CN105640589A - Ultrasound diagnosis apparatus - Google Patents

Abstract

According to one embodiment, an ultrasound diagnosis apparatus includes a transmitter, a receiver, a needle tip position acquisition unit, a ROI setting unit, an image generator, and a display controller. The transmitter transmits ultrasound beams to a subject into which a puncture needle is inserted while scanning the subject. The receiver receives signals reflected from the subject. The needle tip position acquisition unit successively acquires the position of the needle tip of the puncture needle. The ROI setting unit sets a region of interest at least in a direction in which the puncture needle is inserted. The image generator generates an image of the region of interest according to the position of the needle tip based on the signals. The display controller displays the image of the region of interest.

Description

Diagnostic ultrasound equipment

The application based on Japanese patent application 2014-240791 (applying date: 11/28/2014) and Japanese patent application 2015-192326 (applying date: 09/29/2015) enjoys its right of priority based on this application. The application comprises whole contents of above-mentioned application by referring to this application.

Technical field

Embodiments of the present invention relate to diagnostic ultrasound equipment.

Background technology

Diagnostic ultrasound equipment such as has: transmission portion, while sending ultrasound beamformer from ultrasonic probe along depth direction to the subject being punctured puncture needle, by the direction carrying out sending constantly successively switching (scanning) be the direction (width) orthogonal with this direction; Reception portion, the reflected wave conversion received by ultrasonic probe becomes electrical signal, and by postponing to obtain beam signal to electrical signal application time; Image production part, obtain along the figure image signal (representing the signal of the intensity of reflection wave) on the sweep trace of depth direction based on beam signal, by the image signal storage of each point (pixel) on sweep trace is formed faultage image to the position suitable with the position of sweep trace in the frame memory as faultage image storage portion; And indicating meter (display portion), display faultage image.

Here, sometimes width is called " X-direction ", depth direction is called " Y-direction ", by the direction orthogonal with width and depth direction and front and back to being called " Z-direction ". Further, sometimes faultage image is called " B-mode image ", the process obtaining faultage image by diagnostic ultrasound equipment is called " B-mode shooting ". Wherein, depth direction also comprises the direction carrying out radiating with fan-shaped. In order to make ultrasound beamformer radiate with fan-shaped, by arranging time of lag and successively drive vibrator realizes.

The faultage image obtained by diagnostic ultrasound equipment is not only used to diagnostic imaging, such as, be also used as in the radio frequency ablation therapy (Radiofrequencyablation:RFA) of the topical therapeutic method of hepatocellular carcinoma, the examination of living tissue of inspection liver cell tissue etc.In these treatment, checking, it is necessary to use the puncture needle being arranged on ultrasonic probe, tumour etc. is paid close attention to position and accurately punctures.

Therefore, utilization Real Time Observation can have the region-of-interest (regionofinterest:ROI) of constant length and the diagnostic ultrasound equipment of puncture needle at the two-dimensional directional of width (X-direction) and depth direction (Y-direction). The size of region-of-interest is configured to show puncture needle on the faultage image in region-of-interest. Consequently, it is possible to grasp where puncture needle is inserted in subject clearly. Sometimes puncture needle will be observed while the way carrying out puncturing is called " paracentesis under ultrasonic wave (echo) guiding ".

But, in the paracentesis under ultrasonic wave (echo) guides, if the needle point of puncture needle departs from from the faultage image region-of-interest, then needle point will not be displayed on faultage image. Now, if the end mistake being shown in the puncture needle of faultage image is thought by the people performed an operation, and needle point needle point then thrust dark sometimes. In this situation, if there is blood vessel in the front that needle point is advanced, then likely injure blood vessel.

In order to anti-hemostatic tube is injured by needle point, receive the beam signal from reception portion, only the frequency of ultrasound beamformer to be there occurs, the part of Doppler shift carries out detection by carrying out quadrature phase detector for beam signal, and the blood flow signal (representing the signal of flow velocity, variance and power) obtaining on sweep trace is exported based on this detection, by being stored into the blood flow signal of each point (pixel) on sweep trace as the position suitable with the position of sweep trace in the frame memory in blood-stream image storage portion, form blood-stream image. Wherein, sometimes blood-stream image is called " doppler image ", the process obtaining doppler image by diagnostic ultrasound equipment is called " doppler mode shooting ". In addition, here, by based on puncture needle needle point towards direction insert to subject time the insertion route of puncture needle of anticipation or the direction that moves ahead based on needle point and the insertion route of puncture needle envisioned is called " guiding puncture circuit ". That is, guiding puncture circuit successively changes according to these directions.

According to the mode of the entirety of storage guiding puncture circuit, the size of the region-of-interest (ROI) of setting blood-stream image. Propose a kind of blood-stream image making to be taken by doppler mode and obtain and it is overlapped in the next technology (motion technology) carrying out showing with the amount of images (frame rate or body speed are representatively called " frame rate " below) generated by the unit time of the faultage image taken by B-mode and obtain. Thus, no matter there is needle point in which position on guiding puncture circuit, can both rest in whether the front that needle point advances just is having blood vessel to pass through.

But, in above-mentioned motion technology, successively performing by each sweep trace in this characteristic of transmitting-receiving of ultrasound beamformer, needing certain time to obtain the beam signal needed for the generation of blood-stream image. Such as, in order to the blood-stream image obtained in region-of-interest, when when the ultrasound beamformer of width transmitting-receiving regulation radical, region-of-interest needs the time more long along what depth direction and/or width more long (region-of-interest is more big) then now spent, and the generating rate as the inverse needing the time reduces. That is, the region-of-interest (ROI) of blood-stream image is more big, then the higher limit of the generating rate that can realize more reduces, if generating blood-stream image with the higher limit (low frame rate) reduced, then sometimes cannot show blood-stream image in real time.

In order to prevent the reduction of frame rate, can according to tip position after puncture needle insertion starts, the position of the region-of-interest (ROI) of blood-stream image is manually again set at any time by the people performed an operation, but now need to interrupt puncture operation every time, existing not only to become makes operation cure the factor spun out, and can increase the weight of this problem of burden of the people performed an operation.

Summary of the invention

Present embodiment is used for solving the above problems, its object is to, there is provided in a kind of paracentesis under ultrasonic wave (echo) guides and can maintain high frame rate and show blood-stream image or volume image in real time, and eliminate and make operation cure the factor spun out, the people performed an operation is not caused the diagnostic ultrasound equipment of burden.

The diagnostic ultrasound equipment of enforcement mode has: transmission portion, reception portion, tip position obtaining section, region-of-interest configuration part, region-of-interest image production part and display control unit. Transmission portion is while send ultrasound beamformer to the subject of the puncture needle that punctured while scanning. Reception portion receives the signal from subject reflection. Tip position obtaining section successively obtains the tip position of puncture needle. Region-of-interest configuration part at least sets the region-of-interest thrusting on direction of tip position. The tip position that region-of-interest image generation unit is successively obtained by tip position obtaining section, generates the region-of-interest image in region-of-interest based on the signal received. The region-of-interest image generated by region-of-interest image production part is shown by display control unit.

Diagnostic ultrasound equipment according to above-mentioned formation, in paracentesis under ultrasonic wave (echo) guides, it is possible to maintain high frame rate, display blood-stream image or volume image in real time, and eliminate and make operation cure the factor spun out, the people performed an operation is not caused burden.

Accompanying drawing explanation

Fig. 1 is the formation block diagram of the diagnostic ultrasound equipment that the first enforcement mode relates to.

Fig. 2 is the figure of the mutual position relation representing the region-of-interest of ultrasonic wave image, the region-of-interest of blood-stream image and puncture needle.

Fig. 3 is the figure representing speed relation table.

Fig. 4 is the figure representing mobile amount relation table.

Fig. 5 A is the ultrasonic wave image of the three-dimensional in section A.

Fig. 5 B is the ultrasonic wave image of the three-dimensional in section B.

Fig. 5 C is the ultrasonic wave image of the three-dimensional in section C.

Fig. 5 D is the figure of the mutual position relation representing section A, section B and section C.

Fig. 6 is the figure of the mutual position relation representing the region-of-interest of blood-stream image, section A, section B and section C.

Fig. 7 is the time figure representing the action from each portion till the display moving to cross-section image of puncture needle.

Fig. 8 represents in the diagnostic ultrasound equipment that the 2nd enforcement mode relates to, from the time of the action in each portion till the display moving to cross-section image of puncture needle figure.

Fig. 9 A is the ultrasonic wave image of the three-dimensional in section A.

Fig. 9 B is the ultrasonic wave image of the three-dimensional in section B.

Fig. 9 C is the ultrasonic wave image of the three-dimensional in section C.

Fig. 9 D is the figure of the mutual position relation representing section A, section B and section C.

Figure 10 is the formation block diagram of the diagnostic ultrasound equipment that the 3rd enforcement mode relates to.

Figure 11 represents in the diagnostic ultrasound equipment that the 3rd enforcement mode relates to, from the time of the action in each portion till the display moving to cross-section image of puncture needle figure.

Embodiment

In above-mentioned motion technology, in order in the paracentesis under ultrasonic wave (echo) guiding, which position no matter needle point is positioned on guiding puncture circuit, whether the front all resting in needle point traveling is just having blood vessel to pass through, according to the mode of the entirety of storage guiding puncture circuit, set the size of the region-of-interest (ROI) of blood-stream image.Therefore, having to increase region-of-interest, result, can not maintain high frame rate.

On the other hand, in the present embodiment, the position of the region-of-interest of blood-stream image is set according to tip position. Accordingly, it may be possible to the region-of-interest making blood-stream image becomes the size of the necessary inferior limit in the region being defined in tip position and its periphery.

According to above-mentioned formation, owing to making region-of-interest become the size of necessary inferior limit, so generating blood-stream image with high frame rate, thus, blood-stream image can be shown in real time. Further, owing to according to tip position contraposition region-of-interest automatically, making operation cure the factor spun out so can eliminate, the people performed an operation is not caused burden. , owing to the position of region-of-interest is corresponding to tip position, even if so needle point is not shown in ultrasonic wave image, it is also possible to the position based on region-of-interest judges tip position, thus, further the position relation of the blood vessel in needle point and region-of-interest becomes clear. As a result, such as whether the known front advanced at needle point is just having blood vessel to pass through.

Wherein, as ultrasonic wave image, it is possible to be any image of the three-dimensional of X, the two dimension of Y-direction or X, Y, Z-direction, and, the blood-stream image of display overlapping with this ultrasonic wave image can also be two dimension or three-dimensional any image.

In the following embodiments, the formation that the ultrasonic wave image making three-dimensional blood-stream image be overlapped in three-dimensional shows is described.

< first implements mode >

With reference to Fig. 1, the diagnostic ultrasound equipment of the first enforcement mode is described. Fig. 1 is the formation block diagram of diagnostic ultrasound equipment. As shown in Figure 1, diagnostic ultrasound equipment has: calculating part 112, region-of-interest configuration part 113, the transmitting-receiving control portions 114 such as ultrasonic probe 101, reception portion 102, transmission portion 103, ultrasonic wave image production part 104A, blood-stream image generating unit 106A, cross-section image generating unit 108A, display portion 110, tip position obtaining section 111, mobile amount.

Ultrasonic wave image production part 104A has B-mode image process portion 104 and B-mode image storage portion 105. Blood-stream image generating unit 106A is equivalent to an example of the region-of-interest image production part in technical scheme. Blood-stream image generating unit 106A generates the blood-stream image of the blood flow information paying close attention to region as region-of-interest image. Blood-stream image generating unit 106A has doppler image process portion 106 and doppler image storage portion 107. Cross-section image generating unit 108A has the configuration parts 117 such as cross-section image process portion 108, cross-section image storage portion 109, guiding puncture circuit generating unit 115, guiding puncture line memory portion 116 and cross section place.

(ultrasonic probe 101, reception portion 102, transmission portion 103)

Ultrasonic probe 101 has the multiple oscillators being two-dimensionally arranged of the conversion (electroacoustics conversion) carrying out electrical signal and ultrasonic acoustic signal. Transmission portion 103 is while send ultrasound beamformer from oscillator along depth direction to the subject of the puncture needle NL that punctured, while sending direction successively being switched to the direction (width) (scanning of width) orthogonal with this direction, further (Z-direction) carries out the scanning (front and back to scanning) of width, along the longitudinal direction. If ultrasound beamformer arrives the reflection sources in subject, reflect, again return each oscillator.

The reflected wave conversion that reception portion 102 receives by oscillator becomes electrical signal, by postponing to obtain the beam signal suitable with the sweep trace along depth direction to electrical signal application time.

(transmitting-receiving control portion 114)

Transmitting-receiving control portion 114 is according to carrying out B-mode shooting and the mode of doppler mode shooting in timesharing mode, such as according to whenever carry out specifying repeatedly (such as, 4 times) doppler mode shooting just carries out the mode of 1 B-mode shooting, transmission portion 103 and reception portion 102 controlled.

Transmitting-receiving control portion 114 accepts the region-of-interest ROI2 and frame rate R2 of ultrasonic wave image in B-mode is taken, obtain transmission condition (time of lag, transmission times) and receiving conditions (receiving channel, each channel latency amount), by being controlled in transmission portion 103 and reception portion 102 with these conditions, repeat to have the scanning of 1 static image volume of the sweep trace of the radical needed for ultrasonic wave image surface of the three-dimensional in order to describe in region-of-interest ROI2 with frame rate R2.

Transmitting-receiving control portion 114 accepts the region-of-interest ROI1 of blood-stream image in doppler mode is taken, ROI1 ' and frame rate R1, obtain transmission condition (time of lag, transmission times) and receiving conditions (reception channel, each channel latency amount), by transmission portion 103 and reception portion 102 being controlled with these conditions, thus every bar sweep trace carry out specifying repeatedly (such as, 4 times) the transmission of ultrasound beamformer and the reception of reflection wave, repeat with frame rate R1 to have to describe region-of-interest ROI1, the scanning of 1 static image volume of the sweep trace of the radical needed for the blood-stream image of the three-dimensional in ROI1 '. blood-stream image is equivalent to an example of the region-of-interest image in technical scheme.

Fig. 2 be represent region-of-interest ROI1, ROI1 of blood-stream image ', the figure of the mutual position relation of the region-of-interest ROI2 and puncture needle NL of ultrasonic wave image. As described later, owing to obtaining the tip position of puncture needle by the unit time (such as 0.05 second), and successively pay close attention to region in the position corresponding with the tip position obtained, so in common paracentesis, the region-of-interest successively represented is overlapped, if but this is illustrated, then owing to being difficult to see each region-of-interest, so in fig. 2, by successively represent in the position corresponding with tip position 2 region-of-interests ROI1, ROI1 ' be shown in the position being separated from each other. As shown in Figure 2, the main body of ultrasonic probe 101 be provided with have pass through for puncture needle NL and to the guide in the insertion hole that it guides.

(tip position obtaining section 111)

Tip position obtaining section 111 successively obtains the tip position of puncture needle NL. As shown in Figure 1 and Figure 2, tip position obtaining section 111 has: be installed in guide, the mobile quantity sensor (roller rotated by the movement according to puncture needle and the encoder of the rotation amount of measuring roll are formed) of mobile amount when detection puncture needle NL moves along guiding puncture circuit; Sensor is passed through with the reference point that be have passed on guiding puncture circuit by needle point NT detects, this tip position obtaining section 111 is configured to the mobile amount according to lighting from benchmark and obtains insertion, and obtains the position of needle point on coordinate according to the insertion lighted from benchmark on guiding puncture circuit. In addition, being not limited thereto, tip position obtaining section 111 can also be configured to based on the ultrasonic wave image depicting puncture needle NL, and the brightness value of front end of reference puncture needle NL, the shape of puncture needle NL, the tip position of puncture needle NL is obtained by the unit time. The coordinate conversion of the needle point obtained is become the coordinate of three-dimensional ultrasonic wave image (image generated by B-mode image process portion 104 described later) by tip position obtaining section 111.

(mobile amount waits calculating part 112)

Mobile amount calculating part 112 such as grade based on obtain by the per unit time and by the position P1 of the needle point NT after coordinate conversion on three-dimensional coordinate, P2, P3, P4 ... come mobile amount L1=| P2-P1 | of the tip position of Units of Account time, L2=| P3-P2 |, L3=| P4-P3 | ..., the translational speed V1=(L2-L1) of unit time, V2=(L3-L2), V3=(L4-L3), further, calculate direction D1=(P2-P1) that needle point moves ahead, D2=(P3-P2), D3=(P4-P3) ... The mobile amount L and translational speed V of the tip position of the per unit time calculated is equivalent to speed and the acceleration of needle point NT.

Wherein, the mobile amount L and translational speed V of the tip position of per unit time can obtain based on the mobile amount L of the puncture needle NL by reference point that the per unit time is detected by the mobile quantity sensor (above-mentioned) of tip position obtaining section 111. The mobile amount L and translational speed V of the tip position of per unit time can obtain according to the increase and decrease of the angle of rotation (rotation amount) of the roller by unit time survey and angle of rotation (rotation amount).

The mobile amount L etc. of the tip position according to the per unit time set region-of-interest ROI1, ROI1 of blood-stream image ' size (aftermentioned detailed content). Consequently, it is desirable to need the time (inverse of the frame rate R1 of blood-stream image) below when unit time when making the detection amount of movement L etc. is generate blood-stream image. The higher limit of frame rate R1 is 20fps (aftermentioned). Now, unit time during detection mobile amount L etc. was 0.05 (=1/20) second.

(region-of-interest configuration part 113)

Next, the setting of region-of-interest ROI2 and frame rate R2 about ultrasonic wave image is described. Region-of-interest configuration part 113 at least sets the region-of-interest thrust on direction of tip position. The input of the operating portion (not shown) of accepted user before the paracentesis of region-of-interest configuration part 113 under ultrasonic wave (echo) guides, transmission portion 103 is set the region-of-interest ROI2 of the ultrasonic wave image about three-dimensional, and transmission portion 103 is set frame rate R2.

The region-of-interest ROI2 of ultrasonic wave image and frame rate R2 is exported to transmitting-receiving control portion 114 by region-of-interest configuration part 113 in art. In addition, the position of the region-of-interest ROI2 of ultrasonic wave image, size and frame rate R2 are constant, do not change according to mobile amount L (being equivalent to speed) of tip position and/or the translational speed V (being equivalent to acceleration) of the tip position of per unit time of per unit time. Wherein, the input of the operating portion (not shown) of region-of-interest configuration part 113 accepted user, changes frame rate R2.

Next, it is described for about region-of-interest ROI1, ROI1 ' of blood-stream image and the setting of frame rate R1.

Region-of-interest configuration part 113 perform the operation start time, by region-of-interest ROI1, ROI1 ' the initial value (depth index d3 described later) of size and the initial value (such as 14fps described later) of frame rate R1 corresponding with it export transmitting-receiving control portion 114 to.

As shown in Figure 2, if by region-of-interest ROI1, ROI1 of blood-stream image ' size S be set to depth direction, width and front and back to all directions on length d, w, u long-pending, then the size S of region-of-interest ROI1, ROI1 ' is represented by following formula (1).

S=d*w*u (1)

Blood-stream image region-of-interest ROI1, ROI1 ' in, length d, w, u increase and decrease with identical multiplying power.It is not limited to this, it is also possible to the length d of depth direction is set to the mobile of the tip position with the per unit time and measures the corresponding length such as L, it is not set as length w, u measuring the corresponding length such as L and make it constant with mobile.

Region-of-interest configuration part 113 is previously stored with the mobile amount relation table (with reference to Fig. 4) of the corresponding relation representing speed index and/or acceleration index and depth index d0��d5 and represents the speed relation table (with reference to Fig. 3) of the relation of depth index and frame rate R1, in art, by the unit time obtaining tip position by tip position obtaining section 111, obtain the region-of-interest ROI1 of the blood-stream image comprising tip position, the position of ROI1 ', based on the mobile amount L and translational speed V of needle point NT, with reference to mobile amount relation table and speed relation table, obtain as region-of-interest ROI1, the depth index of the size of ROI1 ', frame rate R1 is obtained according to depth index, and deliver to transmitting-receiving control portion 114. thus, set region-of-interest ROI1, ROI1 ' comprises tip position, and namely the upper edge (head in the region-of-interest of the blood-stream image of approximate taper of decaptitating) of region-of-interest ROI1, ROI1 ' becomes tip position (with reference to Fig. 2).

Fig. 3 is the figure of the example representing speed relation table. As with region-of-interest ROI1, ROI1 of blood-stream image ' depth direction on depth index d0��d5 corresponding to the size of value of length d (with reference to Fig. 2), be provided with 6 stages from small to large. Using this with as blood-stream image region-of-interest ROI1, ROI1 ' frame rate R1 corresponding to the depth index d0��d5 of size prestore as speed relation table.

In the speed relation table shown in Fig. 3, become big and make frame rate R1 [fps] from 20 to 10 stage become low corresponding to depth index is interim from d0 to d5. In order to show blood-stream image in real time, it is necessary to frame rate R1 is maintained high. Therefore, frame rate R1 is arranged lower value (being 10fps here). In addition, as the size of the region-of-interest of the blood-stream image corresponding with this lower value, the length d on the depth direction (Y-direction shown in Fig. 2) of the region-of-interest of blood-stream image is arranged higher limit (depth index d5) here. Such as, region-of-interest configuration part 113 makes the lower value of the frame rate R1 that preoperative user inputted by operating portion (not shown) and initial value (14fps) be stored in its storage inside device.

Fig. 4 is the figure of the example representing mobile amount relation table. In the diagram, as the speed index 0��3 corresponding with the size of the value of the mobile amount L of the tip position of per unit time, 4 stages it are provided with from small to large. In addition, as the acceleration index 0��3 corresponding with the size of the value of the translational speed V of the tip position of per unit time, it is provided with 4 stages from small to large.

Such as, in the mobile amount relation table shown in Fig. 4, when acceleration index is 0, if speed index is big by 0,1,2,3 changes, then corresponding with it, depth index is pressed d0, d1, d2, d3 and is become big. When speed index is 0, if acceleration index is big by 0,1,2,3 changes, then corresponding with it, depth index is pressed d0, d1, d2, d3 and is become big. That is, if mobile amount L (being equivalent to speed) of the tip position of per unit time or translational speed V (being equivalent to acceleration) become big, then length d as the depth direction of the size of region-of-interest RO1 is slowly elongated. In addition, such as speed index be 0, acceleration index be 0 time, when speed index is 1, acceleration index is 1, when speed index is 2, acceleration index is 2, when speed index is 3, acceleration index is 3, corresponding with these situations, depth index is pressed d0, d2, d4, d5 and is become big.Namely, if mobile amount L (being equivalent to speed) of the tip position of per unit time and translational speed V (being equivalent to acceleration) become big, then turning into ROI1 ' from region-of-interest ROI1, the length d as the depth direction of the size of region-of-interest is sharply elongated (with reference to Fig. 2). Wherein, when speed index be 3, acceleration index be 2 time, depth index is d5, even if but now make acceleration index increase to 3 from 2, depth index also keeps d5 constant. Like this, depth index is arranged higher limit d5. By depth index is arranged higher limit d5, it is possible to prevent frame rate R1 to be less than lower value 10fps.

Owing to if acceleration index becomes big, then depth index becomes big, thus makes region-of-interest ROI1 ' become big at depth direction, generates its blood-stream image, thus the people performed an operation can look into the distance from tip position along depth direction significantly away from scope. Thus, as shown in Figure 2, when in order to target compound TG is punctured and move rapidly needle point NT, even if than needle point NT towards the forward place of target compound TG there is blood vessel V N, also look into the distance the scope of blood vessel V N existence based on the blood-stream image in the region-of-interest ROI1 ' that depth direction becomes big, so there is no injure the anxiety of blood vessel V N.

In addition, can not also based on above-mentioned speed index and/or acceleration index, depth index is obtained with reference to mobile amount relation table, and the mobile amount L and/or translational speed V of the tip position based on the unit time, according to function f obtain region-of-interest ROI1, ROI1 of blood flow ' depth direction on length d. Length d, as the function f of the mobile amount L and/or translational speed V of the tip position of per unit time, is represented by following formula (2).

D=f (L, V) (2)

Wherein, also length d is arranged higher limit at this. Region-of-interest configuration part 113, in this action, when the length d obtained according to upper formula (2) such as exceedes the higher limit predetermined, exports higher limit. Thus, frame rate R1 can be prevented to be less than lower value.

Transmitting-receiving control portion 114 accepts the region-of-interest ROI2 of ultrasonic wave image and region-of-interest ROI1, ROI1 ' of frame rate R2 and blood-stream image and frame rate R1 thereof thereof, in order to carry out B-mode shooting and doppler mode shooting in a time division manner, such as according to whenever carry out specifying repeatedly (such as, 4 times) doppler mode shooting just carries out the mode of 1 B-mode shooting, transmission portion 103 and reception portion 102 controlled.

(B-mode image process portion 104, doppler image process portion 106)

The beam signal that B-mode image process portion 104 is obtained based on being taken by B-mode, generates three-dimensional ultrasonic wave image, and is stored in B-mode image storage portion 105. The beam signal that doppler image process portion 106 is obtained based on being taken by doppler mode, generates three-dimensional blood-stream image, and is stored in doppler image storage portion 107.

(guiding puncture circuit generating unit 115)

The direction DR that the mobile amount of the tip position that guiding puncture circuit generating unit 115 calculates by calculating parts 112 such as the reason amounts of movement and needle point NT move ahead, generate the guiding puncture circuit GL in three-dimensional ultrasonic wave image, and it is stored in guiding puncture line memory portion 116.

(configuration part 117, the cross-section image process portion 108 such as cross section place)

Fig. 5 A represents the ultrasonic wave image of the three-dimensional in section A, Fig. 5 B represents the ultrasonic wave image of the three-dimensional in section B, Fig. 5 C represents the ultrasonic wave image of the three-dimensional in section C, Fig. 5 D is the figure of the mutual position relation representing section A, section B and section C, Fig. 6 is the figure of the mutual position relation representing ultrasonic wave image, section A, section B and section C.Here, the section that the direction DR (being also the face orthogonal with guiding puncture circuit GL) that section C refers to puncture needle NL moves ahead is orthogonal. In addition, section A refer to orthogonal with section C and along the section of width (X-direction). Further, section B refers to the section orthogonal with section A and section C. Fig. 5 A illustrates region-of-interest ROI1, ROI1 corresponding with tip position '. In addition, Fig. 6 illustrates in the section orthogonal with the axle of puncture needle NL as from the section C of the tip position of puncture needle NL away from the section of predetermined distance.

The direction that the configuration parts such as cross section place 117 accept the position of the needle point NT obtained by the unit time on three-dimensional coordinate and the needle point NT that calculates by calculating parts 112 such as mobile amounts moves ahead, sets the position of the position of the section (section C) not showing cross-section image, its angle (being equivalent to the direction that needle point moves ahead), the quantity (being section A, section B, section C these 3) of section, each section here. Wherein, from tip position, to the position of section C, distance, by the operating portion (not shown) of user, such as, as the arbitrary distance in 0mm��20mm, is input to the configuration parts such as cross section place 117. Cross-section image process portion 108 accepts the position etc. of set each section, generates the cross-section image in section A, section B and section C, and is stored in cross-section image storage portion 109.

(display portion 110)

Display portion 110 has display control unit, and display control unit makes three-dimensional blood-stream image be overlapped in three-dimensional ultrasonic wave image, and, make the guiding puncture circuit GL of puncture needle NL be shown in indicating meter (not shown) (with reference to Fig. 2). Further, display portion 110 makes the cross-section image in indicating meter display section A, section B and section C (with reference to Fig. 5 D and Fig. 6).

(action)

Next, with reference to Fig. 5 A��Fig. 5 D and Fig. 7, the action at each position forming diagnostic ultrasound equipment is described.

When performing the operation beginning, tip position obtaining section 111 obtains the position of needle point NT on the coordinate of the ultrasonic wave image of three-dimensional, region-of-interest configuration part 113 set the region-of-interest ROI2 (constant) of ultrasonic wave image, frame rate R2 (constant), as blood-stream image region-of-interest ROI1, ROI1 ' the depth index (initial value: d3) of size and frame rate R1 (initial value: 14fps). Transmitting-receiving control portion 114 controls transmission portion 103 and reception portion 102 based on the condition comprising these information, B-mode image process portion 104 generates three-dimensional ultrasonic wave image based on acquired reception wave beam, and doppler image process portion 106 generates three-dimensional blood-stream image. Display control unit (not shown) makes three-dimensional blood-stream image be overlapped in three-dimensional ultrasonic wave image and be shown to indicating meter. Wherein, the mobile amount L etc. based on tip position is generated to the guiding puncture circuit of puncture needle NL here, and it is carried out display not speech and.

Fig. 7 is the time figure representing the action from each portion till the display moving to cross-section image of the puncture needle NL art. Wherein, in operation, based on the size (constant) of region-of-interest ROI2 and the ultrasonic wave image of its frame rate R2 (constant) generation three-dimensional of ultrasonic wave image, the ultrasonic wave image of generation is shown in indicating meter. When performing the operation beginning, based on the size (initial value) of region-of-interest ROI1 and the blood-stream image of frame rate R1 (initial value) generation three-dimensional of blood-stream image, the blood-stream image of generation is overlapping with ultrasonic wave image is shown in indicating meter.

Hereinafter, mainly the generation of blood-stream image and its display being overlapped in the three-dimensional that three-dimensional ultrasonic wave image shows is described.

(calculating of position, mobile amount etc.)

As shown in Figure 7, if moving puncture needle NL in operation, then tip position obtaining section 111 is based on mobile quantity sensor and by the detected result of sensor, obtains the position of needle point NT on three-dimensional coordinate by the unit time. Further, mobile amount waits calculating part 112 based on the position of the needle point NT obtained by the unit time on three-dimensional coordinate, and the mobile of tip position calculating the per unit time measures L and translational speed V.

(region-of-interest ROI1, ROI1 ' position, size setting)

Region-of-interest configuration part 113 is based on the position of needle point NT on three-dimensional coordinate and the mobile amount L and/or translational speed V of the tip position of per unit time that calculates, according to this speed index and acceleration index, with reference to the mobile amount relation table shown in Fig. 4, obtain position and the depth index of the region-of-interest of blood-stream image, and with reference to the speed relation table shown in Fig. 3, obtain the frame rate R1 corresponding with depth index, by region-of-interest ROI1, ROI1 of blood-stream image ' position and size and frame rate R1 export transmitting-receiving control portion 114 to.

Therefore, region-of-interest ROI1, ROI1 of blood-stream image ' size (the length d on depth direction) become length corresponding to the mobile amount L and/or translational speed V of the tip position with the per unit time calculated by region-of-interest configuration part 113.

According to the result calculated by calculating parts 112 such as mobile amounts, such as speed index be 2, acceleration index be 1 time, region-of-interest configuration part 113 is with reference to mobile amount relation table, obtain the depth index d3 corresponding with speed index and acceleration index, and, with reference to speed relation table, obtain the frame rate R1 corresponding with depth index d3 and 14fps.

(wave beam transmission, wave beam receive)

Transmitting-receiving control portion 114 accepts the position of region-of-interest ROI1 of blood-stream image and size and frame rate R1, obtain receipt-transmission conditions, by being controlled in transmission portion 103 and reception portion 102, carry out the transmission of ultrasound beamformer and the reception (doppler mode shooting) of reflection wave. In addition, transmitting-receiving control portion 114 accepts size and the frame rate R1 of the region-of-interest ROI2 of ultrasonic wave image, obtain receipt-transmission conditions, by being controlled in transmission portion 103 and reception portion 102, carry out the transmission of ultrasound beamformer and the reception (B-mode shooting) of reflection wave. As mentioned above, it is necessary, B-mode shooting and doppler mode shooting are carried out in a time division manner.

(generation of ultrasonic wave image, blood-stream image generation, coordinate comparison etc.)

The beam signal that B-mode image process portion 104 is obtained based on being taken by B-mode, generates three-dimensional ultrasonic wave image. The beam signal that doppler image process portion 106 is obtained based on being taken by doppler mode, generates three-dimensional blood-stream image. The coordinate of the ultrasonic wave image of the blood-stream image that display control unit (not shown) comparison is three-dimensional and three-dimensional, makes the blood-stream image in the region-of-interest ROI1 corresponding with tip position be overlapped in ultrasonic wave image and shows. Fig. 5 A illustrates the region-of-interest ROI1 of blood-stream image, and illustrates the mark M that the tip position configured in the upper end of region-of-interest ROI1 represents.

Next, according to the result calculated by calculating parts 112 such as mobile amounts, such as speed index be 2, acceleration index be 3 time, region-of-interest configuration part 113 is with reference to mobile amount relation table, obtain the depth index d5 corresponding with speed index and acceleration index, further, with reference to speed relation table, the frame rate R1 corresponding with depth index d5 and 10fps is obtained.

Transmitting-receiving control portion 114 accepts the position of region-of-interest ROI1 ' of blood-stream image and size and frame rate R1, obtain receipt-transmission conditions, by being controlled in transmission portion 103 and reception portion 102, carry out the transmission of ultrasound beamformer and the reception (doppler mode shooting) of reflection wave. In addition, transmitting-receiving control portion 114 accepts size and the frame rate R1 of the region-of-interest ROI2 of ultrasonic wave image, obtain receipt-transmission conditions, by being controlled in transmission portion 103 and reception portion 102, carry out the transmission of ultrasound beamformer and the reception (B-mode shooting) of reflection wave. As mentioned above, it is necessary, B-mode shooting is carried out in a time division manner with doppler mode shooting.

The beam signal that B-mode image process portion 104 is obtained based on being taken by B-mode, generates three-dimensional ultrasonic wave image. The beam signal that doppler image process portion 106 is obtained based on being taken by doppler mode, generates three-dimensional blood-stream image. The coordinate of the ultrasonic wave image of the blood-stream image that display control unit (not shown) comparison is three-dimensional and three-dimensional, makes the blood-stream image in the region-of-interest ROI1 ' corresponding with tip position be overlapped in ultrasonic wave image and shows. According to speed index and acceleration index in Fig. 2, illustrate region-of-interest ROI1, ROI1 of the different blood-stream image of length d '. Wherein, in order to simplify accompanying drawing, eliminate the mark M (with reference to Fig. 5 A) represented by the tip position configured in the upper end of region-of-interest ROI1 ' in fig. 2, in addition, in order to compare region-of-interest ROI1, ROI1 ' size, in region-of-interest ROI1 ', pay close attention to region ROI1 with dotted line.

(cross-section image generation)

Wherein, cross-section image process portion 108 accepts tip position, generates the cross-section image in section A, section B and section C. Display control unit (not shown) makes indicating meter show each cross-section image (with reference to Fig. 5 A��Fig. 5 C). Further, as shown in Figure 5A, cross-section image process portion 108 obtains the position PC of the section C on section A, and the cross-section image that display control unit makes the position PC of section C be overlapped in section A shows.

Owing to showing cross-section image (particularly the cross-section image in section C), it is possible to visual confirmation is in the object (being according to circumstances blood vessel) of the position (i.e. the position of section C) that have left predetermined distance from needle point along depth direction. Further, owing to making the position display of section C in other section (section A or section B), it is possible in the position range estimation of section C being shown in other sections from the distance of needle point to section C.

In addition, the face orthogonal with the direction DR (being also the face orthogonal with guiding puncture circuit GL) that puncture needle NL moves ahead that cross-section image process portion 108 can also be created on the position that have left the distance predetermined from tip position along depth direction (Y-direction) has projected the project image of the blood-stream image being positioned at depth direction than the position in this face, and display control unit makes project image show. Consequently, it is possible to 1 or multiple object (the blood vessel V N shown in Fig. 5 A) that visual confirmation exists from needle point along depth direction at the periphery of needle point NT.

< the 2nd implements mode >

With reference to each figure, the diagnostic ultrasound equipment of the 2nd enforcement mode is described. In this second embodiment, being described mainly for the formation different from the diagnostic ultrasound equipment of the first enforcement mode, for identical formation, the description thereof will be omitted sometimes.

Fig. 8 is the time figure representing the action from each portion till the display moving to cross-section image of puncture needle NL.

In the first embodiment, tip position obtaining section 111 obtains the position of needle point on coordinate by the unit time. the calculating parts 112 such as mobile amount calculate the mobile amount L and translational speed V of the tip position of per unit time based on the tip position obtained, region-of-interest configuration part 113 is in operation, whenever obtaining tip position by tip position obtaining section 111, just the mode of tip position is become according to the upper edge (head in the region-of-interest of the blood-stream image of approximate taper of decaptitating) of the region-of-interest ROI1 of blood-stream image, the region-of-interest ROI1 of the blood-stream image of the length d on depth direction corresponding for the mobile amount L and/or translational speed V with the tip position with the per unit time is set in the position corresponding with tip position.

On the other hand, in this second embodiment, as shown in Figure 8, diagnostic ultrasound equipment does not have the calculating parts 112 such as mobile amount. Region-of-interest configuration part 113 is in operation, whenever obtaining tip position by tip position obtaining section 111, just obtain the region-of-interest ROI1 comprising tip position along the blood-stream image of the travel direction (guiding puncture circuit) of needle point, the region-of-interest ROI1 of the blood-stream image corresponding with tip position is delivered to transmitting-receiving control portion 114. Thus, the upper edge (head in the region-of-interest of the blood-stream image of approximate taper of decaptitating) that set region-of-interest ROI1 comprises tip position, i.e. region-of-interest ROI1 becomes tip position (with reference to Fig. 9 A). In this second embodiment, the position of the region-of-interest ROI1 of blood-stream image is changed in region-of-interest configuration part 113 according to tip position, but the size of the region-of-interest ROI1 of blood-stream image (length d, w, u) does not change according to the mobile amount L and/or translational speed V of the tip position of per unit time, is constant.

Fig. 9 A is the ultrasonic wave image of the three-dimensional in section A. As shown in Figure 9 A, display control unit (not shown) makes the region-of-interest ROI1 of indicating meter display blood-stream image and the mark M for identifying tip position. Mark M is displayed on the position of the upper end of the region-of-interest ROI1 of blood-stream image.

Owing to the region-of-interest ROI1 of blood-stream image moves to the position corresponding with tip position, so display is positioned at the object of depth direction than tip position, whether the people performed an operation can contain blood vessel V N (with reference to Fig. 9 A) by visual confirmation in shown object.

Fig. 9 A is the ultrasonic wave image of the three-dimensional in section A, Fig. 9 B is the ultrasonic wave image of the three-dimensional in section B, Fig. 9 C is the ultrasonic wave image of the three-dimensional in section C, and Fig. 9 D is the figure of the mutual position relation representing ultrasonic wave image, section A, section B and section C.

As shown in Fig. 9 A��Fig. 9 D, in this second embodiment, cross-section image process portion 108 also generates the cross-section image in section A, section B and section C, and display portion 110 makes the cross-section image in section A, section B and section C be shown in indicating meter.

In the above-described embodiment, make blood-stream image be overlapped in ultrasonic wave image and show, but blood-stream image can also be made to be overlapped in morphological image (CT image or MRI image) and show. Wherein, the mark M for identifying tip position is now together shown with blood-stream image. Thus, morphological image shows in real time the position relation of blood vessel and needle point, it is possible to whether the front accurately resting in needle point traveling is just having blood vessel to pass through.

In addition, in the above-described embodiment, in order to easy together visual confirmation region-of-interest ROI1, ROI2, show so display control unit (not shown) makes three-dimensional blood-stream image be overlapped in three-dimensional ultrasonic wave image, but it is not limited thereto.Such as, the ultrasonic wave image that display control unit can also make the blood-stream image of two dimension or three-dimensional be overlapped in two dimension shows. Thus, even if the needle point of puncture needle NL departs from from the ultrasonic wave image of two dimension, it is also possible to by whether two dimension or three-dimensional blood-stream image visual confirmation exist blood vessel at the periphery of needle point. Further, the ultrasonic wave image that display control unit can also make the blood-stream image of two dimension be overlapped in three-dimensional shows. Thus, if the plane parallel of the direction DR that such as puncture needle NL moves ahead and two Dimensional XY, then can by the blood-stream image visual confirmation of two dimension whether the front that needle point is advanced has blood vessel. Further, due to the blood-stream image relative to three-dimensional, the frame rate of the blood-stream image of two dimension maintains higher, so blood-stream image is shown in real time.

Further, in the above-described embodiment, the arbitrary distance that the distance illustrated from tip position to the position of section C is such as decided to be 0mm��20mm, the situation that the cross-section image of the section C of the position determined is shown, but be not limited thereto. The configuration parts such as cross section place 117 are the interim distance determined from tip position to the position of section C as 0mm, 5mm, 10mm, 15mm, 20mm such as, the cross-section image of the section C of the position of the distance that cross-section image process portion 108 generation phase determines, display control unit makes 1 of the cross-section image of the section C of indicating meter selectivity display position or multiple. Thus, the people performed an operation is by according to mobile amount when making needle point NT move to depth direction, inputting desired distance to the configuration parts such as cross section place 117, it is possible to select to be suitable for the cross-section image of the section C of the position of people performed an operation. In addition, by carrying out have selected the display of two or more cross-section image, such as it is not shown in the cross-section image of distance for the section C of the position of 5mm at blood-vessel image, and when being shown in the cross-section image that distance is the section C of the position of 15mm, the people performed an operation knows can make needle point NT move about 10mm to depth direction.

< the 3rd implements mode >

The diagnostic ultrasound equipment of the 3rd enforcement mode is described. In the third embodiment, mainly the formation different from the diagnostic ultrasound equipment of the first enforcement mode being described, for identical, when being configured with, the description thereof will be omitted.

Figure 10 is the formation block diagram of the formation of the diagnostic ultrasound equipment representing the 3rd enforcement mode. The diagnostic ultrasound equipment of the 3rd enforcement mode replaces the blood-stream image generating unit 106A in the first enforcement mode and has volume image generating unit 118A. Volume image generating unit 118A is equivalent to an example of the region-of-interest image production part in technical scheme. Volume image generating unit 118A has volume image process portion 118 and volume image storage portion 119.

Transmitting-receiving control portion 114 is in order to carry out B-mode shooting and bulk-mode shooting in a time division manner, such as, such as according to the mode just carrying out 1 B-mode shooting when repeatedly (4 times) bulk-mode carrying out specifying is taken, transmission portion 103 and reception portion 102 are controlled.

During transmitting-receiving control portion 114 In vivo is taken, accept region-of-interest and the frame rate of volume image, obtain transmission condition (time of lag, transmission times) and receiving conditions (reception channel, each channel latency amount), by transmission portion 103 and reception portion 102 being controlled with these conditions, undertaken by each sweep trace specifying repeatedly (such as, 4 times) the transmission of ultrasound beamformer and the reception of reflection wave, the scanning of 1 static image volume of the sweep trace of the radical repeating to have the form of the three-dimensional in order to describe in region-of-interest with the frame rate of volume image and need.Volume image is equivalent to an example of the region-of-interest image in technical scheme.

The region-of-interest of the volume image in the 3rd enforcement mode corresponding to the blood-stream image shown in Fig. 2 region-of-interest ROI1, ROI1 '. In addition, the frame rate of volume image is corresponding to the frame rate R1 in the first enforcement mode.

Transmitting-receiving control portion 114 accepts the region-of-interest ROI2 of ultrasonic wave image and region-of-interest ROI1, ROI1 ' of frame rate R2 and blood-stream image and frame rate R1 thereof thereof, in order to carry out B-mode shooting and bulk-mode shooting in a time division manner, such as, such as according to whenever repeatedly (4 times) bulk-mode carrying out specifying takes the mode just carrying out 1 B-mode shooting, transmission portion 103 and reception portion 102 are controlled.

The beam signal that volume image process portion 118 is obtained based on being taken by bulk-mode, generates volume image, and is stored in volume image storage portion 119.

Next, with reference to Figure 11, the action at each position forming the 3rd enforcement mode is described.

When the beginning performed the operation, tip position obtaining section 111 obtains the position of needle point NT on the coordinate of the ultrasonic wave image of three-dimensional, region-of-interest configuration part 113 set the region-of-interest ROI2 (constant) of ultrasonic wave image, frame rate R2 (constant), as blood-stream image region-of-interest ROI1, ROI1 ' the depth index (initial value: d3) of size and frame rate R1 (initial value: 14fps). Transmitting-receiving control portion 114 controls transmission portion 103 and reception portion 102 based on the condition comprising these information, and B-mode image process portion 104 generates three-dimensional ultrasonic wave image based on acquired reception wave beam, and volume image process portion 118 generates volume image.

Figure 11 is the time figure of the action from each portion till the display moving to cross-section image of puncture needle NL representing in art. Wherein, in operation, the size (constant) of region-of-interest ROI2 and its frame rate R2 (constant) based on ultrasonic wave image generate three-dimensional ultrasonic wave image, and the ultrasonic wave image of generation is shown in indicating meter. Perform the operation start time, the size (initial value) of region-of-interest ROI1 and frame rate R1 (initial value) based on volume image generate volume image, and the volume image of generation is overlapped in ultrasonic wave image and is shown to indicating meter.

Region-of-interest configuration part 113 is based on the position of needle point NT on three-dimensional coordinate and the mobile amount L and/or translational speed V of the tip position of per unit time that calculates, according to this speed index and acceleration index, with reference to the mobile amount relation table shown in Fig. 4, obtain position and the depth index of the region-of-interest of volume image, and with reference to the speed relation table shown in Fig. 3, obtain the frame rate R1 corresponding with depth index, by region-of-interest ROI1, ROI1 of volume image ' position and size and frame rate R1 export transmitting-receiving control portion 114 to.

Therefore, region-of-interest ROI1, ROI1 of volume image ' size (the length d on depth direction) become length corresponding to the mobile amount L and/or translational speed V of the tip position with the per unit time calculated by region-of-interest configuration part 113.

Transmitting-receiving control portion 114 accepts the position of region-of-interest ROI1 of blood-stream image and size and frame rate R1, obtain receipt-transmission conditions, by being controlled in transmission portion 103 and reception portion 102, carry out the transmission of ultrasound beamformer and the reception (bulk-mode shooting) of reflection wave. In addition, transmitting-receiving control portion 114 accepts size and the frame rate R1 of the region-of-interest ROI2 of ultrasonic wave image, obtain receipt-transmission conditions, by being controlled in transmission portion 103 and reception portion 102, carry out the transmission of ultrasound beamformer and the reception (B-mode shooting) of reflection wave.As mentioned above, it is necessary, B-mode shooting and bulk-mode shooting are carried out in a time division manner.

The beam signal that B-mode image process portion 104 is obtained based on being taken by B-mode, generates three-dimensional ultrasonic wave image. The beam signal that volume image process portion 118 is obtained based on being taken by bulk-mode, generates volume image.

Transmitting-receiving control portion 114 accepts the position of region-of-interest ROI1 ' of blood-stream image and size and frame rate R1, obtain receipt-transmission conditions, by being controlled in transmission portion 103 and reception portion 102, carry out the transmission of ultrasound beamformer and the reception (bulk-mode shooting) of reflection wave. In addition, transmitting-receiving control portion 114 accepts size and the frame rate R1 of the region-of-interest ROI2 of ultrasonic wave image, obtain receipt-transmission conditions, by being controlled in transmission portion 103 and reception portion 102, carry out the transmission of ultrasound beamformer and the reception (B-mode shooting) of reflection wave. As mentioned above, it is necessary, B-mode shooting and bulk-mode shooting are carried out in a time division manner.

The beam signal that B-mode image process portion 104 is obtained based on being taken by B-mode, generates three-dimensional ultrasonic wave image. The beam signal that volume image process portion 118 is obtained based on being taken by bulk-mode, generates volume image. The coordinate of the ultrasonic wave image of display control unit (not shown) comparison volume image and three-dimensional, makes the volume image in the region-of-interest ROI1 ' corresponding with tip position be overlapped in ultrasonic wave image and shows.

The diagnostic ultrasound equipment of mode is implemented according at least one describing above, paracentesis under ultrasonic wave (echo) guides can maintain high frame rate, display blood-stream image or volume image in real time, can eliminate and make operation cure the factor spun out, the people performed an operation is not caused burden.

Several enforcements modes of the present invention being illustrated, these are implemented mode and just illustrate, and are not intended to limit the scope of invention. These enforcement modes can be implemented in other various modes, can carry out various omission, displacement, change in the scope not departing from inventive concept. These enforcement modes and distortion thereof are included in the invention described in claim with in its equivalent scope samely with the scope and purport that are contained in invention.

Claims (10)

1. a diagnostic ultrasound equipment, it is characterised in that, have:

Transmission portion, sends ultrasound beamformer to the subject of the puncture needle that punctured while scanning;

Reception portion, receives the signal reflected from described subject;

Tip position obtaining section, successively obtains the tip position of described puncture needle;

Region-of-interest configuration part, at least sets the region-of-interest thrusting on direction of described tip position;

Region-of-interest image production part, according to the tip position successively obtained by described tip position obtaining section, generates the region-of-interest image in described region-of-interest based on the described signal received; And

Display control unit, shows the region-of-interest image generated by described region-of-interest image production part.

2. diagnostic ultrasound equipment according to claim 1, it is characterised in that,

Described region-of-interest image production part generates the blood-stream image of the blood flow information representing described region-of-interest as described region-of-interest image.

3. diagnostic ultrasound equipment according to claim 1, it is characterised in that,

Described region-of-interest image production part generates the volume image of described region-of-interest as described region-of-interest image.

4. diagnostic ultrasound equipment according to claim 1, it is characterised in that,

The quantity of the image that described region-of-interest image production part generated with the per unit the time more than lower value that predetermines and speed to generate described region-of-interest image,

Described region-of-interest configuration part sets the size of described region-of-interest according to the mode of the lower value being not less than described speed.

5. diagnostic ultrasound equipment according to claim 1, it is characterised in that,

Described region-of-interest configuration part sets the size of described region-of-interest according to the mobile amount of the per unit time of the described tip position successively obtained and/or the translational speed of per unit time.

6. diagnostic ultrasound equipment according to claim 5, it is characterised in that,

The setting of described region-of-interest configuration part from described tip position length in the depth direction as the size of described region-of-interest.

7. diagnostic ultrasound equipment according to claim 1, it is characterised in that,

Described transmission portion also sends ultrasound beamformer on one side in the depth direction, in the enterprising line scanning in the direction orthogonal with this direction and width,

Described reception portion also receives the signal come from the reflection of described subject,

Described diagnostic ultrasound equipment also has the ultrasonic wave image production part generating ultrasonic wave image based on the described signal received,

Described display control unit makes the described region-of-interest image in the described region-of-interest corresponding with the described tip position in described ultrasonic wave image be overlapped in described ultrasonic wave image to show.

8. diagnostic ultrasound equipment according to claim 1, it is characterised in that,

Described diagnostic ultrasound equipment also has cross-section image generating unit, this cross-section image generating unit obtains, based on the described described tip position successively obtained, the direction that described puncture needle moves ahead, and based on the described region-of-interest image in the described region-of-interest corresponding with described tip position, generate the cross-section image the face orthogonal with the direction moved ahead described in described obtaining of the position that have left the distance predetermined from described tip position to the described direction moved ahead

Described display control unit makes described cross-section image show.

9. diagnostic ultrasound equipment according to claim 8, it is characterised in that,

Described cross-section image generating unit is also based on the region-of-interest image in the described region-of-interest corresponding with described tip position, generate along the image in the direction orthogonal with depth direction and width and the face orthogonal with described cross-section image, and obtain the position of the described cross-section image in this image

Described display control unit makes the position display of described cross-section image in described orthogonal section image.

10. diagnostic ultrasound equipment according to claim 1, it is characterised in that,

Described diagnostic ultrasound equipment also has cross-section image generating unit, this cross-section image generating unit obtains, based on the described described tip position successively obtained, the direction that described puncture needle moves ahead, and based on the described region-of-interest image in the described region-of-interest corresponding with described tip position, be created on the face orthogonal with the direction moved ahead described in described obtaining of the position that have left the distance predetermined from described tip position to the described direction moved ahead to have projected than described in the position left be positioned at the project image of described blood-stream image of depth direction

Described display control unit makes described project image show.