showing an ultrasonic image displayed on the monitor 25 when puncture is being performed in the present embodiment. For reference, FIG. 18B shows a conventional ultrasonic image displayed on the monitor 25 when the puncture is being performed.

  As shown in FIG. 17, first, when the puncture needle is moved (S1), a Doppler signal is transmitted from the signal processing unit 5 and the Doppler processing unit 50 to the image generation unit 8. The Doppler processing unit 50 determines whether or not the signal is a signal generated by the movement of the puncture needle (S2).

  As shown in FIG. 18B, conventionally, the image of the puncture needle is buried in the image of the living body, and it is difficult to grasp where the puncture needle is. Therefore, as shown in FIG. Of the signals transmitted from the Doppler processing unit 50 to the image generation unit 8, the threshold value is determined by the image processor 42 using the information on the brightness and position in the B mode and the information on the speed, power, and traveling direction in the Doppler mode. To recognize the puncture needle.

As a threshold value that the image processor 42 determines in order to recognize the puncture needle, for example,
(1) B mode brightness is high (2) Signal near puncture guideline (3) Doppler mode has velocity component (4) Doppler direction and puncture guideline direction almost match (5) Power For example, the image processor 42 recognizes a signal that satisfies at least one of the conditions as a puncture needle. The threshold value is stored in the storage unit 30 and is read out from the storage unit 30 by the image processor 42 when the threshold value is determined.

  In general, the puncture needle has only a relatively strong luminance at the needle tip (tip), but the other portions are weak in luminance, and thus are buried in a living body image. Therefore, when the Doppler signal satisfying the above condition is recognized (S2-Yes), it is recognized that it is caused by the movement of the puncture needle, and the B-mode image signal at the tip of the puncture needle is converted into an image processor. 42 performs peak hold processing. Thereby, the locus of the tip of the puncture needle is regarded as an image of the entire puncture needle, so that the image of the puncture needle becomes clearer and the tip of the puncture needle disappears even when the movement of the puncture needle stops and the Doppler component disappears And where the entire puncture needle is. The peak hold processing by the image processor 42 is performed in a state where the puncture needle is punctured (all states when the puncture needle is inserted, stopped, and removed). And when the puncture needle is moving, the conventional Doppler measurement is not performed.

  Here, in this embodiment, the visibility may be improved by the image processor 42 coloring the recognized puncture needle.

  Further, if the image processor 42 performs processing for displaying only the tip portion of the puncture needle recognized by the B-mode image signal in a different color, only the puncture needle tip can be emphasized, and how far the puncture needle has advanced. Becomes clearer.

  FIG. 19 is a diagram illustrating an image of the puncture needle that is peak-held in the above-described processing when the puncture needle advances and returns in the subject.

  In the puncture operation, a series of operations are performed in which the puncture needle is inserted after the puncture target site (“tumor to be puncture target” in the figure) and then removed. As shown in the above (3), When the needle is inserted, the Doppler image signal has a component that moves away from the body surface of the subject, and when the puncture needle is removed, the Doppler image signal has a component that approaches.

  Therefore, when the puncture needle is inserted, that is, when the Doppler image signal has a component that moves away (S3-Yes in FIG. 17), the locus of the puncture needle (tip portion) is left as described above (S4 in FIG. 17). When the puncture needle is pulled out (S3-No in FIG. 17), that is, when it is detected that the Doppler image signal has a component approaching the body surface of the subject, the tip of the puncture needle that is peak-hold displayed in the above-described processing The image processor 42 performs a process of deleting the moving displacement of the part trajectory (S5 in FIG. 17).

  As a result, the locus of the puncture needle does not remain even after the puncture needle is removed.

  FIG. 20 shows a diagram of when the puncture needle is shifted from the display angle of the puncture guideline and the angle of the puncture guideline is automatically corrected and displayed again.

  Usually, at the time of puncture, the image processing unit 40 generates an image of a line called a puncture guideline (for example, a dotted line), and the control circuit 6 superimposes it on the monitor 25 (on the ultrasonic image), thereby It can be compared with the display of insertion / extraction to / from the specimen.

  However, the puncture needle may be distorted due to the influence of tissue in the living body, and the puncture needle may not advance in the same direction as the direction indicated by the puncture guideline.

  Therefore, processing such as linear regression calculation is performed by the image processor 42 from the locus of the tip of the puncture needle displayed in the above-described processing, and the control circuit 6 predicts the direction in which the puncture needle advances, based on the result obtained thereby. Thus, the deviation from the puncture guideline is corrected and displayed again on the monitor 25.

  Specifically, the puncture guideline is a position where the control circuit 6 performs linear regression calculation based on the position of the puncture needle over time on the ultrasonic image specified by the B-mode image signal, and the puncture guideline is to be displayed. Is obtained by writing the puncture guideline in the display image memory 23. In other words, the position (dot) of the tip of the puncture needle over time specified by the B-mode image signal is considered as statistical data, and the linear regression calculation, which is one of statistical processing, is performed, so that the dot relationship A straight line that can be predicted to advance the puncture needle by approximating a straight line indicating is displayed as a puncture guideline.

  By doing in this way, the man-hour which has manually performed the correction processing of the position and angle of the puncture guideline indicating the ultrasonic image of the puncture needle and the position where the puncture needle is inserted before the subject is punctured Can be reduced. Moreover, since the puncture guideline can be corrected only by providing a linear regression calculation circuit, the correction can be performed by an inexpensive unit.

  Moreover, the puncture guideline of this embodiment may be displayed not as a single straight line but as two straight lines having an arbitrary angle. If the puncture guideline position and angle corrected here exceed the maximum guideline position and angle that can be expected to be corrected, an error message will be displayed to the examiner and correction will be performed again. You may be encouraged.

  For example, first, the control circuit 6 displays the puncture guideline generated by the image processor 42 on the monitor 25 at 67 deg, and the angle of the puncture needle is detected even when the puncture needle is shifted from 67 deg to 63 deg later. Since the image processor 42 corrects the puncture guideline to 63 deg and the control circuit 6 redisplays the result on the monitor 25, the direction in which the puncture needle advances can be displayed as the puncture guideline.

  Further, when the puncture needle is greatly deviated from 67 deg to 50 deg with respect to the puncture guideline, the image processor 42 instructs the monitor to display a message such as “cannot puncture correctly” on the ultrasonic image. . Therefore, the examiner who recognizes this message has an opportunity to redo the puncture.

  By displaying in this way, the examiner can confirm that the puncture needle has deviated significantly from the puncture guideline, and thus can prevent the subject from being harmed.

  FIG. 21 is a diagram showing puncture guidelines displayed on the monitor when the puncture needle is bent in a curved shape in the present embodiment.

  As shown in FIG. 21, when the puncture needle is bent in a curved line, as a method for correcting the puncture guideline deviation, the control circuit 6 performs image data (on the ultrasonic image) obtained by performing secondary regression calculation or the like. The coordinate guide information) represents a curved puncture guideline.

  Also at this time, the control circuit 6 executes the secondary regression calculation based on the position (coordinates) of the puncture needle over time on the ultrasonic image specified by the B-mode image signal. Further, the control circuit 6 writes the coordinates on the ultrasonic image obtained by this calculation into the display image memory 23 as a curved puncture guideline, and the control circuit 6 displays the information on the monitor 25. By doing so, even if the puncture needle bends in a curved shape, the control circuit 6 calculates the predicted path of the puncture needle and displays it on the monitor 25, so that correction can be performed with an inexpensive unit. it can.

(Seventh embodiment)
Next, a seventh embodiment will be described. The ultrasonic diagnostic apparatus according to the present embodiment performs puncture guideline emphasis display according to the sixth embodiment in imaging according to the puncture mode or puncture manual mode according to any of the first to fifth embodiments. is there.

  That is, the control circuit 6 uses the image data acquired according to the imaging mode (auto puncture mode or puncture manual mode) according to any one of the first to fifth embodiments, and performs puncture according to the sixth embodiment. The variable gain amplifier 41, the image processor 42, the display image memory 23, the image generation circuit 24, and the like are controlled so as to execute the guideline emphasis display.

  For example, when performing puncture guideline emphasis display in the visualization using the puncture mode according to the first embodiment, the processing shown in FIG. 17 is executed in step S6 of FIG. That is, the control circuit 6, the image processor 42, and the like perform peak hold processing, puncture guideline angle correction processing, and the like using puncture mode image data and puncture manual mode image data. In addition, the Doppler processing unit 50 uses at least two reflected waves separated by at least two rates or more for each scanning line (reflected waves corresponding to the first and third transmitted ultrasonic waves), and the speed in the Doppler mode. Perform component detection. The control circuit 6, the image processor 42, and the like execute recognition of the puncture needle and the like using the obtained velocity component.

  According to such a configuration, with the imaging mode according to any one of the first to fifth embodiments, a motion artifact caused by the movement of the puncture needle is preferably visualized, and the puncture guideline is highlighted. Accurate and highly visible puncture guidelines can be displayed on an ultrasound image. As a result, it can contribute to further improvement in the quality of medical practice.

  (1) Each function according to the present embodiment can be realized by installing a program for executing the processing in a computer such as a workstation and developing the program on a memory. At this time, a program that can cause the computer to execute the method is stored in a recording medium such as a magnetic disk (floppy (registered trademark) disk, hard disk, etc.), an optical disk (CD-ROM, DVD, etc.), or a semiconductor memory. It can also be distributed.

  (2) In each of the above embodiments, the improvement in the visibility of the puncture needle has been described as an example. However, the present invention is not limited to this, and can also be used when observing other clinically useful information such as movement of a living body.

  (3) In each of the above embodiments, the case where three ultrasonic transmissions (or three ultrasonic transmissions including a dummy rate) are performed for each of a plurality of ultrasonic scanning lines will be described as an example. It was. However, the ultrasonic transmission performed for each scanning line is not limited to three times, and more ultrasonic transmission may be performed. Even in the case of such a configuration, it is possible to visualize a puncture needle or the like more suitably than in the past by using echo signals based on two transmitted ultrasonic waves that are separated in time by at least two rates. Is possible.

  (4) In all the embodiments described above, symmetry is established with respect to the switching of the polarity of transmitted ultrasonic waves (replacement in which all positive polarity is negative and all negative polarity is positive) due to the characteristics of ultrasonic waves. Needless to say.

  In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

  As described above, according to the present invention, it is possible to realize an ultrasonic diagnostic apparatus having a function capable of improving the visibility of a puncture needle in a puncture under an ultrasonic guide, and a control method therefor.

FIG. 1 is a diagram illustrating an example of a block configuration of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a conceptual diagram for explaining a scan sequence executed by the puncture mode function according to the first embodiment. FIG. 3 is a conceptual diagram for explaining signal processing of an ultrasonic echo signal acquired by the puncture mode function according to the first embodiment. FIG. 4 is a diagram showing an example of ultrasonic image display executed by the puncture mode function. FIG. 5 is a diagram showing another example of ultrasonic image display executed by the puncture mode function. FIG. 6 is a flowchart showing the flow of each process executed in the puncture mode. FIG. 7 is a conceptual diagram for explaining a scan sequence executed by the puncture mode function according to the second embodiment. FIG. 8 is a conceptual diagram for explaining signal processing of an ultrasonic echo signal acquired by the puncture mode function according to the second embodiment. FIG. 9 is a conceptual diagram for explaining a scan sequence executed by the puncture mode function according to the third embodiment. FIG. 10 is a conceptual diagram for explaining signal processing of an ultrasonic echo signal executed by the puncture mode function according to the third embodiment. FIG. 11 is a conceptual diagram for explaining a scan sequence executed by the puncture mode function according to the fourth embodiment. FIG. 12 is a conceptual diagram for explaining signal processing of an ultrasonic echo signal executed by the puncture mode function according to the fourth embodiment. FIG. 13 is a conceptual diagram for explaining a scan sequence executed by the puncture manual mode function according to the fifth embodiment. FIG. 14 is a conceptual diagram for explaining signal processing of an ultrasonic echo signal acquired by the puncture manual mode function according to the fifth embodiment. FIG. 15 is a flowchart showing the flow of each process executed in the puncture manual mode according to the fifth embodiment. FIG. 16 is a block diagram illustrating a configuration of an ultrasonic diagnostic apparatus according to the sixth embodiment. FIG. 17 is a flowchart showing an operation in the embodiment of the ultrasonic diagnostic apparatus according to the sixth embodiment. FIG. 18A is a diagram showing an ultrasonic image displayed on the monitor 25 when a puncture is being performed in the sixth embodiment. FIG. 18B is a diagram showing a conventional ultrasonic image displayed on the monitor 25 when puncture is being performed. FIG. 19 is a diagram illustrating an image of the puncture needle that is peak-held in the above-described processing when the puncture needle advances and returns in the subject. FIG. 20 shows a diagram of when the puncture needle is shifted from the display angle of the puncture guideline and the angle of the puncture guideline is automatically corrected and displayed again. FIG. 21 is a diagram showing puncture guidelines displayed on a monitor when the puncture needle is bent in a curved shape in the sixth embodiment.

Claims (26)

In order to visualize the inside of a subject, an ultrasonic diagnostic apparatus that performs ultrasonic transmission at a first time interval on the subject to obtain a first image,
A transmission / reception unit that performs a plurality of ultrasonic transmissions to the subject at a second time interval longer than the first time interval, and receives echo signals corresponding to each transmission ultrasonic wave from the subject; and
An image generation unit that generates second image data by adding or subtracting the echo signals corresponding to each transmission ultrasonic wave to each other;
A display unit for displaying a second image based on the second image data;
An ultrasonic diagnostic apparatus comprising: The first image is an image for visualizing the form of the subject,
The ultrasonic diagnostic apparatus according to claim 1, wherein the second image is an image for visualizing a puncture needle inserted into the subject.   The ultrasonic diagnostic apparatus according to claim 1, wherein the display unit simultaneously displays the first image and the second image.   The ultrasonic diagnostic apparatus according to claim 1, wherein the second time interval is a constant multiple of the first time interval. An input unit for inputting the second time interval;
The ultrasonic diagnostic apparatus according to claim 1, wherein the transmission / reception unit transmits a plurality of ultrasonic waves to the subject at the second time interval input by the input unit. The image generation unit includes:
The position of the tip of the puncture needle inserted into the subject from at least one of the luminance information of the second image, Doppler information and position information based on transmitted ultrasound separated by the second time interval or more. Identify,
The ultrasonic diagnostic apparatus according to claim 1, wherein the second image including the identified locus of the tip is generated.   The image generation unit generates the second image including the identified locus of the tip by performing peak hold processing of a signal corresponding to the tip at the position of the identified tip. Item 6. The ultrasonic diagnostic apparatus according to Item 6.   The image generation unit generates the second image including a movement displacement in which the puncture needle approaches the subject surface using Doppler information based on transmission ultrasonic waves separated by the second time interval or more. The ultrasonic diagnostic apparatus according to claim 7, wherein the locus of the tip portion based on the peak hold process is deleted.   The ultrasonic diagnostic apparatus according to claim 6, wherein the image generation unit generates the first image including a puncture guideline that is a predicted travel path of the puncture needle based on a trajectory of the tip of the puncture needle.   The ultrasonic wave according to claim 9, further comprising a reporting unit for reporting the occurrence of the deviation to the operator when the deviation between the puncture guideline and the locus of the tip of the puncture needle exceeds a predetermined amount. Diagnostic device. In response to an applied drive signal, an ultrasound probe including an ultrasound transducer that transmits and receives ultrasound for each of a plurality of ultrasound scanning directions in the subject;
For each of the plurality of ultrasonic scanning directions, the drive signal is sent to the ultrasonic transducer so that ultrasonic transmission is performed a plurality of times with a predetermined rate period as a reference and including at least one polarity reversal. A transmission control unit to supply;
A receiving unit that receives a plurality of reflected waves based on the transmitted ultrasonic transmissions with the predetermined rate period as a reference;
An image generation unit that generates first image data by performing addition or subtraction processing using two reflected waves that are separated by at least two rates in time in the predetermined rate period among the plurality of reflected waves. When,
A display unit for displaying a first image based on the first image data;
An ultrasonic diagnostic apparatus comprising:   The ultrasonic diagnostic apparatus according to claim 11, wherein the first image is an image for imaging a puncture needle. The image generation unit performs an addition or subtraction process using a predetermined reflected wave of the plurality of reflected waves or at least two reflected waves corresponding to adjacent rates of the plurality of reflected waves. , Generate second image data,
The ultrasonic diagnostic apparatus according to claim 11, wherein the display unit displays the first image and the second image in parallel or superimposed on the basis of the second image data. The transmission control unit executes the ultrasonic transmission a plurality of times including at least one dummy rate that does not transmit ultrasonic waves,
The image generation unit includes:
Of the plurality of reflected waves, the first image data is generated by performing addition processing using two reflected waves that are separated by at least two rates in time and having different polarities in the predetermined rate period. ,
Generating second image data based on a predetermined reflected wave of the plurality of reflected waves;
The ultrasonic diagnostic apparatus according to claim 11, wherein the display unit displays the first image and the second image in parallel or superimposed on the basis of the second image data.   The ultrasonic diagnosis according to claim 11, wherein the image generation unit generates the first image using settings different from the second image for dynamic range, gain, post process, persistence, and other image processing conditions. apparatus.   The ultrasonic diagnostic apparatus according to claim 11, wherein the display unit displays at least a part of the first image in a color different from that of the second image. The transmission control unit performs the plurality of ultrasonic transmissions including at least two polarity inversions;
The image generation unit performs the subtraction process using two reflected waves that are separated by at least two rates in time and have the same polarity in the predetermined rate period among the plurality of reflected waves. The ultrasonic diagnostic apparatus of Claim 11 which produces | generates the image data of. The transmission control unit executes the ultrasonic transmission a plurality of times including at least one dummy rate that does not transmit ultrasonic waves,
The image generation unit performs the subtraction process using two reflected waves that are separated by at least two rates in time and have the same polarity in the predetermined rate period among the plurality of reflected waves. The ultrasonic diagnostic apparatus of Claim 11 which produces | generates the image data of. The transmission control unit executes the ultrasonic transmission a plurality of times including at least one dummy rate that does not transmit ultrasonic waves,
The image generation unit performs the addition process using two reflected waves that are separated by at least two rates in time and have different polarities in the predetermined rate period, among the plurality of reflected waves. The ultrasonic diagnostic apparatus of Claim 11 which produces | generates the image data of. The image generation unit includes:
A puncture inserted into the subject from at least one of the luminance information of the first image, Doppler information and position information based on two reflected waves temporally separated by at least two rates in the predetermined rate period Locate the tip of the needle,
The ultrasonic diagnostic apparatus according to claim 11, wherein the first image including the identified locus of the tip is generated.   The image generation unit generates the first image including the specified locus of the tip by performing peak hold processing of a signal corresponding to the tip at the position of the specified tip. Item 12. The ultrasonic diagnostic apparatus according to Item 11.   The image generation unit includes a displacement of the puncture needle approaching the subject surface using Doppler information based on two reflected waves that are separated by at least two rates in time in the predetermined rate period. The ultrasonic diagnostic apparatus according to claim 21, wherein, when generating an image of, the locus of the tip portion based on the peak hold process is deleted.   The ultrasonic diagnostic apparatus according to claim 20, wherein the image generation unit generates the first image including a puncture guideline that is a predicted travel path of the puncture needle based on a trajectory of the tip of the puncture needle.   The ultrasonic wave according to claim 23, further comprising a reporting unit for reporting the occurrence of the deviation to the operator when the deviation between the puncture guideline and the locus of the tip of the puncture needle exceeds a predetermined amount. Diagnostic device. In order to visualize the inside of a subject, a method of controlling an ultrasonic diagnostic apparatus that obtains a first image by executing ultrasonic transmission to the subject at a first time interval,
A plurality of ultrasonic transmissions to the subject at a second time interval longer than the first time interval, and an echo signal corresponding to each transmission ultrasonic wave is received from the subject,
Second echo data is generated by adding or subtracting the echo signals corresponding to each transmission ultrasonic wave,
Displaying a second image based on the second image data;
An ultrasonic diagnostic apparatus control method comprising: For each of a plurality of ultrasonic scanning directions in the subject, the drive signal is sent to the ultrasonic transducer so that ultrasonic transmission is performed a plurality of times with a predetermined rate period as a reference and including at least one polarity reversal. Supply
Based on the predetermined rate period, a plurality of reflected waves based on the transmitted ultrasonic transmissions are received,
By performing addition or subtraction processing using two reflected waves that are separated by at least two rates in time in the predetermined rate period among the plurality of reflected waves, the first image data is generated,
Displaying a first image based on the first image data;
An ultrasonic diagnostic apparatus control method comprising:

Images