JP2008178589A - Ultrasonic diagnostic apparatus, puncture needle used for ultrasonic diagnosis, and needle information processing program - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic apparatus, a puncture needle used for an ultrasonic diagnosis, and a needle information processing program for improving visibility of the puncture needle used under an ultrasonic image. <P>SOLUTION: The ultrasonic diagnostic apparatus 1 includes: an ultrasonic probe 3 which transmits ultrasound with a subject P punctured with the puncture needle 25 filled inside with a fluid containing a strong reflector and receives ultrasound reflected signals; and data processing parts 12, 13 for generating image signals for making the fluid inside the puncture needle 25 visible from the ultrasound reflected signals received by the ultrasonic probe 3. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus for performing diagnosis while inserting a puncture needle into a treatment target region of a subject, a puncture needle used for ultrasonic diagnosis, and a needle information processing program.

  An ultrasonic diagnostic apparatus irradiates an ultrasonic pulse into a subject from a piezoelectric vibrator built in an ultrasonic probe, receives a reflected wave generated in the subject with the piezoelectric vibrator, and performs various processes. An apparatus for obtaining biological information such as tomographic images and blood flow information in a subject.

  One of the treatment methods using this ultrasonic diagnostic apparatus is called an ultrasonic puncture method. In the treatment by the ultrasonic puncture method, a puncture needle (PEIT (percutaneous ethanol injection treatment) needle, radiofrequency puncture needle, microwave puncture needle is applied to the treatment target part of the subject which is a tumor part such as cancer in an organ under an ultrasonic guide. Including treatment needles such as needles, the same applies hereinafter).

  When ultrasonic diagnosis is performed by inserting a puncture needle into a subject, a guide mechanism and a puncture adapter for setting the insertion direction of the puncture needle are provided in an ultrasonic probe of an ultrasonic diagnostic apparatus used for ultrasonic diagnosis. It is done. Then, the puncture needle is inserted so as to be positioned within the diagnostic visual field of the ultrasonic diagnostic apparatus.

  In addition, on the screen of the ultrasonic diagnostic apparatus, a puncture path of a puncture needle previously installed by a guide mechanism or a puncture adapter is preset. The preset insertion path of the puncture needle is referred to as an index when the puncture needle is inserted into the subject. That is, the puncture needle insertion operation is performed by placing a preset puncture needle insertion path at a target site where the puncture needle is to be inserted.

  Then, cancer coagulation treatment is performed in which cells at the target site are collected from the inserted puncture needle or a drug such as ethanol is injected into the target site via the puncture needle. In recent years, ablation puncture needles that radiate microwaves or radio waves and cauterize cancerous portions are inserted and cancer ablation treatment is performed (see, for example, Non-Patent Document 1).

  In the insertion of the puncture needle performed under the ultrasonic guide, the puncture needle is thin and the insertion direction is substantially parallel to the ultrasonic beam of the ultrasonic diagnostic apparatus at a shallow angle. For this reason, when an ultrasonic image is captured by transmitting and receiving ultrasonic waves, a reflected wave signal with sufficient intensity cannot be obtained by the puncture needle, and the position of the puncture needle may not be displayed stably and clearly on the ultrasonic image. .

  In addition, since the resistance of the organ or tissue exists during the insertion of the puncture needle, the needle tip of the puncture needle bends in a direction with less resistance and deviates from the width of the ultrasonic beam in the tomographic image direction (slice direction). The puncture needle may be inserted. In this case, there is no puncture needle in the ultrasonic tomographic plane. Furthermore, since organs and tissues move with breathing, there is a possibility that the puncture needle may shift out of the ultrasonic beam that is the visual field after insertion.

In view of this, a technique has been devised that emphasizes a reflected signal within a predetermined range along the guide direction of the puncture needle guide mechanism when a reflected signal with sufficient strength cannot be obtained from the puncture needle (for example, Patent Document 1). reference). Also, a technique has been devised that corrects the ultrasonic beam to a puncture needle that is out of the field of view when the puncture needle is out of the field of view (see, for example, Patent Document 2).
JP 63-290550 A JP 2000-107178 A Edited by Shigehiro Kokubun and Fuminori Moriyasu, “Practical Liver Cancer Radiocoagulation”, Nanedo, May 2002

  However, in a diagnosis using a puncture needle under a conventional ultrasonic guide, an ultrasonic image cannot be obtained with sufficient accuracy, and observation is often difficult. As a result, there is a risk that the operation of inserting the puncture needle into the target diagnostic site becomes very difficult. In other words, the conventional technique has a problem that it cannot be said to be sufficient in terms of stability and operability in displaying an image of the puncture needle.

  In general, in ultrasound-guided treatment, the ultrasonic probe is moved and observed at various positions on the body surface, so that the positional relationship between the blood vessels and surrounding organs and the tumor and the positional relationship between the needle tip of the puncture needle Be grasped. In particular, in the case of cauterization treatment using radio waves and microwaves under ultrasound guidance, it is necessary to observe the progress with ultrasound images during the treatment.

  In addition, in the cauterization treatment, there is a problem that the back of the cauterization site cannot be observed from the position of the ultrasonic probe immediately above the treatment site due to tissue alteration due to cauterization and generated bubbles. For this reason, the puncture adapter is removed from the ultrasound probe during treatment, the puncture needle is separated from the ultrasound probe, and then the organ or tissue including the periphery of the target diagnostic site is scanned with the ultrasound probe from the desired direction. Often observed.

  However, it is difficult to reliably detect a puncture needle punctured in the liver with a B-mode image. This is because the puncture needle may be difficult to see depending on the relationship between the position of the puncture needle and the ultrasonic beam and the brightness of the organ into which the puncture needle is inserted.

  In recent years, a three-dimensional ultrasonic diagnostic apparatus displays an image of a predetermined volume or displays a plurality of designated tomographic planes in real time. However, in the present situation, when displaying a three-dimensional image, a method for displaying the needle tip of the puncture needle and its surroundings following the puncture needle to be inserted has not been established.

  The present invention has been made to cope with such a conventional situation, and an ultrasonic diagnostic apparatus capable of improving the visibility of a puncture needle used under an ultrasonic image, a puncture needle used for ultrasonic diagnosis, and An object is to provide a needle information processing program.

  In order to achieve the above object, an ultrasonic diagnostic apparatus according to the present invention is characterized in that, as described in claim 1, an ultrasonic puncture needle into which a fluid containing a strong reflector is injected is punctured in a subject. An ultrasonic probe that transmits a sound wave and receives an ultrasonic reflection signal, and data processing that generates an image signal from which the fluid inside the puncture needle can be visually recognized from the ultrasonic reflection signal received by the ultrasonic probe Part.

  Further, in order to achieve the above-described object, the ultrasonic diagnostic apparatus according to the present invention is a state in which a puncture needle into which a fluid containing a strong reflector is injected is punctured in a subject as described in claim 6 An ultrasonic probe for transmitting an ultrasonic wave and receiving an ultrasonic reflection signal, and a signal for detecting a fluid signal received from the fluid inside the puncture needle among the ultrasonic reflection signals received by the ultrasonic probe And a detector.

  In addition, the puncture needle used for ultrasonic diagnosis according to the present invention has a flow channel for injecting a fluid containing a strong reflector, as described in claim 10, in order to achieve the above-described object. It is characterized by that.

  Further, in order to achieve the above-described object, the needle information processing program according to the present invention forms a fluid flow path inside the computer and sets the fluid flow path as described in claim 12. A fluid containing a strong reflector is injected into the puncture needle provided with a characteristic shape part whose shape is different from the shape of the flow path in the other part, and further received by the ultrasonic probe while puncturing the subject. A signal detection unit for detecting a fluid signal received from the fluid inside the puncture needle, and a signal processing unit for detecting the position of the characteristic shape portion from the fluid signal detected by the signal detection unit And a needle information calculation unit that obtains needle information that is information related to the puncture needle based on the position of the characteristic shape portion detected by the signal processing unit and the shape information of the puncture needle. It is characterized in that to function.

  In the ultrasonic diagnostic apparatus, the puncture needle used for ultrasonic diagnosis, and the needle information processing program according to the present invention, the visibility of the puncture needle used under the ultrasonic image can be improved.

  Embodiments of an ultrasonic diagnostic apparatus, a puncture needle used for ultrasonic diagnosis, and a needle information processing program according to the present invention will be described with reference to the accompanying drawings.

  FIG. 1 is a configuration diagram showing an embodiment of an ultrasonic diagnostic apparatus and a puncture needle according to the present invention.

  The ultrasonic diagnostic apparatus 1 is configured by providing an ultrasonic probe 3, a console 4, and a monitor 5 in an apparatus main body 2. The console 4 is configured by providing an input device 9 such as a keyboard 7 and a trackball 8 on an operation panel 6. The apparatus main body 2 includes an ultrasonic transmission unit 10, an ultrasonic reception unit 11, a B mode processing unit 12, a color mode processing unit 13, a display unit 14, a cine memory 15, a database 16, a CPU (Central Processing Unit) 17, a speed parameter. In addition to the setting unit 18, a puncture needle information processing system 19 is mounted.

  The puncture needle information processing system 19 includes a signal detection unit 20, a signal processing unit 21, and a needle information calculation unit 22. Part or all of the puncture needle information processing system 19 and other components of the apparatus main body 2 can be constructed by reading a program into a computer or can be configured by a circuit.

  The ultrasonic transmission unit 10 has a function of generating a transmission pulse and giving it to the ultrasonic probe 3, while the ultrasonic reception unit 11 receives a reception signal from the ultrasonic probe 3 to receive the B mode processing unit 12 and the color mode. It has a function to be given to the processing unit 13. The ultrasonic probe 3 converts the transmission pulse received from the ultrasonic transmission unit 10 into an ultrasonic pulse and transmits it to the diagnostic part P0 in the subject P, while receiving the reflected signal generated at the diagnostic part P0, It has the function to give to the ultrasonic receiver 11 as a received signal.

  The B mode processing unit 12 has a function of processing a reception signal received from the ultrasonic wave reception unit 11 to generate a B mode image signal. The color mode processing unit 13 has a function of processing a reception signal received as a Doppler signal from the ultrasonic reception unit 11 and generating a Doppler image signal by the Doppler method. The color mode processing unit 13 is provided with a wall filter (fall filter) 23 as is well known. Then, the wall filter 23 removes unnecessary clutter components from the Doppler signal and extracts a velocity component such as a blood flow signal included in a preset velocity range. Further, a Doppler image signal is generated based on the extracted velocity component.

  The display unit 14 performs a display process of the B mode image signal acquired from the B mode processing unit 12 and the Doppler image signal acquired from the color mode processing unit 13 to generate an image signal to be displayed on the monitor 5. A function of writing and storing the generated image signal in the cine memory 15 and a function of displaying the ultrasonic image such as a B-mode image or a Doppler image by supplying the generated image signal to the monitor 5. In the display unit 14, for example, an image signal obtained by combining a B-mode image and a Doppler image is generated. The cine memory 15 is a memory for storing the image signal created in the display unit 14.

  On the other hand, the ultrasonic probe 3 is provided at a position where ultrasonic waves can be transmitted to and received from the diagnosis site P0 of the subject P. The ultrasonic probe 3 is provided with a guide mechanism 24, and a puncture needle 25 is provided at a predetermined position of the guide mechanism 24. The guide mechanism 24 guides the insertion direction of the puncture needle 25 when the puncture needle 25 is inserted into the subject P. Furthermore, a fluid injection device 26 for injecting a required fluid into the puncture needle 25 is connected to the puncture needle 25. The fluid injection device 26 is provided with a function of controlling the fluid injection speed as necessary.

  The ultrasonic diagnostic apparatus 1 and the puncture needle 25 form an ultrasonic guided puncture system. That is, the puncture needle 25 is configured to be inserted toward the diagnosis site P0 of the subject P under the ultrasound guide by the ultrasound diagnostic apparatus 1.

  FIG. 2 is a cross-sectional view showing a structural example of the puncture needle 25 shown in FIG.

  The puncture needle 25 is a needle having a sharp tip, and a fluid X channel 30 is formed therein. The flow path 30 of the fluid X is, for example, a path that is guided from the root side of the puncture needle 25 to the root side after passing through the tip side. For this reason, the fluid X can be perfused into the puncture needle 25 by flowing the fluid X from the fluid injection device 26 into the flow path 30 of the puncture needle 25.

  Further, the flow path 30 of the fluid X inside the puncture needle 25 can be formed by, for example, a hole having a required inner diameter, but the shape of a desired portion is different from the shape of other portions. Hereinafter, the shape part of this different flow path 30 is referred to as a characteristic shape part 31. FIG. 2 is a diagram illustrating an example in which the diameter of the flow path 30 is made smaller than that of other portions in the characteristic shape portion 31 of the puncture needle 25 and the flow path 30 is narrowed.

  The fluid X injected into the flow path 30 of the puncture needle 25 can be any fluid X as long as it is a fluid X that can acquire an ultrasonic reflection signal. The fluid X is injected into the flow path 30 at a constant flow rate, for example, manually, and is perfused or retained in the flow path 30. In addition, if a contrast agent including a strong reflector such as a microbubble that generates an ultrasonic reflection signal that is relatively stronger and stronger than an organ or an organ in the subject P is used as the fluid X, an ultrasonic receiver By processing the ultrasonic reflection signal from the strong reflector received by 11 in the B mode processing unit 12, the fluid X can be visualized as a B mode image.

  In addition, since the shape of the flow channel 30 inside the puncture needle 25 is different from the shape of other portions in a specific portion, a portion (specific shape portion) where the flow channel 30 is different can be confirmed as an image. . For example, as shown in FIG. 2, when the flow path 30 is narrow at a specific portion, the shape of the flow path 30 is captured as an image.

  Further, when the fluid X is perfused inside the puncture needle 25 and a strong reflector such as a microbubble is moving, if the Doppler signal from the fluid X is received and collected by the ultrasonic receiver 11, the color mode In the processing unit 13, the flow of the fluid X can be detected as a Doppler image by the Doppler method. In particular, when the specific shape portion inside the puncture needle 25 has a shape in which the flow path 30 is narrow, the flow velocity of the fluid X becomes faster than the other portions. It is possible to detect. Therefore, conversely, even if the flow path 30 in a specific part is widened, it is possible to detect the difference in the velocity of the fluid X similarly by the Doppler mode.

  The fluid X in the puncture needle 25 is thus generated as an image signal on the display unit 14 by the B mode method or the Doppler method, and is given to the monitor 5 to be displayed as an image. Can be understood more clearly.

  FIG. 3 is a schematic diagram illustrating an example of an image generated by the ultrasonic diagnostic apparatus 1 illustrated in FIG. 1 and visualized with the puncture needle 25.

  FIG. 3 shows an example in which the puncture needle 25 is provided with a channel 30 in one direction and the inner diameter of the channel 30 is partially reduced. As shown in FIG. 3, when the puncture needle 25 is inserted toward the diagnosis site P0 of the subject P, the positions of the puncture needle 25 and the specific shape site can be visualized. The image of the puncture needle 25 and the specific shape part can be obtained as a B-mode image, or can be obtained as a Doppler image by the Doppler method using the velocity difference of the fluid X.

Specific examples of the fluid X injected into the puncture needle 25 include a contrast agent containing a strong reflector such as microbubbles, a microcapsule enclosing gas, or a contrast agent containing microparticles. However, not only a contrast agent as a drug but also a liquid containing a strong reflector can be used as the fluid X for other industrial liquids. The contrast agent can be prepared by stirring a suitable solvent to generate microbubbles. For example, a method for creating a bubble containing carbon dioxide as a main component is known as the “CO ₂ angio method”.

  If the fluid X injected into the puncture needle 25 is a contrast agent, it is a B-mode image or a Doppler image depending on a contrast mode which is a video mode (imaging method) in which data processing is tuned up for the contrast agent. It is possible to detect the position of the puncture needle 25 with high sensitivity regardless of whether or not. For example, a contrast agent such as Sonovue (registered trademark), OPTISON (registered trademark), Definitity, Sonazoid (registered trademark) in which a hardly soluble gas such as fluorocarbon is enclosed as microbubbles can be used as the fluid X. In this case, if an ultrasonic diagnostic image is generated by a low acoustic pressure harmonic echo method that generates an ultrasonic diagnostic image using twice or three times the fundamental frequency of the ultrasonic reflected signal and a harmonic (harmonic) component, Microbubbles can be imaged with high sensitivity without perfusing X, and the puncture needle 25 can be observed stably for a certain period of time.

  Furthermore, if the fluid X injected into the puncture needle 25 is a contrast agent such as Levovist (registered trademark) in which air is encapsulated as microbubbles, a high-pressure harmonic echo method, a dynamic flow method using pseudo Doppler, or a powered The puncture needle 25 can be imaged with high sensitivity by an imaging method such as a plastic method.

  However, when using the high sound pressure contrast mode, the microbubbles may be lost by the transmitted ultrasonic waves. Therefore, in order to visualize the puncture needle 25 clearly, it is important to perfuse the contrast medium and always distribute fresh microbubbles in the puncture needle 25. In other words, if the contrast medium containing microbubbles is perfused into the puncture needle 25 as the fluid X, the disappearance of the microbubbles can be suppressed, and a high-intensity ultrasonic reflection signal can be stably generated with a fresh contrast medium. Can be obtained.

  As described above, the imaging method of the puncture needle 25 is not limited to the contrast mode using the contrast agent, and depending on the conditions, the B mode method using the fundamental wave of the reflected signal is also possible.

  Further, the perfusion speed of the fluid X is controlled by the fluid injection device 26 so that the moving speed becomes faster than the periphery of the fluid X, while the predetermined speed component extraction speed of the wall filter 23 provided in the color mode processing unit 13 is set. If the parameter (filter coefficient) is set according to the perfusion speed of the fluid X, the fluid X moving faster than the surroundings can be appropriately detected and imaged by the Doppler method.

  In particular, when a puncture needle 25 is punctured under contrast with a contrast agent to treat a liver tumor, the puncture needle 25 is punctured while clearly imaging the liver in a contrast mode using the Doppler method. If the color information is colored using the velocity information of the contrast medium flowing in the blood vessel 25, the liver tumor and the puncture needle 25 can be discriminated and displayed on the monitor 5. In this case, the setting of the speed parameter of the wall filter 23 according to the speed of the contrast agent is effective.

  Therefore, the speed parameter setting unit 18 adjusts the speed parameter for determining the speed component extracted by the wall filter 23 according to the information input from the input device 9 via the operation panel 6 to the perfusion speed of the fluid X. A function to set is provided.

  Here, a detailed example of the speed parameter setting method of the wall filter 23 will be described. When setting the speed parameter of the wall filter 23, the insertion angle θ of the puncture needle 25 is referred to. Therefore, the speed parameter setting unit 18 has a function of giving image information to the display unit 14 so that the insertion angle θ of the puncture needle 25 is displayed on the monitor 5.

  FIG. 4 is a schematic diagram of an ultrasonic image displaying the insertion angle θ of the puncture needle 25 shown in FIG.

  A puncture adapter for fixing the puncture needle 25 to the ultrasonic probe 3 is attached to the ultrasonic probe 3 as the guide mechanism 24 or in addition to the guide mechanism 24. And it is comprised so that the direction of the puncture needle 25 can be changed by driving a puncture adapter. Therefore, the inclination angle of the puncture line 50 representing the insertion angle θ of the puncture needle 25 can be obtained based on the control information given to the puncture adapter.

  The insertion angle θ of the puncture needle 25 is normally selected by the user and input from the apparatus panel 6 to the CPU 17. Then, the puncture line 42 is displayed on the ultrasonic image displayed on the monitor 5 corresponding to the puncture angle θ of the puncture needle.

Here, assuming that the perfusion speed of the fluid X is set to v by the fluid injection device 26, the Doppler shift frequency fd observed in the Doppler mode is expressed as in Expression (1).
[Equation 1]
fd = 2vf0cosθ / c (1)
However, in Formula (1), c shows the sound speed of blood and is about 1500 m / sec. F0 indicates the transmission frequency of the ultrasonic wave. As described above, θ is an angle formed by the traveling direction B of the ultrasonic beam and the puncture line 50 and indicates the insertion angle of the puncture needle 25. In Expression (1), for example, assuming that the ultrasonic transmission frequency f0 = 2 MHz, the perfusion speed v = 250 mm / sec of the fluid X, and the insertion angle θ of the puncture needle 25 = 20 degrees, the Doppler shift frequency fd≈ 0.6kHz.

  Therefore, the value of the cutoff frequency of the signal, which is one of the velocity parameters of the wall filter 23, is a Doppler shift frequency fd≈0.6 so that the fluid X with the perfusion velocity v = 250 mm / sec obtained by the equation (1) can be observed. The cut-off value can be set so that the kHz Doppler signal can be sufficiently detected.

  Thus, the cutoff value of the wall filter 23 can be calculated from the insertion angle θ of the puncture needle 25 and the perfusion speed v of the fluid X. Therefore, the speed parameter setting unit 18 is configured to calculate an appropriate cutoff value of the wall filter 23 in response to the input of the insertion angle θ of the puncture needle 25 and the perfusion speed v of the fluid X from the operation panel 6. . The speed parameter setting unit 18 is configured to give the obtained cutoff value to the wall filter 23 for control.

  As shown in FIG. 4, the angle formed between the traveling direction B of the ultrasonic beam and the puncture line 50, that is, the insertion angle θ of the puncture needle 25 is different for each ultrasonic beam. Therefore, if the cutoff value of the wall filter 23 is set for each ultrasonic beam, the fluid X can be detected more accurately and specifically and imaged.

  Moreover, since blood flow exists in a living organ, there is a possibility that discrimination between the blood flow and the fluid X is not sufficiently performed. However, in an organ such as the liver, for example, blood flow with a speed exceeding 200 mm / sec is limited to the artery and the time phase is limited between beats. Therefore, for example, if the perfusion speed v of the fluid X is set to a high value of about 200 mm / sec, it is effective in improving the specific visibility of the fluid X.

  In addition, when an ultrasonic contrast agent or microbubble is used as the fluid X, it is known that the fluid X reacts as an ultrasonic wave to be transmitted and the bubble disappears. On the other hand, when the microbubbles are observed by the Doppler method under the condition where the sound pressure of the transmission ultrasonic wave is set high, a wide band Doppler shift frequency is observed even if the bubbles are stationary. Therefore, when an ultrasonic contrast agent or microbubble is used as the fluid X, the cut-off value of the wall filter 23 is set as the blood flow in the organ under the condition that the sound pressure of the transmission ultrasonic wave is set high. By setting the speed to a rarely high speed, specific imaging of the fluid X is possible.

  Further, instead of setting the cut-off value of the wall filter 23, the color of the color map corresponding to the Doppler shift frequency fd calculated according to the equation (1) is made specific so that the puncture needle 25 or the puncture needle It becomes possible to observe the fluid X perfused in the 25 with good visibility on the Doppler image. In this case, a color map adjustment unit is provided, and the color map adjustment unit receives the insertion angle θ of the puncture needle 25 and the perfusion speed v of the fluid X from the operation panel 6 and calculates the Doppler shift frequency fd. The instruction information may be given to the display unit 14 so as to change the color of the color map corresponding to the obtained Doppler shift frequency fd to a predetermined color.

  As described above, the optimum cut-off value of the wall filter 23 can be automatically calculated and set if the information on the contrast medium to be administered and the insertion angle θ of the puncture needle 25 are given.

  Next, functions of the puncture needle information processing system 19, the CPU 17, and the database 16 will be described.

  The CPU 17 functions to control the signal detection unit 20, the signal processing unit 21, and the needle information calculation unit 22 of the puncture needle information processing system 19 and the database 16 according to information input from the input device 9 via the operation panel 6. It has a function of executing writing and reading of information. The CPU 17 also has a function of controlling the overall operation of the ultrasonic diagnostic apparatus 1 in accordance with information from the input device 9, but the description thereof is omitted here. Further, as described above, the CPU 17 generates image information for displaying the puncture line 42 on the monitor 5 in accordance with the insertion angle θ of the puncture needle 25 input from the device panel 6, and the generated image information is displayed on the display unit 14. The function to output to.

  The signal detection unit 20 acquires an image signal such as a B-mode image signal or a Doppler image signal from the display unit 14, and an image from the fluid X (strong reflector such as a microbubble or a microcapsule) injected into the puncture needle 25. It has a function of detecting a signal and a function of supplying an image signal from the detected fluid X to the signal processing unit 21.

  The signal processing unit 21 receives an image signal from the fluid X from the signal detection unit 20 and automatically detects the position of the characteristic shape portion 31 formed in the flow path 30 of the puncture needle 25 by an arbitrary image recognition method. And the position of the puncture needle 25 and the characteristic shape part 31 is given to the needle information calculation unit 22 as position information.

  Here, as an example of the image recognition method for detecting the image signal from the fluid X (that is, the puncture needle 25), for example, a detection method by performing threshold processing of signal intensity can be mentioned. That is, a method using a luminance difference of a B-mode image or a speed difference in a Doppler image can be mentioned.

  In the method of detecting an image signal from the puncture needle 25 using the luminance difference of the B-mode image, a threshold value of luminance is set in the signal detection unit 20, and an area equal to or larger than the set threshold value is set in the fluid X in the puncture needle 25. The position of the fluid X (puncture needle 25) can be detected by regarding the region.

  Furthermore, the position of the feature-shaped part 31 can be detected by recognizing the part having the shape of the feature-shaped part 31 in the region of the fluid X (puncture needle 25) by the signal processing unit 21. For example, when the portion where the flow path 30 of the fluid X is narrowed as shown in FIG. 2 is the characteristic shape portion 31, a portion having a small width in the region of the fluid X (puncture needle 25) Can be detected.

  On the other hand, in the method of detecting the image signal from the puncture needle 25 using the difference in speed of the Doppler image, the signal detection unit 20 determines the position of the puncture needle 25 by regarding the area above the constant speed as the area of the puncture needle 25. Can be detected. Further, in the area of the puncture needle 25, a part having a speed different from that of other parts can be detected as the characteristic shape part 31 by the signal processing unit 21. For example, when the portion where the flow path 30 of the fluid X is narrowed as shown in FIG. 2 is the characteristic shape portion 31, a high speed portion can be detected as the characteristic shape portion 31 in the region of the puncture needle 25. it can.

  In the database 16, shape information of the puncture needle 25 is stored in advance. The information stored in the database 16 can also include the shape of the specific shape portion and position information on the puncture needle 25. Then, the CPU 17 is configured to be able to give the shape information of the puncture needle 25 stored in the database 16 to the needle information calculation unit 22 in accordance with an instruction from the input device 9.

  The needle information calculation unit 22 is based on the position information of the puncture needle 25 and the characteristic shape portion 31 received from the signal processing unit 21 and the shape information of the puncture needle 25 and the characteristic shape portion 31 received from the database 16 via the CPU 17. Needle information such as the needle tip position of the puncture needle 25, the estimated cauterization region at the center of the needle tip of the puncture needle 25, the estimated position of the needle tip when the needle tip of the puncture needle 25 cannot be detected, the course direction of the puncture needle 25, etc. It has a function to give the display section 14 image information such as a symbol, a figure, and a sentence for displaying the obtained needle information and the obtained needle information.

  And the display part 14 is comprised so that the image signal for displaying the needle | hook information received from the needle | hook information calculating part 22 can be given to the monitor 5 and displayed. Accordingly, the needle information can be displayed in a superimposed manner together with the B mode image signal and the Doppler image signal acquired from the B mode processing unit 12 and the color mode processing unit 13. In this case, the needle information can be highlighted on the B-mode image (tomographic image) as necessary.

  Here, the necessity of the function which calculates | requires the above needle | hook information is demonstrated.

  FIG. 5 is a schematic diagram showing an example in which needle information indicating the position of the puncture needle 25 is superimposed and displayed on the diagnostic image by the ultrasonic diagnostic apparatus 1 shown in FIG.

  FIG. 5 shows an example in which the puncture needle 25 is provided with a flow path 30 in one direction and the inner diameter of the flow path 30 is partially reduced.

  As shown in FIG. 5, there are cases where the puncture needle 25 cannot be confirmed as an image because microbubbles exist in the vicinity of the diagnostic site P0 of the subject P. For example, when a puncture needle 25 is punctured to treat a liver tumor, the liver tumor may be stained with a contrast agent for the purpose of clarifying the boundary of the liver tumor. In such a case, if a contrast medium is also encapsulated inside the puncture needle 25, it becomes difficult to distinguish the surrounding stained liver tumor from the puncture needle 25.

  However, since the shape of the flow path 30 and the characteristic shape portion 31 inside the puncture needle 25 is stored in the database 16 and is already known, the shape of the puncture needle 25 can be accurately grasped based on the characteristic shape portion 31. it can. That is, as shown in FIG. 5, even when the needle tip of the puncture needle 25 cannot be confirmed with the gas being cauterized, the needle tip position of the puncture needle 25 is compensated by complementing the shape information of the puncture needle 25. If the reference is marked by the symbol 40, the user can easily grasp the needle tip position of the puncture needle 25.

  Similarly, even if the tip of the puncture needle 25 is out of the cross section of the target subject P, the tip of the puncture needle 25 is complemented by the shape information of the puncture needle 25. It is possible to display a guide for the position.

  Furthermore, if the needle information automatically detected by the needle information calculation unit 22 is used, various images can be displayed. For example, the puncture needle 25 can be highlighted. Further, even if the luminance of the ultrasonic image is partially lost, it is possible to display it complemented from the shape information of the puncture needle 25. Furthermore, it is possible to extrapolate the course direction of the puncture needle 25 from the position information of the puncture needle 25 and display the course direction of the puncture needle 25 as a line.

  Next, the operation and action of the ultrasonic guided puncture system formed by the ultrasonic diagnostic apparatus 1 and the puncture needle 25 will be described.

  FIG. 6 is a flowchart showing an example of a flow when the puncture needle 25 is inserted toward the diagnostic region P0 of the subject P under the ultrasonic guide by the ultrasonic diagnostic apparatus 1 shown in FIG. Reference numerals with numerals indicate the steps of the flowchart.

  First, in step S1, a contrast agent containing, for example, microbubbles is injected as the fluid X into the flow path 30 of the puncture needle 25 by the fluid injection device 26. At this time, it is controlled by the fluid injection device 26 so that the injection speed of the contrast agent becomes a required speed. As a result, the contrast medium is perfused through the flow path 30 of the puncture needle 25. Further, the speed parameter of the wall filter 23 is set in advance according to the injection speed of the contrast agent as required.

  Next, in step S2, ultrasonic waves are transmitted to the subject P. That is, the ultrasonic transmission unit 10 generates a transmission pulse and applies the transmission pulse to the ultrasonic probe 3, and the ultrasonic probe 3 converts the transmission pulse received from the ultrasonic transmission unit 10 into an ultrasonic pulse and converts it into the subject P. Transmit to the diagnostic site P0. Then, the ultrasonic probe 3 receives the reflected signal generated at the diagnostic site P0 of the subject P and gives it to the ultrasonic receiving unit 11 as a received signal.

  Next, in step S <b> 3, the B-mode processing unit 12 acquires a reception signal from the ultrasonic wave reception unit 11 and generates a B-mode image signal. Further, the color mode processing unit 13 acquires a reception signal as a Doppler signal from the ultrasonic wave reception unit 11 and generates a Doppler image signal by the Doppler method. The B-mode image signal and the Doppler image signal are given to the display unit 14 and synthesized. In addition, the cine memory 15 is used as a memory for a B-mode image signal or a Doppler image signal as appropriate.

  Then, a B-mode image and a Doppler image are displayed on the monitor 5. At this time, since the contrast agent is injected into the puncture needle 25, the position and schematic shape of the puncture needle 25 are visualized as a B-mode image or a Doppler image. In particular, when the speed parameter of the wall filter 23 is set in accordance with the injection speed of the contrast medium, the Doppler signal from the contrast medium flowing inside the puncture needle 25 is appropriately extracted. For this reason, the puncture needle 25 can be visualized more clearly as a Doppler image.

  FIG. 7 is a diagram showing an example in which the puncture needle 25 is visualized as a B-mode image by the ultrasonic diagnostic apparatus 1 shown in FIG.

  As shown in FIG. 7, the puncture needle 25 can be visualized by generating a B-mode image using an ultrasonic reflection signal from the contrast medium flowing inside the puncture needle 25.

  However, when a contrast medium is injected in the vicinity of the diagnostic site P0, it may be difficult to visually recognize the puncture needle 25. In such a case, an instruction to display needle information is input by operating the input device 9. Then, the signal detection unit 20, the signal processing unit 21, and the needle information calculation unit 22 are controlled by the CPU 17.

  First, in step S4 of FIG. 6, the signal detection unit 20 acquires an image signal such as a B-mode image signal or a Doppler image signal from the display unit 14, and the contrast agent injected into the puncture needle 25 by means such as threshold processing. The image signal from is detected. Then, the signal detection unit 20 gives an image signal from the puncture needle 25 to the signal processing unit 21.

  Next, in step S <b> 5, the signal processing unit 21 automatically detects the position of the characteristic shape portion 31 formed in the flow path 30 of the puncture needle 25 from the image signal from the puncture needle 25 received from the signal detection unit 20. . Then, the signal processing unit 21 gives the positions of the puncture needle 25 and the characteristic shape portion 31 to the needle information calculation unit 22 as position information.

  Next, in step S <b> 6, the needle information calculation unit 22 acquires position information of the puncture needle 25 and the characteristic shape part 31 from the signal processing unit 21. On the other hand, the needle information calculation unit 22 acquires shape information of the puncture needle 25 and the characteristic shape portion 31 from the CPU 17. Then, the needle information calculation unit 22 geometrically determines the position of the needle tip of the puncture needle 25 from the position information and shape information of the puncture needle 25 and the characteristic shape portion 31, the estimated cauterization region at the needle tip center of the puncture needle 25, and the puncture Needle information such as the estimated position of the needle tip when the needle tip of the needle 25 cannot be detected and the course direction of the puncture needle 25 is obtained. Furthermore, the needle information calculation unit 22 creates image information such as symbols, figures, and sentences for displaying the obtained needle information and supplies the image information to the display unit 14.

  Next, in step S7, the display unit 14 provides the monitor 5 with an image signal for displaying the needle information in addition to the B-mode image signal and the Doppler image signal. As a result, needle information such as the needle tip position of the puncture needle 25 is displayed on the monitor 5 so as to be visible. For this reason, even if the needle tip position of the puncture needle 25 cannot be visually recognized by the contrast agent in the vicinity of the diagnosis site P0, the user can obtain a guide for the needle tip position of the puncture needle 25 from the supplemented needle information.

  The ultrasonic diagnostic apparatus 1 and the puncture needle 25 described above image the puncture needle 25 with high sensitivity by perfusing the fluid X in the puncture needle 25 instead of the puncture needle 25 itself. For this reason, the visibility of the needle tip of the puncture needle 25 can be improved easily.

  Conventionally, a technique for confirming the needle tip of the puncture needle by moving the puncture needle itself has often been employed. On the other hand, when the ultrasonic diagnostic apparatus 1 and the puncture needle 25 shown in FIGS. 1 and 2 are used, even if the puncture needle 25 is stationary, the fluid X perfused in the puncture needle 25 is used for visualization. Therefore, in particular, the detection sensitivity of the puncture needle 25 that has stopped can be improved.

Further, when the target tumor is imaged by contrast echo method, if the Doppler image of the puncture needle 25 is generated using the bubbles inside the puncture needle 25, the puncture needle 25 is displayed in a discriminative manner from other contrast sites. Furthermore, even when the tip of the puncture needle 25 is out of the diagnostic section or when it is difficult to visually recognize the tip of the puncture needle 25 during cauterization, the puncture needle 25 and features that are already known Needle information such as the needle tip position can be obtained from the shape information of the shape part 31 by a process such as complementation. Then, by displaying the obtained needle information, the user can easily grasp the position of the puncture needle 25.

  The technique for imaging the puncture needle 25 by perfusing the fluid X in the puncture needle 25 described above can also be applied to the three-dimensional ultrasonic diagnostic apparatus 1.

  FIG. 8 shows a scanning surface 60 in the case where the puncture needle 25 is inserted toward the diagnostic site P0 under the ultrasonic guide using the two-dimensional array probe or the mechanical 4D probe as the ultrasonic probe 3 shown in FIG. It is a schematic diagram.

  As shown in FIG. 8, in the three-dimensional ultrasonic diagnostic apparatus 1, three-dimensional scanning is performed using a two-dimensional array probe or a mechanical 4D probe as the ultrasonic probe 3. That is, ultrasonic echo data is collected by moving the scanning surface 60 in two axial directions. The mechanical 4D probe is an ultrasonic probe 3 configured such that the one-dimensional array probe is mechanically swung.

  In the three-dimensional ultrasonic diagnostic apparatus 1, ultrasonic volume image data indicating three-dimensional spatial information is generated from the collected ultrasonic echo data in the B mode processing unit 12 and the color mode processing unit 13. The generated ultrasonic volume image data is output from the display unit 14 to the monitor 5 and displayed.

  At this time, the signal detection unit 20 acquires ultrasonic volume image data from the display unit 14 as an image signal such as a B-mode image signal or a Doppler image signal, and data from the fluid X flowing through the puncture needle 25 is an ultrasonic volume. Detected from within image data. Data from the detected fluid X is displayed on the monitor 5 as an ultrasonic volume image indicating the three-dimensional spatial information of the puncture needle 25. Also, an ultrasonic volume image that is a three-dimensional image of the puncture needle 25 can be displayed on the monitor 5 as an MPR (multi-planar reconstruction) image.

  FIG. 9 is a diagram showing an example in which the MPR image obtained by the three-dimensional scanning shown in FIG.

  As shown in FIG. 9, an ultrasonic image of the diagnostic site P0 including the image of the puncture needle 25 can be displayed on the monitor 5 as an MPR image. In the example needle information calculation unit 22, needle position information of the puncture needle 25 is detected as three-dimensional information. Then, for example, one axis 70a of the MPR image that is three-dimensional information coincides with the insertion direction of the puncture needle 25.

  In the example of FIG. 9, the axis 70a indicating the insertion direction of the puncture needle 25 and the axis 70b orthogonal to the axis 70a are superimposed on the upper left screen together with the diagnostic region P0. For this reason, the depth position of the puncture needle 25 can be confirmed. In addition, an orthogonal plane obtained by rotating the upper left screen by 90 degrees about the insertion direction of the puncture needle 25 is displayed on the upper right screen. Furthermore, a plane orthogonal to the insertion direction of the puncture needle 25 is displayed on the lower left screen. For this reason, two axes 70b and 70c orthogonal to each other are displayed on the lower left screen.

  Thus, in the three-dimensional ultrasonic diagnostic apparatus 1, position information of the puncture needle 25 can be obtained as three-dimensional information.

The block diagram which shows embodiment of the ultrasonic diagnosing device and puncture needle which concern on this invention. Sectional drawing which shows the structural example of the puncture needle shown in FIG. The schematic diagram which shows an example of the image which was produced | generated by the ultrasound diagnosing device shown in FIG. 1, and the puncture needle was visualized. The schematic diagram of the ultrasonic image which displayed the insertion angle of the puncture needle shown in FIG. The schematic diagram which shows the example which displayed the needle | hook information which shows the position of the puncture needle on the diagnostic image by the ultrasonic diagnostic apparatus shown in FIG. The flowchart which shows an example of the flow at the time of inserting the puncture needle toward the diagnostic site | part of a subject under the ultrasonic guide by the ultrasonic diagnostic apparatus shown in FIG. The figure which shows the example which imaged the puncture needle as a B-mode image by the ultrasonic diagnostic apparatus shown in FIG. The schematic diagram which shows the scanning surface in the case of inserting a puncture needle toward a diagnostic region under an ultrasonic guide using a two-dimensional array probe or a mechanical 4D probe as the ultrasonic probe shown in FIG. The figure which shows the example which displayed the MPR image obtained by the three-dimensional scanning shown in FIG.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus 2 Apparatus main body 3 Ultrasonic probe 4 Console 5 Monitor 6 Operation panel 7 Keyboard 8 Trackball 9 Input device 10 Ultrasonic transmission part 11 Ultrasonic reception part 12 B mode processing part 13 Color mode processing part 14 Display part 15 Cine memory 16 Database 17 CPU
18 Speed parameter setting unit 19 Puncture needle information processing system 20 Signal detection unit 21 Signal processing unit 22 Needle information calculation unit 23 wall filter
24 Guide mechanism 25 Puncture needle 26 Fluid injection device 30 Flow path 31 Characteristic shape portion 40 Symbol 50 Puncture line 60 Scan planes 70a, 70b, 70c Axis P Subject P0 Diagnostic portion X Fluid

Claims (12)

An ultrasonic probe for transmitting an ultrasonic wave in a state where a puncture needle into which a fluid containing a strong reflector is injected is punctured in a subject and receiving an ultrasonic reflection signal;
A data processing unit that generates an image signal capable of visually recognizing the fluid inside the puncture needle from the ultrasonic reflection signal received by the ultrasonic probe;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to claim 1, wherein the data processing unit includes a B-mode processing unit that generates a B-mode image in which the fluid can be visually recognized from the ultrasonic reflection signal. The ultrasonic diagnostic apparatus according to claim 1, wherein the data processing unit includes a color mode processing unit that generates a Doppler image in which the fluid can be visually recognized from the ultrasonic reflection signal received as a Doppler signal. . The data processing unit uses the fluid velocity to generate a Doppler image in which the fluid can be visually recognized by discriminating from other parts in the subject from the ultrasonic reflection signal received as a Doppler signal. The ultrasonic diagnostic apparatus according to claim 1, further comprising a color mode processing unit. The data processing unit includes a color mode processing unit that generates a Doppler image in which the fluid can be visually recognized from the ultrasonic reflection signal received as a Doppler signal,
The ultrasonic diagnostic apparatus according to claim 1, further comprising a speed parameter setting unit configured to set a speed parameter of a filter included in the color mode processing unit according to a speed of the fluid. An ultrasonic probe for transmitting an ultrasonic wave in a state where a puncture needle into which a fluid containing a strong reflector is injected is punctured in a subject and receiving an ultrasonic reflection signal;
A signal detection unit for detecting a fluid signal received from the fluid inside the puncture needle among the ultrasound reflected signals received by the ultrasound probe;
An ultrasonic diagnostic apparatus comprising: Inside the puncture needle, there is provided a characteristic shape portion where the shape of the flow path of the fluid is different from the shape of the flow path in other portions,
A signal processing unit for detecting the position of the characteristic shape portion from the fluid signal detected by the signal detection unit;
Based on the position of the characteristic shape portion detected by the signal processing unit and the shape information of the puncture needle, a needle information calculation unit that obtains needle information that is information related to the puncture needle;
A display unit for displaying the needle information created by the needle information calculation unit on a monitor;
The ultrasonic diagnostic apparatus according to claim 6, further comprising: The needle information calculation unit is configured to obtain at least one of a needle tip position of the puncture needle, an estimated cauterization region at the center of the needle tip, and a course direction as needle information. Ultrasonic diagnostic equipment. The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic diagnostic apparatus is configured to acquire a signal indicating three-dimensional spatial information of the puncture needle from the fluid. A puncture needle used for ultrasonic diagnosis, characterized in that a flow path for injecting a fluid containing a strong reflector is formed inside. The puncture needle used for ultrasonic diagnosis according to claim 10, wherein a characteristic shape portion having a shape of the flow path different from that of the flow path in another portion is provided. Computer
A fluid containing a strong reflector in the inside of a puncture needle in which a fluid channel is formed, and the shape of the fluid channel is different from the shape of the channel in other parts. A signal detection unit for detecting a fluid signal received from the fluid inside the puncture needle among ultrasonic reflected signals received by the ultrasound probe in a state where the fluid is injected and further punctured into the subject;
Based on the signal processing unit that detects the position of the characteristic shape portion from the fluid signal detected by the signal detection unit, and the position information of the characteristic shape portion detected by the signal processing unit and the shape information of the puncture needle A needle information calculation unit for obtaining needle information which is information on the puncture needle,
Needle information processing program characterized by functioning as

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