CN109414245A - The display methods and its ultrasonic image-forming system of supersonic blood movement spectrum - Google Patents

Abstract

A kind of supersonic blood imaging display methods and display system, system include: probe (1)；Transmit circuit (2), for motivating above-mentioned probe (1) to scanning objective emission ultrasonic beam；Circuit (4) and Beam synthesis module (5) are received, for receiving the echo of the ultrasonic beam, obtains ultrasound echo signal；Data processing module (9) generates movement velocity curve spectrum according to blood flow velocity for calculating the blood flow velocity of multiple target points in area-of-interest according to the ultrasound echo signal；And display (8), for showing that movement velocity curve is composed.

Description

The display methods and its ultrasonic image-forming system of supersonic blood movement spectrum Technical field

The present invention relates to blood flow information imaging display techniques in ultrasonic system, more particularly to the display methods and its ultrasonic image-forming system of a kind of supersonic blood movement spectrum.

Background technique

In medical ultrasound image equipment, within Ultrasonic Radiation to examined object, color Dopplerimaging realizes imaging as impulse wave and continuous wave Doppler, also with the Doppler effect between red blood cell and ultrasonic wave.Color Dopplerimaging includes two-dimensional ultrasonic image system, pulse Doppler (one-dimensional Doppler) blood flow analysis system, continuous wave Doppler blood flow measurement system and color Doppler (two-dimensional Doppler) blood flow display system.Oscillator generates two orthogonal signalling that difference is pi/2, it is multiplied respectively with doppler blood flow signal, its product is transformed into digital signal through analog/digital (A/D) converter, it is filtered through comb filter, after the low frequency component for removing the generations such as vascular wall or valve, it is sent into autocorrelator and makees Autocorrelation Detection.Since every sub-sampling all contains Doppler flow information caused by many a red blood cells, what is obtained after Autocorrelation Detection is the mixed signal of multiple blood flow velocity.Autocorrelation Detection result is sent into velocity calculator and variance calculator and acquires average speed, is stored in digital scan converter (DSC) together with through FFT treated blood flow frequency spectrum information and two-dimensional image information.Finally, sending color monitor to show as pseudo-color coding blood flow data by color processor, to complete color doppler flow imaging according to the direction of blood flow and velocity magnitude.

Frequency spectrum Doppler is used for the quantitative Diagnosis of valve stenosis and arteriosclerotic lesion etc..What traditional frequency spectrum Doppler obtained is frequency spectrum of the blood flow along transonic direction velocity component.It is not actual speed spectrum distribution, and it is influenced by gimmick, blood vessel and the angle in transonic direction are also difficult to be consistent when scanning every time, therefore cause the precision of measurement and repeatability poor, are unable to get the velocity amplitude for more efficiently reacting blood flow actual conditions.Although true speed can be estimated using the method for angle correction, the case where this is only limitted to laminar flow, and the angle corrected is similarly subjected to the influence of gimmick there may be certain deviations.More actual blood circumstance can not be effectively reacted about Doppler frequency spectrum in view of above-mentioned, it is necessary to provide a kind of more intuitive blood flow information displaying scheme.

Summary of the invention

Based on this, it is necessary to aiming at the shortcomings in the prior art, provide the display methods and its ultrasonic image-forming system of a kind of supersonic blood movement spectrum, provide more intuitive blood flow movement information display scheme, and provide better observation visual angle for user.

A kind of display methods of supersonic blood movement spectrum is provided in one embodiment of the present of invention comprising:

The ultrasonic signal in scanning target is obtained by probe；

Based on the ultrasonic signal, the blood flow velocity in the scanning target in vascular is obtained；

According to the ultrasonic signal, at least part of ultrasound image of the scanning target is obtained；

Obtain the concern position being located in the vascular；

The associated coordinates system of speed and time is drawn in viewing area；

In the associated coordinates system, the variation of the value of blood flow velocity at the concern position is shown according to the variation sequence of time, obtains movement velocity curve spectrum associated with the concern position；

The concern position is marked on the ultrasound image.

A kind of ultrasonic image-forming system is provided in one embodiment of the present of invention comprising:

Probe；

Transmit circuit, for motivating described pop one's head in scanning objective emission ultrasonic beam；

Circuit and Beam synthesis module are received, for receiving the echo of the ultrasonic beam, obtains the ultrasonic signal in scanning target；

Image processing module, for being based on the ultrasonic signal, obtain the blood flow velocity in the scanning target in vascular, according to the ultrasonic signal, obtain at least part of ultrasound image of the scanning target, the concern position being located in the vascular is obtained, the associated coordinates system of speed and time is drawn in viewing area；And

Display, for showing the variation of the value of blood flow velocity at the concern position according to the variation sequence of time in the associated coordinates system, movement velocity curve spectrum associated with the concern position is obtained, and show ultrasound image, the concern position is marked on the ultrasound image.

Detailed description of the invention

Fig. 1 is the block diagram representation of the ultrasonic image-forming system of one embodiment of the invention；

Fig. 2 is the schematic diagram of the plane ultrasonic wave beam of the Vertical Launch of one embodiment of the invention；

Fig. 3 is the schematic diagram of the plane ultrasonic wave beam of the deflection transmitting of one embodiment of the invention；

Fig. 4 is the received schematic diagram of multi-angle in one embodiment of the invention；

Fig. 5 is the method flow schematic diagram of one embodiment of the invention；

Fig. 6 is the method flow schematic diagram of one embodiment of the invention；

Fig. 7 is the method schematic diagram of the screening blood flow velocity maximum value of the one of embodiment of the present invention；

Fig. 8 is the method schematic diagram of the screening blood flow velocity maximum value of the one of embodiment of the present invention

Fig. 9 is the method flow schematic diagram of the one of embodiment of the present invention；

Figure 10 is the method flow schematic diagram of the one of embodiment of the present invention；

Ultrasound image in multiple embodiments in Figure 11, Figure 12, Figure 13, Figure 14 and Figure 15 respectively present invention The schematic diagram of comparison display is composed with movement velocity curve；

Figure 16 (a) is that blood flow velocity Vector Message calculates schematic diagram under first mode in one embodiment of the invention；

Figure 16 (b) is that blood flow velocity Vector Message calculates schematic diagram under second mode in one embodiment of the invention；

Figure 17 is the present invention display schematic diagram that movement velocity curve is composed in one embodiment；

Figure 18 is the method flow schematic diagram of the one of embodiment of the present invention.

Specific embodiment

Fig. 1 is the structural block diagram schematic diagram of the ultrasonic image-forming system of the present embodiment one embodiment.As shown in Figure 1, the ultrasonic image-forming system generally includes: probe 1, transmitting/reception selection switch 3, receives circuit 4, Beam synthesis module 5, signal processing module 6, image processing module 7 and display 8 at transmit circuit 2." multiple " herein refer to more than or equal to 2.

In ultrasound imaging procedure, transmit circuit 2 by what is focused by delay there is certain amplitude and polar transmitting pulse to select switch 3 to be sent to probe 1 by transmitting/reception.Probe 1 is by exomonental excitation, to scanning target (such as, human body or the intracorporal organ of animal, tissue, blood vessel etc., it is not shown in the figure) transmitting ultrasonic wave, the ultrasonic echo from the reflected information with scanning target in target area is received after certain time-delay, and this ultrasonic echo is converted into electric signal again.The electric signal that the conversion of circuit receiving transducer 1 generates is received, obtains ultrasound echo signal, and these ultrasound echo signals are sent into Beam synthesis module 5.Beam synthesis module 5 is focused the processing such as delay, the summation of weighted sum channel to ultrasound echo signal, obtains ultrasonic signal, and ultrasonic signal feeding signal processing module 6 is then carried out relevant signal processing, such as filtering.Image processing module 7 is sent by the ultrasound echo signal that signal processing module 6 is handled.The difference of the imaging pattern according to needed for user of image processing module 7, different processing is carried out to signal, obtain the image data of different mode, then the ultrasound image of different mode is formed through processing such as log-compressed, dynamic range adjustment, digital scan conversions, such as B image, C image, the two dimensional images such as D image, in addition, the ultrasound image may also include 3-D image.The ultrasound image that image processing module 7 generates is sent into display 8 and is shown.In addition, image processing module 7 can also calculate the blood flow velocity of target point according to ultrasound echo signal, and it will export to blood flow velocity and be shown to display.Image processing module 7 and signal processing module 6 is separately positioned on the different processors or is integrated in same processor 9.

The target point mentioned in the present embodiment can be a pixel on ultrasound image or contain at least two the region unit of pixel.The blood flow velocity mentioned in the present embodiment, for characterizing the flow rate information of blood flow movement state in scanning target, for example, may include the velocity vector etc. for being used to characterize target point blood flow velocity in scanning target for scanning the Doppler frequency of target point in target, or estimate to obtain.As it can be seen that image processing module 7 The blood flow velocity of calculating can be a velocity amplitude, be also possible to a velocity vector.Velocity vector includes velocity amplitude and directional velocity, usually uses the expression way of vector.The manifestation mode of velocity amplitude can be numerical value, be also possible to spectrum expression, for example, the velocity amplitude of blood flow can be Doppler frequency value, be also possible to the expression of Doppler frequency spectrum form.The relevant calculation mode of blood flow velocity will hereafter will be explained in more detail.

Probe 1 generally includes the array of multiple array elements.In transmitting ultrasonic wave every time or reception ultrasonic wave, a part in 1 all array elements or all array elements of popping one's head in participates in the transmitting of ultrasonic wave.At this time, each array element or every part array element in the array element of these participation ultrasonic wave transmittings is respectively by exomonental excitation, and emit ultrasonic wave respectively, the ultrasonic wave that these array elements emit respectively is superimposed in communication process, the synthesis ultrasonic beam for being launched into scanning target is formed, the direction of propagation of the synthesis ultrasonic beam is the launch angle of ultrasonic wave mentioned herein.The array element for participating in ultrasonic wave transmitting can be launched pulse excitation simultaneously；Alternatively, the array element for participating in ultrasonic wave transmitting, which was launched between the time of pulse excitation, can certain delay.It is launched the delay between the time of pulse excitation by the array element that control participates in the transmitting of ultrasonic wave, the direction of propagation of above-mentioned synthesis ultrasonic beam can be changed, hereafter will be explained in detail.

The delay between the time of pulse excitation is launched by the array element that control participates in the transmitting of ultrasonic wave, can also make the ultrasonic wave of each array element transmitting for the transmitting for participating in ultrasonic wave will not focus in communication process, will not be completely divergent, but form plane wave generally planar on the whole.Or, the delay between the time of pulse excitation is launched by the array element that control participates in the transmitting of ultrasonic wave, the ultrasonic beam of each array element transmitting can be made to be superimposed in predetermined position, so that in the maximum intensity of the pre-position ultrasonic wave, namely make the ultrasonic wave " focusing " of each array element transmitting to the pre-position, the predetermined position of the focusing is known as " focus ", in this way, the ultrasonic beam of the synthesis of acquisition is the wave beam for focusing on the focal point, referred to herein as " focused ultrasound beams ".During transmitting focusing ultrasonic beam, the array element for participating in the transmitting of ultrasonic wave can be worked in a manner of scheduled transmitting time delay (i.e. there are scheduled time delays between the time that the array element of the transmitting of participation ultrasonic wave is launched pulse excitation), the ultrasonic wave of each array element transmitting is focused in focal point, forms focused ultrasound beams.Or the delay between the time of pulse excitation is launched by the array element that control participates in the transmitting of ultrasonic wave, it dissipates the ultrasonic wave of each array element transmitting for the transmitting for participating in ultrasonic wave in communication process, forms on the whole substantially diverging wave.Herein, the ultrasonic wave of this divergence form is referred to as " diverging ultrasonic beam ".

Linearly aligned multiple array elements give electric impulse signal excitation simultaneously, and each array element emits ultrasonic wave simultaneously, and the direction of propagation of the ultrasonic beam of synthesis is consistent with the array element arrangement normal direction of plane.For example, the plane wave of Vertical Launch as shown in Figure 2, participates in not having time delay (i.e. each array element, which was launched between the time of pulse excitation, does not have time delay) between each array element of the transmitting of ultrasonic wave at this time, each array element is launched pulse while motivating.The ultrasonic beam of generation is plane wave, that is plane ultrasonic wave beam, and the direction of propagation of the plane ultrasonic wave beam and the surface for launching ultrasonic wave of probe 1 are generally vertically, that is, the angle between the direction of propagation of the ultrasonic beam synthesized and the normal direction of array element arrangement plane is zero degree.But if the driving pulse being applied between each array element has one A time delays, each array element is also successively according to this time delay emission ultrasonic beam, the normal direction of the direction of propagation of the ultrasonic beam then synthesized and array element arrangement plane just has certain angle, as synthesize the launch angle of wave beam, change above-mentioned time delays, can also adjust the size of the launch angle of synthesis wave beam and the direction of the launch in the plane of scanning motion of synthesis wave beam relative to the normal direction of array element arrangement plane.Such as, Fig. 3 show the plane wave of deflection transmitting, participate in having scheduled time delay (i.e. each array element, which was launched between the time of pulse excitation, scheduled time delay) between each array element of the transmitting of ultrasonic wave at this time, each array element is launched pulse and motivates in a predetermined sequence.The ultrasonic beam of generation is plane wave, that is plane ultrasonic wave beam, and the normal direction of the array element of the direction of propagation of the plane ultrasonic wave beam and probe 1 arrangement plane has a certain degree, and (for example, the angle a) in Fig. 3, which is the launch angle of the plane ultrasonic wave beam.By changing decay time, the size of adjustable angle a.Similarly, either plane ultrasonic wave beam, focused ultrasound beam still dissipate ultrasonic beam, the array element for the transmitting that ultrasonic wave can be participated in by adjusting control is launched the delay between the time of pulse excitation, " launch angle " that synthesizes wave beam is formed by between the direction of synthesis wave beam and the normal direction of array element arrangement plane to adjust, synthesis wave beam here can be plane ultrasonic wave beam mentioned above, focused ultrasound beam or diverging ultrasonic beam etc..

Furthermore, although only providing the implementation of the launch angle of linear array above, but for two-dimensional ultrasound transducer, it can be understood as the combination of multiple linear arrays, therefore, the array element for the transmitting that two-dimensional ultrasound transducer can also participate in ultrasonic wave by control is launched the delay between the time of pulse excitation, to adjust " launch angle " that is formed by synthesis wave beam between synthesis wave beam and the normal direction of array element arrangement plane.

Further, the aperture location of the received array element (referred to as receiving array element herein) of ultrasonic wave, the receiving angle of adjustable received ultrasound echo signal are participated in by control.For example, as shown in figure 4, ultrasonic probe includes array element portion 1, array element portion 2, array element portion 3 and array element portion 4.Array element portion 1, array element portion 2, array element portion 3 and array element portion 4 can be an array element or multiple array elements.Array element can be received with the combination in one or more of array element portion 1, array element portion 2, array element portion 3 and array element portion 4.In Fig. 4, to comprising aiming spot A scanning one launch angle of objective emission ultrasonic beam when, using array element portion 1 as reception array element, receive the echo of the reflected ultrasonic beam of some aiming spot A out of scanning target, according to the line (label is in Fig. 4) of the aperture location in array element portion 1 and aiming spot A, the receiving angle a1 of the echo of current time received ultrasonic beam can be determined.Simultaneously, according to using array element portion 2 as reception array element, receive the echo of the reflected ultrasonic beam of some aiming spot A out of scanning target, according to the line (label is in Fig. 4) of the aperture location in array element portion 2 and aiming spot A, the receiving angle a2 of the echo of current time received ultrasonic beam can be determined.The echo of the ultrasonic beam returned from the same target position A can obtain the echo of the ultrasonic beam of two different receiving angles.Therefore, according to receive array element aperture location and aiming spot between line and ultrasound element arrange plane normal direction between angle, come define above-mentioned ultrasonic beam echo " receiving angle ".The aperture location of array element is received on probe by changing, It then can change " receiving angle " of the echo of ultrasonic beam, to obtain the echo of the ultrasonic beam of different receiving angles.

Based on above-mentioned explanation, to scanning objective emission ultrasonic beam, it is expected that when obtaining the ultrasonic signal of multiple angles from scanning target, both it can change the receiving angle of the echo of ultrasonic beam by changing the aperture location of reception array element on probe, to obtain the corresponding ultrasonic signal of different receiving angles from scanning target；The array element for the transmitting that can also participate in ultrasonic wave by control is launched the delay between the time of pulse excitation, change the launch angle of ultrasonic beam, the echo of ultrasonic beam based on different launch angles obtains the corresponding ultrasonic signal of different launch angles from scanning target.Image processing module 7 can calculate in scanning target or scan the blood flow velocity of multiple target points in area-of-interest in target according to the ultrasonic signal of different angle.

Furthermore, it further include operation control module 10 in ultrasonic image-forming system shown in FIG. 1, for receiving the adjustment signal from operation user's input, the adjustment signal includes the adjustment that the imaging parameters such as the launch angle to ultrasonic beam, receiving angle, ultrasonic beam type carry out, or can also include the adjustment of the calculated result progress of the image to organization chart picture processing module, area-of-interest or blood flow velocity vector.Operating control module 10 can be man-machine interactive interface, such as keyboard, idler wheel, the touch gestures reception connecting with the display screen with touch function and computing module, mouse, the transceiver module in relation to gesture control signal etc..Display 8 in Fig. 1 includes one or more display screens, and the display screen in the present embodiment can be touch display screen, LED display etc..

The image data or movement velocity curve spectrum of image processing module output can also pass through wireless transport module, it is transferred on remote display and is shown, the scheme of the present embodiment is not limited to desk-top ultrasonic device, can also include all equipment that can be used for showing ultrasound image being included in medical internet system.

A kind of display methods of supersonic blood movement spectrum is provided in Fig. 5, its speed curve movement spectrum for being used to generate a period of time in area-of-interest, can show such as peak veloity,PV in area-of-interest change with time situation or cursor position selection multiple semi-cylindrical hills at the changes in contrast situation of blood flow velocity at any time.Wherein, the movement velocity curve spectrum can be movement velocity curve there are two types of the form of expression, one, and at the corresponding moment, record pays close attention to the value of blood flow velocity at position；The second is movement velocity map, the erythrocyte number distribution of friction speed value size in blood flow velocity at the concern position is recorded at the corresponding moment.Further, a kind of method of speed curve movement spectrum that can be detected automatically at peak veloity,PV is provided in the present embodiment, hereinafter referred maximum movement speed curve spectrum, it, which is provided, is different from traditional curve spectrogram, its can not by the gimmick of scanning probe, probe positions movement and every time scanning when the factors such as blood vessel and the variation of the angle in transonic direction influenced, and in map in moment reflection area-of-interest optimum position blood flow information, and doctor is given to provide better diagnostic base.When estimating the maximum value of blood flow using angle correction, laminar flow can be directed to, and for more complicated position, such as heart, at carotid sinus, it is not available angle correction, even if in long and straight blood vessel, such as arteria carotis communis, vertebral artery etc., being influenced angle correction still by gimmick will cause biggish error, therefore the method for using the present embodiment can provide more accurate data branch for doctor It holds, and the above problem can also be avoided, execution process is simple, and data are more accurate.Specific method is shown in steps are as follows.

As shown in figure 5, a kind of supersonic blood imaging display methods provided in this embodiment includes the following steps S100 to step S600.

In the step s 100, using circuit 4 and Beam synthesis module 5 is received, the ultrasonic signal in scanning target is obtained by probe 1.

In wherein some embodiments, using 2 incentive probe 1 of transmit circuit to scanning objective emission ultrasonic beam, the echo for receiving the ultrasonic beam obtains the ultrasonic signal.In the present embodiment to scanning objective emission ultrasonic beam may include: focused ultrasound beams and non-focused ultrasound wave beam, wherein non-focused ultrasound wave beam include: virtual source ultrasonic beam, non-diffraction ultrasonic beam, diverging at least one of a variety of beam types such as ultrasonic beam or plane ultrasonic wave beam or at least two or more combination (here " more than " include this number, it is the same below).Certainly, the ultrasonic beam of the above several types is not limited in the embodiment of the present embodiment.It can be seen that the ultrasonic signal in step S100 can be the echo-signal of ultrasonic beam.

In one of the embodiments, in the step s 100 include: step 121: to scanning objective emission focused ultrasound beams, the echo of collectiong focusing ultrasonic beam obtains and focuses ultrasound echo signal, to rebuild ultrasound image or calculating blood flow velocity etc..Alternatively, in the step s 100 including step 122: to scanning objective emission plane ultrasonic wave beam, the echo of receiving plane ultrasonic beam obtains plane ultrasonic echo-signal, to rebuild ultrasound image or calculating blood flow velocity etc..It or in the step s 100 include above-mentioned steps 121 and step 122: to scanning objective emission focused ultrasound beams, to obtain focusing ultrasound echo signal；To scanning objective emission plane ultrasonic wave beam, to obtain plane ultrasonic echo-signal.Focusing ultrasound echo signal can be used as rebuilding at least part ultrasound image of scanning target, in the hope of obtaining the preferable ultrasound image of quality as background image, and plane ultrasonic echo-signal may be used as calculating the image data basis of blood flow velocity in the step S200 in Fig. 5.

In the step s 100 according to two kinds of ultrasonic beam, then to scanning two kinds of ultrasonic beams of target alternate emission.For example, being inserted into the process to scanning objective emission focused ultrasound beams during to scanning objective emission plane ultrasonic wave beam, that is, be alternately performed above-mentioned steps 121 and step 122.It can guarantee the synchronism of two kinds of ultrasonic beam image data acquisitions in this way, improve the accuracy for the blood flow velocity that the transmitting of multi-beam angle obtains.

In addition to beam type by diversified forms, can also receive the ultrasonic signal of multiple angles to calculate blood flow velocity or ultrasound image in the step s 100.For example, in the step s 100 can be to the ultrasonic beam of scanning objective emission difference launch angle, to receive the ultrasonic signal for obtaining multiple angles.Alternatively, receiving the ultrasonic signal of different receiving angles from scanning target.As it can be seen that the ultrasonic signal of multiple angles can correspond to multiple launch angles or multiple receiving angles.Shown in specific as follows:

1, for the ultrasonic beam to scanning objective emission difference launch angle, the ultrasonic signal of multiple angles can be received along different launch angles.

In one embodiment of the present embodiment, it in the step s 100 may include: along multiple launch angles to scanning objective emission ultrasonic beam, the echo for receiving the ultrasonic beam obtains the ultrasound echo signal of multiple angles as the received ultrasonic signal of step S100.

In one of the embodiments, in the step s 100 include: along multiple launch angles to scanning objective emission ultrasonic beam, in this process, the process to scanning objective emission ultrasonic beam can be alternately performed according to the difference of launch angle.Such as, if along two launch angles to scanning objective emission ultrasonic beam, first along first launch angle to scanning objective emission ultrasonic beam, then again along second launch angle to scanning objective emission ultrasonic beam, a scan period is completed, above-mentioned scan period process is finally repeated in.Alternatively, can also first along a launch angle to scanning objective emission ultrasonic beam, then along another launch angle to scanning objective emission ultrasonic beam, complete scanning process after successively having executed all launch angles.To obtain different launch angles, it can be obtained by changing the time delay of each array element or every part array element in the array element for participating in ultrasonic wave transmitting, specifically can refer to the explanation of Fig. 2 or Fig. 3.

In one of the embodiments, along each launch angle to scanning objective emission repeated ultrasonic wave beam, to obtain repeated ultrasonic wave signal, for the processing of subsequent ultrasonic image data.For example, along multiple launch angles respectively to the multiple non-focused ultrasound wave beam of scanning objective emission or along multiple launch angles respectively to scanning objective emission multi-focusing ultrasonic beam.And the transmitting of ultrasonic beam each time corresponds to and obtains a ultrasonic signal.

It is alternately performed the process to scanning objective emission repeated ultrasonic wave beam according to the difference of launch angle, the echo data approximate calculation obtained can be made in the blood flow velocity vector of the target point of synchronization, improve the computational accuracy of velocity vector information.Such as, if along three launch angles respectively to scanning objective emission n times ultrasonic beam, it can be first along first launch angle to scanning objective emission ultrasonic beam at least once, then again along second launch angle to scanning objective emission ultrasonic beam at least once, and then along third launch angle to scanning objective emission ultrasonic beam at least once, a scan period is completed, is finally repeated in above-mentioned scan period process until completing the scanning times in all launch angles.The emitting times of ultrasonic beam in the same scan period under different launch angles can be identical, can not also be identical.For example, if it is the transmitting ultrasonic beam along two launch angles, then according to A1 B1 A2 B2 A3 B3 A4 B4 ... Ai Bi, and so on.Wherein, Ai is the i-th transmitting in first launch angle；Bi is the i-th transmitting in second launch angle.And if it is the transmitting ultrasonic beam along three launch angles, then according to A1 B1 B1C1 A2 B2 B2C2 A3 B3 B3C3 ... Ai Bi BiCi, and so on.Wherein Ai is the i-th transmitting in first launch angle；Bi is the i-th transmitting in second launch angle；Ci is the i-th transmitting in third launch angle.

When selected in above-mentioned steps S100 to scanning two kinds of beam types of objective emission ultrasonic beam when, it can be with two kinds of ultrasonic beam of alternate emission, for example, above-mentioned steps S100 includes: step S101, to scanning objective emission multi-focusing ultrasonic beam, to obtain the image data for rebuilding ultrasound image.Step S102, along one or more launch angles to the scanning multiple plane ultrasonic wave beam of objective emission, to obtain calculating speed Vector Message Image data.However, it is possible to be inserted into the process to scanning objective emission focused ultrasound beams during to scanning objective emission plane ultrasonic wave beam.For example, during being uniformly inserted into execution above-mentioned steps S102 to the multi-focusing ultrasonic beam of scanning objective emission.Or it is also possible that and above-mentioned at least part to the scanning multiple plane ultrasonic wave beam of objective emission and the above-mentioned any alternate emission mode for being alternately performed scheme at least part for scanning objective emission multi-focusing ultrasonic beam is able to achieve using any one.It can use focused ultrasound beams in the present embodiment and obtain the preferable ultrasound image of quality；And can use the velocity vector information that the high feature of plane ultrasonic wave beam frame per second obtains high real-time, and in order to have better synchronism both on data acquisition, by the way of two kinds of ultrasonic waveform alternate emission.

Reception circuit 4 and Beam synthesis module 5 receive the echo of the ultrasonic beam of above-mentioned transmitting, obtain ultrasonic signal after carrying out Beam synthesis.For example, working as the echo of collectiong focusing ultrasonic beam, then focusing ultrasonic signal is obtained；When the echo of receiving plane ultrasonic beam, then planar ultrasonic wave signal is obtained, and so on.Emit what type of ultrasonic beam in the step s 100, then the corresponding echo for receiving what type of ultrasonic beam, generates the ultrasonic signal of corresponding types.For example, focused ultrasound beams are corresponding to focus ultrasonic signal, plane ultrasonic wave beam corresponding flat ultrasonic signal, the corresponding diverging ultrasonic signal of diverging ultrasonic beam etc., do not enumerate one by one herein.

When receiving the echo of the ultrasonic beam of circuit 4 and the reception above-mentioned steps S100 transmitting of Beam synthesis module 5, the each array element or every part array element timesharing that can use in the array element for participating in ultrasonic wave transmitting realize the echo that the ultrasonic beam emitted in above-mentioned steps S100 is received when transmitting and receive capabilities, the array element on probe is either divided into receiving portion and emitting portion, then utilizes echo of ultrasonic beam emitted in each array element participated in the received array element of ultrasonic wave or every part array element reception above-mentioned steps S100, etc..

When emitting ultrasonic beam in a launch angle in the step s 100, the echo of the ultrasonic beam from the launch angle is received, it is corresponding to obtain one group of ultrasonic signal.When emitting ultrasonic beam in multiple launch angles in the step s 100, the echo of the corresponding ultrasonic beam for receiving multiple launch angles obtains the multiple groups ultrasonic signal for corresponding to multiple launch angles.Based on different launch angles, the multiple groups ultrasonic signal corresponding to different launch angles can receive.In addition, one group of ultrasonic signal includes repeated ultrasonic wave signal, repeated ultrasonic wave signal can correspond to receive the multiecho signal of the repeated ultrasonic wave beam emitted in each launch angle, wherein the transmitting of a ultrasonic beam is corresponding to obtain a ultrasonic signal.Such as, in the step s 100 along multiple and different launch angles respectively to the scanning multiple plane ultrasonic wave beam of objective emission, the echo of the corresponding plane ultrasonic wave beam of above-mentioned multiple launch angles is then received respectively, obtain the multiple groups planar ultrasonic wave signal for belonging to different launch angles, wherein every group of planar ultrasonic wave signal includes planar ultrasonic wave signal at least twice, and each planar ultrasonic wave signal, which is originated from, to be executed once in a launch angle to echo obtained the step of scanning objective emission ultrasonic beam.In another example for scanning objective emission multi-focusing ultrasonic beam, then receiving the echo of above-mentioned focused ultrasound beams in step S100, obtaining multi-focusing ultrasonic signal.

2, along different receiving angles from scanning the multiple angles of intended recipient ultrasonic signal.

When 2 incentive probe 1 of transmit circuit in the step s 100 along one or more launch angles to scanning objective emission ultrasonic beam when, the aperture location of the reception array element on adjusting probe can be passed through, to receive the echo of the ultrasonic beam from scanning target, obtain the ultrasonic signal along different receiving angles, as the ultrasonic signal for the different angle for receiving acquisition in step S100, for details, reference can be made to shown in Fig. 4 and related description.Along multiple launch angles to scanning objective emission ultrasonic beam process referring to related description above.

Such as, in one of the embodiments, in the step s 100, when reception carrys out the echo of ultrasonic beam in self-scanning target, the aperture location that array element is received in probe is then adjusted to first position, for receiving the echo of the ultrasonic beam of the launch angle, obtain first group of ultrasonic signal for belonging to the first receiving angle, the aperture adjustment of array element will be received to the second position, for receiving the echo of the ultrasonic beam of the launch angle, obtain second group of ultrasonic signal for belonging to the second receiving angle, similarly, to obtain multiple groups ultrasonic signal based on different receiving angles.

Referring to above along the execution sequence and rule of multiple launch angles, in the above-described embodiments along different receiving angles from scanning the multiple angles of intended recipient ultrasonic signal during, the receive process of multiple groups ultrasonic signal can also be alternately performed according to the difference of receiving angle.In one of the embodiments, 2 incentive probe 1 of transmit circuit to scanning objective emission ultrasonic beam, the echo for dividing multiple and different receiving angles to receive the ultrasonic beam respectively, obtain the ultrasonic signal that multiple groups adhere to different receiving angles separately, wherein along a receiving angle from the corresponding echo-signal for receiving one group of ultrasonic beam of scanning target, for subsequent Beam synthesis, the calculating of the processing of ultrasound image data and blood flow velocity vector.Along multiple receiving angles respectively from the echo of scanning intended recipient multiple groups ultrasonic beam.Such as, in the step s 100 to scanning objective emission plane ultrasonic wave beam, the echo of ultrasonic beam is repeatedly received along a receiving angle, obtain one group of planar ultrasonic wave signal, it include multiple planar ultrasonic wave signal in this group of planar ultrasonic wave signal, the echo of multiple groups plane ultrasonic wave beam is received along different receiving angles, to obtain the multiple groups planar ultrasonic wave signal for adhering to different receiving angles separately.

3, the ultrasonic signal obtained based on a launch angle or a receiving angle also with the maximum value for calculating blood flow velocity in subsequent step and can also obtain ultrasound image.Such as, in the step s 100 along a launch angle to scanning objective emission plane ultrasonic wave beam, the echo of ultrasonic beam is then repeatedly received along a receiving angle, obtains one group of plane ultrasonic echo-signal, includes multiple plane ultrasonic echo-signal in this group of plane ultrasonic echo-signal.It may be replaced by other above-mentioned ultrasonic waveforms in this certain embodiment.

Based on the adjustment launch angle or adjustment receiving angle being noted above, the ultrasonic signal along an angle or multiple angles can be obtained in the step s 100, angle herein may include launch angle or receiving angle.One group of ultrasonic signal of acquisition corresponding with a launch angle or receiving angle, corresponding different launch angle or receiving angle can obtain multiple groups ultrasonic signal, include the ultrasonic signal obtained at least once along launch angle or receiving angle in each group of ultrasonic signal.According to the combination of wherein any one group of ultrasonic signal or ultrasonic signal more than two, at least part of ultrasound image of available scanning target.In addition, Based on any one or two or more sets of combination in multiple groups ultrasonic signal, the blood flow velocity of target point in available area-of-interest.

In the step s 100, facilitate for ease of calculation, with promotion image display effect, in the ultrasonic signal for obtaining multiple angles in scanning target by probe, the ultrasonic signal of multiple angles belongs to different receiving angle or launch angle, according to the corresponding different angle of super wave signal, it is stored as at least one set of data frame collection relevant to angle.One group of ultrasonic signal of above-mentioned acquisition is namely stored as one group of data frame collection relevant to angle, it includes an at least frame image data that data frame, which is concentrated,.

In step s 200, image processing module 7 obtains the blood flow velocity in scanning target in vascular according to the ultrasonic signal obtained in step S100.

The corresponding blood flow velocity direction of all target points in the entire imaging region of scanning target can be first calculated in step S200, then according to the acquisition of concern position, then extracted corresponding blood flow velocity and carried out display processing.Alternatively, concern position can also first be determined, ultrasound image is then obtained to calculate blood flow velocity related with concern position, is handled for subsequent display.

Blood flow velocity can be specific as follows shown by a variety of calculations.

The first, calculates blood flow velocity using Doppler mapping technology.

Firstly, obtaining ultrasonic signal according to mode described previously, this ultrasonic signal can be the ultrasonic signal for adhering to one or more angles separately.This angle can be launch angle or receiving angle.Following embodiment is, to scanning objective emission ultrasonic beam, and to receive the echo-signal of the ultrasonic beam as being illustrated for the ultrasonic signal in step S100 along one or more launch angles.In doppler imaging method, continuously emit repeated ultrasonic wave beam in same launch angle for scanning target；The echo of the repeated ultrasonic wave beam of transmitting is received, obtains repeated ultrasonic echo-signal, each value has corresponded to the value when being scanned in a launch angle on a target position in ultrasound echo signal each time.

Then, it is calculated in the following way in step s 200:

Repeated ultrasonic wave signal in one group of ultrasonic signal is done into Hilbert transformation along the direction where launch angle respectively, obtains the multiple images data using each target point upper value of complex representation；After n times transmitting receives, just there are N number of complex values along time change on each target point, then, calculate velocity magnitude of the target point z on launch angle direction according to following two formula (1) and (2):

Wherein, V_zIt is the velocity amplitude along launch angle calculated, c is the velocity of sound, f₀It is the centre frequency of probe, T_prfIt is the time interval between twice emitting, N is the number of transmitting, and x (i) is the real part in i-th transmitting, and y (i) is the imaginary part in i-th transmitting,To take imaginary-part operator,To take real part operator.Above formula (1) and (2) are the calculation formula of velocity amplitude on a fixed position.

Secondly, and so on, the velocity amplitude on each target point can be found out by this N number of complex values.

If calculating the blood flow velocity in step S200 using the above method, doppler velocity value V can be taken_zThe blood flow velocity on target point is characterized, can also be taken comprising doppler velocity value V_zVelocity amplitude, the vector expression way that directional velocity is launch angle on characterization target point characterize the blood flow velocity on target point.The form of expression of blood flow velocity can be unlimited, and the blood flow velocity component on the angle direction obtained using Doppler mapping technology is provided in certain above-described embodiment.

The launch angle used in the above-described embodiments is as embodiment, if obtaining repeated ultrasonic echo-signal along receiving angle using what is be noted above, it can also then be calculated using aforesaid way, but launch angle hereinbefore then replaces with receiving angle, directional velocity is then receiving angle.

It can obtain respectively in different angle as the velocity amplitude on directional velocity according to the ultrasonic signal of different angle using above-mentioned Doppler's calculation, doppler velocity value can be referred to as herein, this doppler velocity value can be characterized with Doppler frequency.In addition, doppler velocity value can also be showed with the form of Doppler frequency spectrum.

In general, using doppler principle, carrying out doppler processing in ultrasonic imaging to ultrasonic signal, the movement velocity of scanning target or the motion parts in it can be obtained.For example, by autocorrelation estimation method, perhaps crosscorrelation estimation method can obtain the movement velocity of scanning target or the motion parts in it according to ultrasonic signal after obtaining ultrasonic signal.To ultrasonic signal carry out doppler processing with the method for obtaining the movement velocity of scanning target or the motion parts in it can be used it is currently in use in this field or may using in the future it is any can method to calculate speed in the movement for scanning target or the motion parts in it by ultrasonic signal, this will not be detailed here.

Second, the mode based on speckle tracking calculates the blood flow velocity for obtaining target point in area-of-interest using the offset of same blob between two field pictures to obtain.Shown in specific as follows.

Firstly, obtaining ultrasonic signal according to mode described previously, this ultrasonic signal may include at least one set of ultrasonic signal.

Secondly, obtaining at least two frame ultrasound images, such as obtain at least first frame ultrasound image and the second frame ultrasound image according to the ultrasonic signal.As it was noted above, the ultrasound image for calculating the blood flow velocity of target point can be obtained in the present embodiment using plane ultrasonic echo-signal.Plane ultrasonic wave beam is generally propagated in entire imaging region, therefore, in general, the corresponding collimated beam of sound echo-signal obtained of the plane ultrasonic wave beam once emitted can be obtained a frame collimated beam of sound echo image data by processing.It herein, will be to planar ultrasonic wave The corresponding collimated beam of sound echo-signal obtained of beam perform corresponding processing and the ultrasound image data of scanning target that obtains referred to as " collimated beam of sound echo ".

Then, tracing area is selected in first frame ultrasound image, which may include the target point for wishing to obtain its velocity vector.For example, tracing area can choose some neighborhood of target point or some data block comprising target point.

Secondly, region corresponding with the tracing area is searched in the second frame ultrasound image, for example, search has the region of maximum comparability as tracking result region with tracing area above-mentioned.Here, the metrics process of similitude can find similar matrix using following formula, and the region for having maximum comparability with tracing area above-mentioned is found based on similar matrix.

Similar matrix is calculated using following formula (3) or (4) in two dimensional image.

Wherein, X₁For first frame ultrasound image, X₂For the second frame ultrasound image.I and j is the transverse and longitudinal coordinate of two dimensional image.When indicating that the formula calculated result on the right of it reaches minimum, the value of K and L.The then position new in representative image K, L.M, N are the size of tracing area in figure.WithIt is the average value in first frame and the second frame tracing area and tracking result region.

Similar matrix is calculated using following formula (5) or (6) in 3-D image.

Wherein, X₁For first frame ultrasound image, X₂For the second frame ultrasound image.I, j and k are the coordinates of 3-D image.When indicating that the formula calculated result on the right of it reaches minimum, A, B, the value of C.The then transverse and longitudinal coordinate position new in representative image A, B, C.M, N, L are the size of tracing area in figure.WithIt is the average value in first frame and the second frame tracing area and tracking result region.

Finally, can be obtained the velocity vector of the target point according to the time interval between tracing area above-mentioned and the position and the first frame image data and the second frame image data in tracking result region above-mentioned.For example, velocity amplitude can by the distance between tracing area and tracking result region (i.e. the moving displacement of target point within a preset time interval), divided by first frame collimated beam of sound echo image data and the second frame collimated beam of sound echo Time interval between data obtains, and directional velocity can be for from tracing area to the direction of the line in tracking result region, the i.e. moving direction of target point within a preset time interval.

In addition, can also carry out wall filtering processing before carrying out speed calculating at least two frame ultrasound images of acquisition, exactly do wall filtering respectively along time orientation for the point on position each on image.Tissue signal on image changes over time smaller, and blood flow signal is then changed greatly due to the flowing of blood flow.Therefore wall filter of the high-pass filter as blood flow signal can be used.After wall filtering, the biggish blood flow signal of frequency is remained, and the lesser tissue signal of frequency will be cut.The signal-to-noise ratio of signal after wall filtering, blood flow signal can greatly enhance.

Based on the above method, the absolute value for the velocity vector that the blood flow velocity in step S200 can obtain for the above method, or be velocity vector.

The third, it is specific as follows shown based on the velocity vector of time gradient and spatial gradient acquisition target point at target point.

Firstly, obtaining ultrasonic signal according to mode described previously, this ultrasonic signal may include at least one set of ultrasonic signal.This ultrasonic signal can be the ultrasound echo signal for adhering to one or more angles separately.This angle can be launch angle or receiving angle, and following embodiment illustrates by taking launch angle as an example.

Secondly, obtaining at least two frame ultrasound images according to ultrasonic signal；

Then, it is obtained at target point according to ultrasound image along the first gradient of time orientation, it is obtained at target point according to ultrasound image along the second gradient of launch angle, the 5th velocity component in launch angle and the 6th velocity component on the direction perpendicular to launch angle for, along the 3rd gradient in the direction perpendicular to launch angle, target point being calculated according to first gradient, the second gradient and 3rd gradient at target point are obtained according to ultrasound image；

Secondly, obtaining the velocity vector of target point according to the 5th velocity component and the synthesis of the 6th velocity component, including the velocity amplitude and synthetic degree of angle obtained after synthesis, synthetic degree of angle is directed toward directional velocity.

The launch angle used in the above-described embodiments is as embodiment, if at least two frame ultrasound images obtain repeated ultrasonic echo-signal along receiving angle using what is be noted above, it can also then be calculated using aforesaid way, but " launch angle " in each step should be replaced by receiving angle.The above process carries out calculating the calculating speed and accuracy that can promote velocity vector using plane ultrasonic echo-signal in one of the embodiments,.Based on the above method, the absolute value for the velocity vector that the blood flow velocity in step S200 can obtain for the above method, or be velocity vector.

4th kind, based on the data frame collection for adhering to different angle separately, association obtains the velocity component along multiple and different angles at target point；Velocity component relevant to multiple and different angles is synthesized, the velocity vector at the target point is obtained.For example, can use Doppler mapping technology to calculate along the velocity component of multiple angles at target point, then synthesis obtains the velocity vector of target point.It is specifically as follows.

Firstly, obtaining at least two groups ultrasonic signal according to mode described previously, at least two groups ultrasonic signal can be the ultrasonic signal for adhering to multiple launch angles or receiving angle separately, and following embodiment illustrates by taking launch angle as an example.

Secondly, referring to the calculating process for utilizing Doppler mapping technology above, calculating separately the corresponding velocity component of each group of data frame collection based on the data frame collection for adhering to different angle separately, obtaining at least two velocity components relevant to the angle.At least two velocity components are obtained at each target point.Each velocity component may include with the velocity amplitude on doppler velocity value characterization target point, and corresponding launch angle characterizes the directional velocity on target point；It can also only include with the velocity amplitude on doppler velocity value characterization target point.

Then, according to the variation sequence of time at obtaining the velocity vector of target point, including the velocity amplitude and synthetic degree of angle obtained after synthesis, synthetic degree of angle is directed toward directional velocity when at least two velocity component corresponding at target point being carried out speed contract.

The launch angle used in the above-described embodiments is as embodiment, if obtaining multiple groups ultrasound echo signal along multiple receiving angles using what is be noted above, it can also then be calculated using aforesaid way, but " launch angle " in each step should be replaced by " receiving angle ".

Certainly it is directed to the corresponding ultrasound echo signal of a launch angle, the present embodiment is not limited to the above method, can also use other as is generally known in the art or the following method that may be used.Ultrasound image referred to herein can be two-dimensional image data, be also possible to the 3 d image data of multiple two-dimensional image data compositions, hereafter together.

The calculation for hereinbefore having been presented for a variety of velocity amplitudes in relation to blood flow or velocity vector may be incorporated for the blood flow velocity of the target point in estimating step S200, the blood flow velocity calculated in step S200 herein can be a velocity amplitude, it is also possible to a velocity vector, velocity vector includes velocity amplitude and directional velocity.If the blood flow velocity in step S200 is a velocity amplitude, it can then be indicated with Doppler frequency, Doppler frequency spectrum, or velocity amplitude in velocity vector information can also be taken, this velocity amplitude can be the absolute value or other value forms of expression of velocity vector.If the blood flow velocity in step S200 is a velocity vector, blood flow velocity, which may is that, characterizes velocity amplitude, the velocity vector of receiving angle or launch angle characterization directional velocity with Doppler frequency；It can also be by modes such as multi-angle velocity composite, multi-angle Spectrum synthesizing or SPECKLE TRACKINGs come approximate calculation velocity vector.Velocity amplitude can be the one of which in the statistic of approximation or true velocity size, acceleration magnitude, velocity variance assessed value of target point etc. characterization speed state in blood flow velocity.Directional velocity above can be launch angle mentioned above or receiving angle, alternatively, the directional velocity obtained when calculating speed vector or the synthetic degree of angle for carrying out acquisition when composite calulation.

In addition, the corresponding blood flow velocity of the target point that acquisition is calculated in step S200 may include one or more velocity amplitudes, it also may include one or more velocity vectors.

The target point of the present embodiment can be interested point or position in scanning target, be usually expressed as, at least part ultrasound image of the scanning target shown over the display, the sense that can be labeled or can be demonstrated The point of interest or position.Such as, target point can be the pixel or pixel region that user inputs in the region of interest, it is also possible to the multiple discrete pixels points or pixel region of system automatically generated in area-of-interest, for determining the relative position for calculating blood flow velocity at some pixel or certain block neighborhood of pixels block image coordinate.

Target point in step S200 can be multiple pixels that user inputs in the region of interest or neighborhood of pixels (data block), it is also possible to the multiple discrete pixels points or neighborhood of pixels (data block) of system automatically generated in area-of-interest, or can also be all pixels point or neighborhood of pixels (data block) in area-of-interest.

The area-of-interest being mentioned herein, the region or entire imaging region that the system that can be is formed on the ultrasound image automatically, or can also be that user inputs selection instruction on the ultrasound image and obtains region, etc..At least one pixel of usual area-of-interest, or include at least one pixel neighborhood of a point (data block).

The blood flow velocity of each target point in multiple semi-cylindrical hills in vascular can be calculated in step s 200, and this multiple semi-cylindrical hills can mutually include.For example, step S200 is further comprising the steps of in wherein some embodiments:

Firstly, obtaining the blood flow velocity of multiple target points in the first area-of-interest；

Secondly, obtaining the blood flow velocity of multiple target points in the second area-of-interest.

Further, the first perceptual region can be the region or entire imaging region that system is formed on the ultrasound image automatically, or can also be that user inputs selection instruction on the ultrasound image and obtains region, etc..It includes subregion in the first area-of-interest, or the area-of-interest for partially overlapping with the first area-of-interest or not being overlapped completely that second area-of-interest, which can be,.

In wherein some embodiments, if the first perceptual region is entire imaging region, second area-of-interest is included in the subregion in the first area-of-interest, so, the blood flow velocity of each target point in entire imaging region can be first calculated, the blood flow velocity of multiple target points in the first area-of-interest and the second area-of-interest is then extracted according to selected area-of-interest.The blood flow velocity for extracting two area-of-interests or more than two area-of-interests is compared, and can show the movement velocity curve spectrum in two regional scopes of comparison simultaneously, such as shows the maximum movement speed curve spectrum in two regional scopes of comparison simultaneously.

In step S300, image processing module 7 obtains at least part of ultrasound image of scanning target according to above-mentioned ultrasonic signal.

The ultrasound image of this paper can be three-D ultrasonic stereo-picture, it is also possible to two-dimensional ultrasonic image, such as B figure, to the image in the three dimensional ultrasonic image data library obtained by above-mentioned sweep volume that shows, or pass through the enhanced B image of two-dimentional blood flow display technology acquisition.

In one embodiment of the present embodiment, the imaging of plane ultrasonic wave beam is can be used in ultrasound image, and focused ultrasound beams imaging also can be used.But since the ability that focused ultrasound beams emit every time is relatively concentrated, and it is only imaged in capability set, therefore the echo-signal signal-to-noise ratio obtained is high, the ultrasonograph quality of acquisition is preferable, and the main lobe of focused ultrasound beams is narrow, secondary lobe is lower, and the lateral resolution of the ultrasound image of acquisition is also higher.

So focused ultrasound beams imaging can be used in ultrasound image in one embodiment of the present embodiment.While in order to obtain the ultrasound image of more high quality, multiple transmitting focusing ultrasonic beam can be emitted, in the step s 100 to realize that scanning obtains a frame ultrasound image.

In one embodiment of the present embodiment, to scanning objective emission multi-focusing ultrasonic beam in above-mentioned steps S100, and the echo of collectiong focusing ultrasonic beam in step s 200, one group of focus beam echo-signal is obtained, at least part of ultrasound image of scanning target is obtained according to the focus beam echo-signal.The ultrasound image of high quality can be obtained using ultrasonic wave is focused.Combination emission process in relation to plane ultrasonic wave beam and focused ultrasound beams is referring to aforementioned related content.

In step S400, image processing module 7 obtains the concern position being located in vascular.

Concern position in the present embodiment can be cursor position, the combination one of in the position where user's selected location and blood flow velocity maximum value or both.In addition, concern position may include one, it also may include multiple.A concern position in the present embodiment can be an area-of-interest, if an area-of-interest, then the blood flow velocity of the concern position can be one of them in area-of-interest in the mean value of multiple target point Hemodynamic environment angle value, variance, mean square deviation, maximum value and minimum value.Alternatively, a concern position can also be equal to a target point.In addition, concern position can also be any one target point in area-of-interest, or selected target point (such as position where user's selected location, blood flow velocity maximum value).

According to determining concern position, execute the process of step S500 to step S600, the associated coordinates system of speed and time are drawn in viewing area using display, in the associated coordinates system, the variation that the value of blood flow velocity at the concern position is shown according to the variation sequence of time obtains movement velocity curve spectrum associated with the concern position.In above process, it can be changed with time using image processing module recording blood flow velocity at the concern position, be cached in advance, then pass through the content that display shows step S500 and step S600 again.

Associated coordinates system in relation to speed and time can be found in the coordinate system of attached drawing 11, Figure 12 and Figure 13 and Figure 14, Figure 15 and the movement velocity curve spectrum in Figure 17.

In wherein some embodiments, referring to attached drawing 17, if paying close attention to position includes at least two, in so above-mentioned steps S600, under the same associated coordinates system, the variation for showing the value of blood flow velocity at least two concern position according to the variation sequence of time simultaneously obtains movement velocity curve associated at least two concern position respectively.In the present embodiment, it also can use image processing module and record blood flow velocity at least two concern positions at the same time and change with time, cached, then pass through the content that display shows step S500 and step S600 again.

Concern position in above-described embodiment can be cursor position and user's selected location.It is of course also possible to include area-of-interest 92 and area-of-interest 95, cursor position 97, vascular 93 in ultrasound image 91 as shown in figure 17.Above-mentioned concern position includes the position 94 where the peak veloity,PV in area-of-interest 92, Position 96 and cursor position 97 where peak veloity,PV in area-of-interest 95.Therefore, it obtains respectively and pays close attention to position 97 with above three, 96,94 associated movement velocity curve combinings are in a coordinate system, the movement velocity curve 98 in Figure 17 is formed, wherein the curve 981,982 drawn, 983 are respectively associated above three concern position 97,96,94.In addition, not limiting centainly in the multiple concern positions obtained in further above-mentioned steps S400 comprising the position where peak veloity,PV, can also be comprising any one position in cursor position and at least one area-of-interest.It can also be as shown in the movement velocity curve 98 in Figure 17 according to the result that above-mentioned steps S500 and step S600 is formed.

In wherein some embodiments, as shown in fig. 6, the concern position in step S400 includes the position where peak veloity,PV.Therefore, it also needs to increase following steps in step S400:

Step S410, image processing module 7 search the maximum value in blood flow velocity,

Step S420, image processing module 7 determine the concern position according to the position where the maximum value.Part concern position can be according to the concern position that the position where the maximum value determines in the step s 420, based on this, determine that at least one concern position is the position where the maximum value in the step s 420, and simultaneously also comprising other concern positions, other any positions that concern position can be cursor position or user selectes, so as shown in figure 17, the blood flow velocity variation of the position and cursor position where showing maximum value can be compared simultaneously.

Below by search the maximum value in blood flow velocity determine concern position for, illustrated as follows.

In above-mentioned steps S600, image processing module 7 is in associated coordinates system, the variation of the value of the blood flow velocity at the position where the maximum value is shown according to the variation sequence of time, obtain movement velocity curve spectrum associated with the position where the maximum value, to generate maximum movement speed curve spectrum, the maximum movement speed curve spectrum records the corresponding blood flow velocity of blood flow velocity maximum value position and the corresponding relationship between the time.

For the method that image processing module 7 in step S410 searches the maximum value in blood flow velocity, reference can be made to hereafter explaining in detail.

For the blood flow velocity of the step S200 target point obtained, the maximum value obtained in blood flow velocity can be compared frame by frame, can also be compared with multiframe.For details, reference can be made to be detailed below.

The first, in step S410 using it is following compare frame by frame by the way of.

Firstly, multiple target points are in current time corresponding blood flow velocity in extraction area-of-interest；Then, compare blood flow velocity in current time, determine maximum value；Secondly, the target point where the maximum value in blood flow velocity when current time is considered as the first concern position；Finally, in movement velocity curve spectrum, the value of the corresponding blood flow velocity in association display first concern position, obtains maximum movement speed curve spectrum at the position where current time when executing step S600.

Shown in Figure 7, usual one or many ultrasound echo signals can obtain a frame ultrasound image, every frame Ultrasound image corresponds to an acquisition moment.Firstly, extracting the blood flow velocity of multiple target points in area-of-interest in every frame ultrasound image (such as T1, T2, T3, T4).Such as, corresponding multiple target point A in T1 frame image, B, C, the blood flow velocity of D is respectively v1-1, v1-2, v1-3, v1-4, corresponding multiple target point A in T2 frame image, B, C, the blood flow velocity of D is respectively v2-1, v2-2, v2-3, v2-4, corresponding multiple target point A in T3 frame image, B, C, the blood flow velocity of D is respectively v3-1, v3-2, v3-3, v3-4, corresponding multiple target point A in T4 frame image, B, C, the blood flow velocity of D is respectively v4-1, v4-2, v4-3, v4-4, the blood flow velocity used herein can be velocity amplitude, it is also possible to velocity vector.Then, the blood flow velocity of each target point in ultrasound image is compared frame by frame, the maximum value of blood flow velocity in area-of-interest in every frame ultrasound image is extracted, such as the blood flow velocity maximum value in T1, T2, T3, T4 frame image is respectively v1-1, v2-2, v3-3, v4-2.Secondly, target point where the maximum value searched in area-of-interest in every frame ultrasound image is considered as the first concern position, that is v1-1, v2-2, v3-3, v4-2 target point A, B, C, B in T1, T2, T3, T4 frame image respectively, is considered as the first concern position.Finally, in maximum movement speed curve spectrum, establish the corresponding relationship between blood flow velocity and time variable, and t1, t2, t3, t4 at the time of T1, T2, T3, T4 frame image respectively correspond in maximum movement speed curve spectrum, corresponding record v1-1, v2-2, v3-3, v4-2.Certainly, here v1-1, v2-2, v3-3, v4-2 can be indicated with Doppler frequency or Doppler frequency spectrum, each moment is by the corresponding Doppler frequency of corresponding record maximum value or Doppler frequency spectrum so in maximum movement speed curve spectrum, to form a kind of new profile information that can be always ensured that display maximum position speed.When using Doppler frequency spectrum to be compared, the comparison of maximum value can be carried out by taking the envelope of Doppler frequency spectrum.

It is second, shown in Figure 8, in step S410 by the way of the comparison of following multiframe.

Firstly, extracting in preset time period in area-of-interest multiple target points corresponding blood flow velocity at various moments, wherein according to the ultrasonic signal, calculate in preset time period in area-of-interest each target point corresponding blood flow velocity at various moments.For example, usually one or many ultrasound echo signals can obtain a frame ultrasound image, every frame ultrasound image corresponding acquisition moment.Extract the blood flow velocity of multiple target points in area-of-interest in multiple frames of ultrasonic image (such as T11, T12, T13, T14).Such as, corresponding multiple target point A1 in T11 frame image, B1, C1, the blood flow velocity of D1 is respectively v11-1, v11-2, v11-3, v11-4, corresponding multiple target point A1 in T12 frame image, B1, C1, the blood flow velocity of D1 is respectively v12-1, v12-2, v12-3, v12-4, corresponding multiple target point A1 in T13 frame image, B1, C1, the blood flow velocity of D1 is respectively v13-1, v13-2, v13-3, v13-4, corresponding multiple target point A1 in T14 frame image, B1, C1, the blood flow velocity of D1 is respectively v14-1, v14-2, v14-3, v14-4, the blood flow velocity used herein can be velocity amplitude, it is also possible to speed Spend vector.Multiple frames of ultrasonic image in the present embodiment can be continuous multiple image, be also possible to discrete multiple image.

Then, compare the corresponding blood flow velocity of each moment in preset time period, determine blood flow in preset time period The maximum value of speed.For example, comparing the blood flow velocity in multiple frames of ultrasonic image (such as T11, T12, T13, T14), maximum value is searched, maximum value at least meets one of following rule:

1, the corresponding target point of maximum value within a preset period of time each moment when blood flow velocity be maximum.Such as, the v11-1 > v11-2 > v11-3 > v11-4 in T11 frame image, the v12-1 > v12-2 > v12-3 > v12-4 in T12 frame image, the v13-1 > v13-2 > v13-3 > v13-4 in T13 frame image, the v14-1 > v14-2 > v14-3 > v14-4 in T14 frame image, then maximum value is respectively v11-1, v12-1, v13-1 and v14-1, i.e. target point A1 at various moments on blood flow velocity.

2, maximum value is the maximum value in moment each in preset time period corresponding blood flow velocity.For example,

V11-1 > v11-2 > v11-3 > v11-4 > v13-1 > v13-2 > v13-3 > v13-4 > v14-1 > v14-2 > v14-3 > v14-4 > v12-1 > v12-2 > v12-3 > v12-4

Then, the maximum value of each moment corresponding blood flow velocity is v11-1 in preset time period, and the corresponding target point of maximum value is A1.

Secondly, the target point where the maximum value found is considered as the second concern position, i.e. the position in T11, T12, T13, T14 frame image is target point A1.

Finally, in movement velocity curve spectrum, being located in preset time period when executing step S600 and being associated with display second concern position corresponding blood flow velocity within a preset period of time, obtain maximum movement speed curve spectrum.

In maximum movement speed curve spectrum, establish the corresponding relationship between the blood flow velocity and time variable of target point A1, t11, t12, t13, t14 at the time of T11, T12, T13, T14 frame image respectively correspond in maximum movement speed curve spectrum, corresponding record v11-1, v12-1, v13-1, v14-1.Certainly, v11-1, v12-1, v13-1, v14-1 here can be indicated with Doppler frequency, be shown in the maximum movement speed curve spectrum then extracting the corresponding Doppler frequency spectrum of target point A in preset time period.

Further, extract in next preset time period in area-of-interest multiple target points corresponding blood flow velocity at various moments, such as corresponding multiple target point A1 in T15 frame image, B1, C1, the blood flow velocity of D1 is respectively v15-1, v15-2, v15-3, v15-4, corresponding multiple target point A1 in T16 frame image, B1, C1, the blood flow velocity of D1 is respectively v16-1, v16-2, v16-3, v16-4, corresponding multiple target point A1 in T17 frame image, B1, C1, the blood flow velocity of D1 is respectively v17-1, v17-2, v17-3, v17-4, corresponding multiple target point A1 in T18 frame image, B1, C1, the blood flow velocity of D1 is respectively v18-1 , v18-2, v18-3, v18-4.Then, it is determined that in preset time period blood flow velocity maximum value.For example, v12-3 is the maximum value in above-mentioned all blood flow velocity of each moment.The target point where the maximum value v12-3 found is so considered as the second concern position, i.e. the position in T15, T16, T17, T18 frame image is target point B1.Finally, in maximum movement speed curve spectrum, t15, t16, t17, t18 at the time of T15, T16, T17, T18 frame image respectively correspond in maximum movement speed curve spectrum, corresponding record v15-2, v16-2, v17-2, v18-2, the i.e. corresponding blood flow velocity of target point B1.

If above-mentioned blood flow velocity Doppler frequency or Doppler frequency spectrum indicate, each moment is by the Doppler frequency or Doppler frequency spectrum of blood flow velocity maximum value position in corresponding record certain time period so in maximum movement speed curve spectrum, to form a kind of new profile information that can be always ensured that display maximum position speed.

When searching the maximum value in blood flow velocity in step S410, if blood flow velocity uses velocity vector, acquisition maximum value can be compared using the absolute value of velocity vector.Preset time period in above-described embodiment can be the self defined time section perhaps time interval etc. of the period of systemic presupposition or user before from selected area-of-interest to change area-of-interest.When user changes the position that area-of-interest will then reaffirm concern position in the way of Fig. 9.

No matter which kind of above-mentioned situation, each moment corresponding concern position can immobilize within a preset period of time in maximum speed movement spectrum, can also at any time the variation of variable and change, therefore, create that newly generated maximum speed movement spectrum included in the present embodiment is not the corresponding velocity information in concern position, can be the corresponding velocity information in many concern positions, and these pay close attention to positions can be identical, can not also be identical, it is related to the maximum value of blood flow velocity.In one of the embodiments, above-mentioned preset time period is greater than or equal to a cardiac cycle, when using the second way, the tracking of maximum value may be implemented within a cardiac cycle, and one second concern position is obtained, to show the situation of change of blood flow velocity maximum value in continuous multiple cardiac cycles one by one in maximum speed movement spectrum.

There may be the rest periods when carrying out maximum value search within a preset period of time can use historical data continuously to search maximum value, shown in text specific as follows for the counting accuracy and continuity for improving maximum speed movement spectrum.In above-mentioned steps S100, it obtains current slot and corresponds to received ultrasonic signal, in above-mentioned steps S200, extract the corresponding ultrasound echo signal of historical time section, current slot and the corresponding ultrasound echo signal of historical time section are combined, the ultrasound echo signal in preset time period is obtained；Then it according to the ultrasound echo signal in preset time period, calculates in preset time period the corresponding blood flow velocity of each target point in area-of-interest, and searches the maximum value of blood flow velocity according to the method described above according to these results.

Furthermore, ultrasonic signal based on an angle, calculate the process for obtaining blood flow velocity, maximum value can be searched using the above method, and the ultrasonic signal based on multiple angles obtains velocity component of the target point in multiple angles respectively, when velocity component based on multiple angles searches the maximum value of blood flow velocity, aforementioned maximum value can be determined using one of following two mode.

It is shown in Figure 9, step S110 is executed in the step s 100, and by receiving circuit 4 and Beam synthesis module 5 from the ultrasonic signal of the scanning multiple angles of intended recipient, the angle includes launch angle or receiving angle；In step s 200, it executes in step S210, ultrasonic signal of the image processing module based on an angle, calculate velocity component of multiple target points in the angle in area-of-interest, according to the ultrasonic signal of the multiple angle, velocity component of the multiple target point respectively in the multiple angle is obtained respectively；Upper Execution step S411 is stated in step S410, according to multiple target points velocity component in multiple angles respectively, searches the maximum value in blood flow velocity.

Such as, in some embodiments of the present embodiment, the velocity component respectively in multiple angles is subjected to velocity fitting in step S210, synthesis obtains the corresponding blood flow velocity vector of multiple target points, searches the maximum value in the blood flow velocity vector to the maximum value in the determination blood flow velocity.If as blood flow velocity being compared extraction maximum value using blood flow velocity vector in step s310, then can use in the present embodiment, and compare frame by frame or mode that multiframe compares carries out the screening of maximum value in conjunction with previously mentioned.It can be obtained by the velocity fitting of multiple angles and be more nearly true blood flow velocity, and carry out the screening of maximum value based on the information, result can be enabled more accurate, the diagnostic message provided is more accurate.

If in step S410, the maximum value in the blood flow velocity vector of above-mentioned synthesis is searched to the maximum value in the determination blood flow velocity, so, the mode according to figure 8 compared frame by frame, each moment corresponding record can be in maximum movement speed curve spectrum, the concern position corresponding blood flow velocity where the maximum value obtained according to blood flow velocity vector.However, the mode that multiframe according to Fig. 9 compares, preset time period corresponding record be can be in maximum movement speed curve spectrum, the blood flow velocity of the concern position where the maximum value obtained according to blood flow velocity vector within a preset period of time.Secondly, the value of the blood flow velocity shown in movement velocity curve spectrum in the present embodiment, can be corresponding Doppler frequency at concern position, be also possible to pay close attention to the velocity amplitude that corresponding blood flow velocity vector is included at position, for example, the absolute value of blood flow velocity vector.

In another example in some embodiments of the present embodiment, more multiple target points speed in multiple angles respectively searches the maximum value in multiple angles in velocity component, to the maximum value in the determination blood flow velocity.If being compared extraction maximum value as blood flow velocity using velocity component in multiple angles in step S410, then can use in the present embodiment, and compare frame by frame or mode that multiframe compares carries out the screening of maximum value in conjunction with previously mentioned.More multiple target points velocity component in multiple angles respectively can also be replaced according to the different of angle in some embodiments of the present embodiment, search the maximum value in multiple angles in velocity component, to the maximum value in extraction rate component, to assess the maximum value of blood flow velocity in current time or preset time period.Although what is compared under this mode is velocity component, but it is more accurate that the maximum position of blood flow velocity can be made to extract as far as possible, the accuracy of diagnostic message offer can't be provided because of transmitting or fixing for receiving angle, from another aspect provides a kind of methods for accurately seeking blood flow velocity maximum position, and convenience of calculation, operand is few, and does not need to increase cost on hardware.

If in step S410, search the maximum value in multiple angles in velocity component, to the maximum value in the determination blood flow velocity, then search the component maximum value in the velocity component, the concern position is determined according to the target point where the component maximum value, the blood flow velocity recorded in maximum movement speed curve spectrum is the velocity component on the concern position in an angle, and an angle is belonging to the component maximum value The corresponding angle of ultrasonic signal.So, the mode according to figure 7 compared frame by frame, each moment corresponding record in maximum movement speed curve spectrum pay close attention on position velocity component in an angle corresponding velocity amplitude at various moments.However, the mode that multiframe according to figure 8 compares, the preset time period corresponding record in maximum movement speed curve spectrum, pay close attention to the velocity amplitude of velocity component within a preset period of time on position in an angle.

Step S500 and step S600 is combined to be illustrated together in the detailed process of interpretation procedure S400 in above-mentioned each embodiment, such as Fig. 6 to 10, its object is to explain the mode in relation to searching blood flow velocity maximum value, but actually, which kind of either go to search the maximum value in blood flow velocity using above-mentioned mode, such as, using blood flow velocity vector, velocity component, the different types of blood flow velocity of doppler velocity value etc. goes to be compared, maximum value has finally been determined, after concern position has been determined according to maximum value, so generating movement velocity curve time spectrum, the corresponding blood flow velocity in concern position of map record can be doppler velocity, velocity amplitude in blood flow velocity vector, one of a variety of blood flow velocity types of velocity amplitude of velocity component etc., and it not necessarily is in step S410 for looking into Look for blood flow velocity when maximum value.Such as, the maximum value in blood flow velocity is determined according to blood flow velocity vector in step S410, after obtaining concern position according to maximum value, maximum movement speed curve time spectrum is being generated, the corresponding relationship between its corresponding doppler velocity in record concern position and time variable can be made.In another example, the maximum value in blood flow velocity is determined according to Doppler frequency in step S410, after obtaining concern position according to maximum value, maximum movement speed curve time spectrum is being generated, the velocity amplitude in its corresponding blood flow velocity vector in record concern position and the corresponding relationship between time variable can be made.Also such as, the maximum value in blood flow velocity is determined according to Doppler frequency in step S410, after obtaining concern position according to maximum value, maximum movement speed curve time spectrum is being generated, the corresponding relationship between its corresponding doppler velocity in record concern position and time variable can be made.As it can be seen that the corresponding blood flow velocity in concern position recorded in maximum movement speed curve spectrum can be consistent with used blood flow velocity when searching maximum value in step S410 in step S600, it can also be inconsistent.Several embodiments will be provided with reference to the accompanying drawings below.

In wherein some embodiments, as shown in fig. 6, in step s 200, image processing module calculates the doppler velocity value of multiple target points in area-of-interest according to the ultrasonic signal；In step S410, image processing module searches the maximum value in the doppler velocity value of the multiple target point, searches maximum value by the way of Fig. 7 or Fig. 8 based on doppler velocity value；In the step s 420, image processing module determines that concern position, the concern position correspond to the target point where the maximum value；In step S600, image processing module is in associated coordinates system, the variation of doppler velocity value at the concern position is shown according to the variation sequence of time, obtain maximum movement speed curve spectrum associated with the concern position, the corresponding relationship between the corresponding doppler velocity value of maximum movement speed curve spectrum record blood flow velocity maximum value and time variable.

In wherein some embodiments, as shown in figure 9, receiving the ultrasonic signal of the multiple angles of acquisition by receiving circuit and Beam synthesis module in step s 110, wherein angle can be launch angle or receiving angle； In step S210, image processing module calculates in area-of-interest multiple target points respectively along the doppler velocity value of multiple angles according to the ultrasonic signals of multiple angles；In step S410, image processing module searches the maximum value in the doppler velocity value of the multiple target point, wherein, velocity fitting is carried out along the doppler velocity value of multiple angles respectively to multiple target points, the corresponding blood flow velocity vector of multiple target points is obtained, blood flow velocity vector is then based on and searches maximum value by the way of Fig. 9 or Figure 10；Alternatively, can also be by the way of Fig. 9 or Figure 10, for more multiple target points respectively along the doppler velocity value of multiple angles, extracting maximum doppler velocity value is maximum value, and determines the corresponding angle of the maximum value.In the step s 420, image processing module determines that concern position, the concern position correspond to the target point where the maximum value；In step S600, image processing module is in associated coordinates system, the variation of doppler velocity value at the concern position is shown according to the variation sequence of time, maximum movement speed curve spectrum associated with the concern position is obtained, the maximum movement speed curve spectrum records corresponding relationship of the concern position between the doppler velocity value and time variable in the corresponding angle of the maximum value.Certainly, the corresponding angle of maximum value can change according to the determination of maximum value here, can also immobilize.

In conclusion maximum value in the blood flow velocity being noted above is included at least with one of Types Below: the maximum value in the Doppler frequency of angle or Doppler frequency spectrum；Maximum value in the Doppler frequency of different angle or Doppler frequency spectrum；For the maximum value being fitted along the Doppler frequency of multiple angles or Doppler frequency spectrum in blood flow velocity vector obtained；With the maximum value in blood flow velocity vector obtained based on adjacent two frame or the calculating of multiple frames of ultrasonic image, wherein the angle ranging from the launch angle of ultrasonic beam or the receiving angle of ultrasound echo signal.Specifically it is referred to the implementation of the detailed process unrestricted choice above method of confession mentioned above.

A variety of methods for calculating blood flow velocity have been noted above, and the blood flow velocity that movement velocity curve is composed in step S600 can also be arbitrarily to select in a manner of any one of the above, therefore, in one of the embodiments, as shown in figure 18, in step s 200, based on ultrasonic signal, the blood flow velocity obtained in the scanning target in vascular includes: at least part based on ultrasonic signal, the first blood flow velocity (step S231) in the scanning target in vascular is obtained according to the first calculation method, at least part based on ultrasonic signal, the second blood flow velocity (step S232) in the scanning target in vascular is obtained according to the second calculation method；Render display first blood flow velocity (step S710) on the ultrasound image using display, in step S600 in movement velocity curve spectrum, the value of the second blood flow velocity changes with time (step S640) at display record concern position.In such a way that display renders show that first blood flow velocity can be found in the rendering for the blood flow projectile figure hereinafter mentioned on the ultrasound image.For example, showing the particle projectile on the ultrasound image, the color coding and/or length of particle projectile are related to the value of the first blood flow velocity of specific location in vascular.

Further, it is based on embodiment shown in fig. 6, in a wherein variant embodiment, in step S410, searches the maximum value in the first blood flow velocity.In the step s 420 according to where the maximum value obtained at this time Position determines concern position.However in the step S600, in movement velocity curve spectrum, the value of the second blood flow velocity changes with time at display record concern position.

First calculation method and the second calculation method can be from hereinbefore in relation to unrestricted choices in the method mentioned in step S200.Certainly, the type of ultrasonic signal used by the calculating of the first blood flow velocity and the second blood flow velocity is not limited in the present embodiment or receives mode yet, such as first the calculating of blood flow velocity and the second blood flow velocity can be based on same group of ultrasonic signal, different groups of ultrasonic signals can also be based on.Further for example, the calculating of the first blood flow velocity and the second blood flow velocity can be based on the ultrasonic signal of same ultrasound in nature, it can also be based on the ultrasonic signal of different ultrasound in nature.Also for example, the first blood flow velocity and calculating for the second blood flow velocity can be based on the super wave signals obtained using different transmittings or reception mode, the ultrasonic signal that identical transmitting or reception mode can also be used to obtain.Therefore, the calculating of first blood flow velocity and the second blood flow velocity uses at least part of the ultrasonic signal obtained in step S100, and obtaining for ultrasonic signal can be using the combination of any one embodiment or multiple embodiments in the explanation above in relation to step S100.Above-mentioned first blood flow velocity can be blood flow velocity vector, and the blood flow velocity vector includes directional velocity and velocity amplitude；Above-mentioned second blood flow velocity also may include: that Doppler frequency, blood flow velocity vector, above-mentioned speed one of are divided in vector.

The above process does not limit the number of area-of-interest namely the method for the present embodiment is equally applicable to that there are in the case where multiple semi-cylindrical hills, can compare maximum movement speed curve spectrum corresponding to blood flow velocity maximum value in display different zones.For example, including: step S211 in step S200 as shown in Figure 10 in some embodiments, the blood flow velocity of multiple target points in the first area-of-interest is obtained according to received ultrasonic signal；Step S212 obtains the blood flow velocity of multiple target points in the second area-of-interest according to received ultrasonic signal.The restriction of first area-of-interest and the second area-of-interest can refer to related area-of-interest above and illustrate.Above-mentioned steps S410 the following steps are included:

Step S413 searches the maximum value of blood flow velocity in the first area-of-interest, obtains first maximum value；

Step S414 searches the maximum value of blood flow velocity in the second area-of-interest, obtains second maximum value；

In one of the embodiments, first area-of-interest is entire sample boxes (ROI), second area-of-interest is customized sample boxes, customized sample boxes are up to system default sample boxes, a minimum target point, customized sample boxes can in system default sample boxes random change location.So, blood flow velocity global maximum of first maximum value for entire sample boxes (ROI), i.e., the maximum value that all positions change over time in entire sample boxes (ROI), this time refer to blood flow imaging duration；Second maximum value is the blood flow velocity local maximum in customized sample boxes, i.e., the maximum value that all positions change over time in customized sample boxes, this time refers to blood flow imaging duration.

In the step s 420, a concern position Q1 (step S421) is obtained according to first maximum value, another concern position Q2 (step S422) is determined according to the second maximum value.

In step S600, in associated coordinates system, a concern position is shown according to the variation sequence of time The variation of the value of blood flow velocity at Q1 obtains movement velocity curve spectrum (step S610) associated with a concern position Q1.In associated coordinates system, the variation of the value of blood flow velocity at another concern position Q2 is shown according to the variation sequence of time, obtains movement velocity curve spectrum (step S620) associated with another concern position Q2.

In step S500, the corresponding relationship between the corresponding blood flow velocity of one concern position Q1 and time variable can also be recorded, to generate maximum movement speed curve spectrum (step S511) corresponding with one concern position Q1.Corresponding relationship between the corresponding blood flow velocity of record another concern position Q2 and time variable, to generate maximum movement speed curve spectrum (step S512) corresponding with another described concern position Q2.

Further, in above process, it can also increase following steps S513: obtain the position where cursor, the corresponding relationship at the position where cursor between blood flow velocity and time variable be recorded, to generate the real time kinematics map at cursor position.In step S600, in associated coordinates system, according to the variation of the value of blood flow velocity at the variation sequence display highlighting position of time, movement velocity curve spectrum (step S630) associated with cursor position is obtained.Purpose is to compare the blood flow velocity at display highlighting position in the maximum movement speed curve spectrum of above-mentioned generation, to obtain more intuitive observation data.The calculation method of blood flow velocity can refer to related description above at cursor position mentioned herein, be not repeated herein.Certain step S513 can also increase in method flow shown in Fig. 7, and the real time kinematics map at cursor position is shown simultaneously with maximum movement speed curve spectrum.

In above-described embodiment, and another described concern position Q2 corresponding maximum movement speed curve spectrum, real time kinematics map corresponding with the associated movement velocity curve spectrum of another concern position Q2 and cursor position can show in the same associated coordinates system and form a movement velocity curve spectrum.

In addition, the maximum movement speed curve spectrum mentioned in the above process is a seed type of movement velocity curve spectrum, depending on paying close attention to the type of position.In one of the embodiments, the maximum movement speed curve spectrum for corresponding relationship between recording velocity values and time variable is shown by display, such as velocity amplitude can be characterized with doppler velocity value, the form of expression of the maximum movement speed curve spectrum can be similar to the form of expression of Doppler frequency spectrum.Certainly, it shows that the maximum movement speed curve for recording the velocity amplitude in blood flow velocity vector and the curved line relation between time variable is composed by display in one of the embodiments, composes structural relation see, for example, Fig. 7 and curve employed in figure 8.The form of expression of maximum movement speed curve spectrum can be various, and the present embodiment is limited not to this, as long as the map of corresponding relationship is in the scope of the claimed of the present embodiment between characterization blood flow velocity and time variable.

As shown in figure 5, showing ultrasound image by display, and concern position determining in annotation step S400 on the ultrasound image in step S700.As shown in figure 11, on the same display interface, ultrasound image 50, area-of-interest 51 are shown in corresponding region, while showing the concern corresponding largest motion in position 52 speed It writes music line spectrum 53, and marks concern position 52 in ultrasound image 51.If it is constant within a preset period of time to pay close attention to position 52, when showing maximum movement speed curve spectrum 53 within a preset period of time, concern position 52 immobilizes in area-of-interest 51.If concern position 52 is constant within a preset period of time, or changes over time referring to method mentioned above, then concern position 52 can jump in area-of-interest 51.As shown in figure 12, when showing that the corresponding maximum movement speed curve of t31, t32, t33 composes 53, concern position in area-of-interest 51 successively jumps to A32 and A33 from A31, certainly the historical movement track of concern position can be drawn on ultrasound image 50 by way of line 54 or rendering, to show the situation of change for corresponding to maximum value position in maximum movement speed curve spectrum 53.

Referring to Figure 13 and Figure 12, the corresponding position label concern position in maximum movement speed curve spectrum 53, or the variation of concern position.Such as, in Figure 12, the corresponding position label concern position in maximum movement speed curve spectrum 53, the mode of label can be the pictorial symbolization used by label concern position in the corresponding position label area-of-interest in maximum movement speed curve spectrum 53, or coordinate (as shown in figure 13) of the label concern position in ultrasound image.In another example, in Figure 13, the variation of label concern position during maximum movement speed curve spectrum 53 is sequentially shown, unfilled triangle mark is for indicating t31 moment corresponding concern station location marker and image coordinate location, the triangle of filling is identified for indicating currently to show the corresponding concern station location marker of moment t32 and image coordinate location, thus the change conditions for the mark position expressed one by one.Certainly, no matter the mode of text or the mode of identifier, during display, in area-of-interest label concern position identifier can with maximum movement speed curve compose 53 display show one by one.

In addition, the map part of the different concern positions can also be corresponded to come separator using color or instruction icon in maximum movement speed curve spectrum 53.For example, in Figure 12 and Figure 13, the color of the corresponding map part t31, t32, t33, t34 and t35 or instruction icon (such as triangle in Figure 13) separator in maximum movement speed curve spectrum 53.Further, the color of the corresponding map part t31, t32, t33, t34 and t35 or instruction icon (such as triangle in Figure 13) can also use identical color or instruction icon with A31, A32, A33 is identified in area-of-interest in maximum movement speed curve spectrum 53.

In some embodiments of the present embodiment, it can also browse in the following ways and check concern position and its corresponding map part, such as in Figure 14, identify cursor 55 in the shift position of the area-of-interest 51；When shift position is close to or at the concern position A32, the part map (the corresponding map part t32 in such as Figure 16) in the maximum movement speed curve spectrum 53 is highlighted, the part map is associated with the concern position；Opposite, it can also identify shift position of the cursor 55 in maximum movement speed curve spectrum 53, when part map (the corresponding map part t32 in such as Figure 14) that the shift position is composed close to or at the maximum movement speed curve, the concern position A32 in the area-of-interest 51 is highlighted, highlighted concern position is associated with the part map.

In some embodiments of the present embodiment, the regional choice instruction that user makes on the ultrasound image is obtained；It is instructed according to the regional choice, determines the area-of-interest 51.Here regional choice instruction can be the adjusting to sample boxes, such as the adjusting to irregular frame 51.

In addition, the ultrasound image shown in above-mentioned steps S700 can have blood flow velocity with Overlapping display.Here blood flow velocity can be any method being noted above and calculate the blood flow velocity obtained, can be velocity vector.

Blood flow velocity vector is obtained for example, calculating in step S200, then image processing module is superimposed blood flow velocity vector on the ultrasound image and forms blood flow projectile figure, shows simultaneously in output to display with maximum movement speed curve spectrum.Blood flow projectile figure shows the speed of blood flow, the flow direction for also showing blood flow indicates some endovascular blood flow mobility status in area-of-interest 51 by arrow in Figure 17, the length of arrow indicates the size of velocity amplitude, and the direction of arrow indicates directional velocity.Below in conjunction with the formation for explaining blood flow projectile figure in some embodiments.

Image processing module 7 is used for the ultrasonic signal obtained based on above-mentioned steps S100, obtains the blood flow velocity vector of target point.Such as, in one of the embodiments, in step s 200, firstly, obtaining the distribution density instruction of user's input, target point is randomly choosed in scanning target according to distribution density instruction, calculate the corresponding velocity vector of target point selected, to obtain the velocity vector of the target point selected, the velocity vector of acquisition is labeled on the ultrasound image, to show over the display.Then, the corresponding velocity vector of target point selected is calculated, obtains the velocity vector information of the target point selected, the labeled blood flow that formed on the ultrasound image of the velocity vector of acquisition casts figure, to show over the display.In step s 200 include the blood flow velocity vector for obtaining target point in scanning target based on ultrasonic signal, hereinafter will be explained in detail explanation.

Calculate in step s 200 the target point of acquisition blood flow velocity vector be mainly used in following step S800 with maximum movement speed curve spectrum comparison show, therefore according to the different display modes of blood flow velocity vector, different blood flow velocity vectors can be obtained in step s 200.

Such as, in one embodiment of the present embodiment, it include: according to the ultrasonic signal obtained in above-mentioned steps S100 in above-mentioned steps S200, it calculates target point and is located at the blood flow velocity vector in the ultrasound image of different moments at the first display position, the blood flow velocity Vector Message being located at obtaining target point in the ultrasound image of different moments.During the velocity vector for being so superimposed blood flow on the ultrasound image, the velocity vector that can be the blood flow in each moment ultrasound image at the first display position of comparison display display.As shown in Figure 16 (a), according to the ultrasonic signal obtained in above-mentioned steps S200, can obtain respectively t1, t2 ..., tn moment corresponding ultrasound image data P1, P2 ..., in Pn, then calculate target point at various moments in ultrasound image at the first display position (position of black dot in figure) velocity vector.In the present embodiment, the first display position is always positioned at the position in two dimensional image (H1, W1) target point in ultrasound image at various moments.Based on this, in subsequent step S800 when comparison display velocity vector, i.e., the ultrasound image that is shown in display The different moments corresponding velocity vector calculated is shown in P0 at position (H1, W1).If target point referring in above-mentioned specific embodiment according to the autonomous selected section of user or all or by system default, so correspondence can know corresponding first display position, and by calculating the velocity vector information in current time corresponding ultrasound image at the first display position to compare display, this display pattern is known as first mode herein, hereafter together.Effect diagram when two dimensional image P0 display is given in Figure 16 (a) example, in can certainly being shown applied to 3-D image, the ultrasound image at each moment is taken as previously mentioned sweep volume and obtains 3 d image data library, and the first display position is taken as the space three-dimensional spatial coordinate position in 3 d image data library, being not repeated herein.

In another embodiment of the present embodiment, it include: according to the ultrasonic signal obtained in above-mentioned steps S100 in above-mentioned steps S300, target point continuous moving corresponding position and velocity vector for successively obtaining into ultrasound image are calculated, to obtain the velocity vector of target point.In the present embodiment, the velocity vector for being moved to the another position of ultrasound image from a position in a time interval by computing repeatedly target point, to obtain target point since after continuous moving initial position in ultrasound image the corresponding velocity vector in each corresponding position.That is, to determine that the calculating position of velocity vector can be obtained by calculating in the ultrasound image of the present embodiment.During the velocity vector for being so superimposed blood flow on the ultrasound image, the blood flow velocity vector that can be at the position for calculating acquisition in each moment ultrasound image of display is compared.

As shown in Figure 16 (b), according to the ultrasonic signal obtained in above-mentioned steps S100, can obtain respectively t1, t2 ..., tn moment corresponding ultrasound image data P11, P12 ..., in P1n, then, according to some or all of autonomous selection target point of user or by the density etc. of system default target point in reference above-described embodiment, determine the initial position of target point, if position is in Figure 16 (b), velocity vector A1 of the initial position in moment t1 ultrasound image P11 is then calculated at first point of (H1, W1).Secondly, target point (i.e. black dot in figure) is calculated from the position (H2, W2) on the ultrasound image P12 that the initial position on the ultrasound image P11 of moment t1 is moved to moment t2, then according to ultrasonic signal, the velocity vector in ultrasound image P12 at position (H2, W2) is obtained, to compare display.Such as, the direction of velocity vector along moment t1 ultrasound image P11 on the position (H1, W1), a mobile time interval is (wherein, t2- moment, t1=moment time interval), calculate displacement when reaching the second moment t2, second display position of the target point on second moment ultrasound image so on first moment t1 just has found, then the velocity vector on this second display position is obtained according to the ultrasonic signal obtained in upper step S200 again, to obtain target point speed Vector Message in moment t2 ultrasound image P12.And so on, per two adjacent moment, along target point in the direction of the first moment corresponding velocity vector, the time interval at mobile two neighboring moment obtains displacement, corresponding position of the target point on the second moment ultrasound image is determined according to displacement, the velocity vector that target point corresponding position from the ultrasound image that the first moment was moved to for the second moment is obtained further according to ultrasonic signal can obtain speed arrow of the target point from continuous moving at (H1, W1) in ultrasound image at (Hn, Wn) in this way Amount, to obtain the velocity vector of target point corresponding position in the ultrasound image from initial position continuous moving to different moments, to obtain the velocity vector of target point, shows that it simultaneously with ultrasound image.

In the display mode of the present embodiment, target point is calculated in the moving displacement of a time interval and determines according to the displacement corresponding position of target point in ultrasound image, it is mobile according to the time interval since the target point of initial selected, this time interval can be determined by system tranmitting frequency, it can also be and determined by display frame rate, or it can also be the time interval of user's input, the position reached after target point movement is calculated by the time interval inputted according to user, is then obtaining the velocity vector at the position to compare display.When initial, N number of initial target point can be marked in figure according to mode described previously, has arrow to indicate the size and Orientation of this flow velocity, as shown in Figure 16 (b) on each initial target point.In the step S800 of comparison display, label target point continuous moving arrives the corresponding velocity vector obtained when corresponding position, is formed at any time in the mark for flowing shape.By marking Figure 16 (b) mode to calculate the velocity vector of acquisition, so change with time, in newly-generated figure, originally position change can occur for the arrow of each point, the movement that arrow can be used in this way, can form similar blood flow flow process, so as to user it is observed that approximate true blood flow flows imaging results, this display pattern is known as second mode herein, hereafter together.Equally, effect diagram when two dimensional image P10 display is given in Figure 16 (b) example, in can certainly being shown applied to 3-D image, the ultrasound image at each moment is taken as previously mentioned sweep volume and obtains 3 d image data library, and the first display position is taken as the space three-dimensional spatial coordinate position in 3 d image data library, being not repeated herein.

In order to improve display effect, it avoids identifying human eye can not due to blood flow velocity shows too fast, then in one embodiment of the present embodiment, it further include when showing the velocity vector about blood flow in the above process, slow play processing is carried out to the velocity vector that above-mentioned steps S200 is obtained, to compare display slow play treated velocity vector.For example, carrying out slow play processing to velocity vector first, velocity vector at a slow speed is generated；Then, the velocity vector at a slow speed described in Overlapping display on above-mentioned ultrasound image, forms above-mentioned blood flow projectile figure, to realize that blood flow projectile figure and the comparison of movement velocity curve spectrum are shown.

Describe the variation of blood flow velocity on target point by generating particle projectile as mark in one of the embodiments, the color coding and/or length of particle projectile are related to the velocity amplitude of specific location blood flow in the vascular；And the particle projectile is sent into display, show that the particle projectile changes with time in the specific location of the ultrasound image, dynamically show the movement of blood flow in the vascular to the Dynamically Announce by particle projectile, to obtain blood flow projectile figure.Further, the particle projectile further includes direction signs, and the direction of the direction signs is related to the directional velocity of the blood flow.It can clearly can describe practical flow direction of the target point in scanning target in the blood flow projectile figure of display using the method for the present embodiment, compared to the mode for the size and Orientation that corresponding display position only in the picture shows the blood flow velocity that current location changes over time, actual blood flow trend in expression scanning target that can be more accurate, truer and vivid.This In can by the point or arrow of flowing, or can with other marks of drawing direction come describe flowing blood flow flowing process.Referring in Figure 15, particle projectile is indicated using arrow 56.

In addition, particle projectile can also only include direction signs, the direction of the speed value information without carrying blood flow, direction signs is related to the directional velocity of specific location blood flow in the scanning target.The particle projectile comprising direction signs is shown in the specific location of ultrasound image, dynamically to show the direction of motion of blood flow in the scanning target.

Particle projectile in the present embodiment can be the manifestation mode similar to arrow, and the length and/or thickness of arrow can be used for showing the velocity amplitude of blood flow, and the direction of arrow can be used for showing the directional velocity of blood flow.Specific position in the present embodiment refers to, a specific position shows the corresponding particle projectile when velocity vector about blood flow on the ultrasound image, specific position can be the position for marking the velocity vector of display blood flow, such as can be the first display position or the second display position mentioned in Figure 16 (a) and Figure 16 (b).

In addition, based on the above embodiment, if it exists when multiple concern positions, then the corresponding maximum movement speed curve spectrum in multiple concern positions can be displayed side by side in display area, it can also be with Overlapping display.For example, with reference to shown in Figure 17, providing a kind of comparison and show the embodiment of multiple maximum movement speed curves spectrum.In the display interface, including for showing the ultrasonic image area 91 of ultrasound image, to show the blood flow state in blood vessel 93, embodiment as shown in connection with fig. 10, first area-of-interest is 92, and the second area-of-interest is 95, and black triangle characterizes the corresponding concern position 96 of second maximum value found in the second area-of-interest 95, bullet characterizes the corresponding concern position 94 of first maximum value found in the first area-of-interest 92, cursor position 97.The simultaneous display concern corresponding maximum movement speed curve in position 96 composes 981 (chain-dotted line is expressed as in figure) in maximum movement speed curve spectrum viewing area 98, it pays close attention to the corresponding maximum movement speed curve in position 94 and composes 983 (being expressed as dotted line in figure), the corresponding real time kinematics map 982 (being expressed as solid line in figure) of cursor position 97.Figure 19 gives the mode of three kinds of map Overlapping displays together.As it can be seen that can be composed using display with maximum movement speed curve corresponding with one concern position and another described concern position in Figure 12, it further can be with the real time kinematics map at Overlapping display cursor position.

In addition, as shown in figure 17, the maximum value of blood flow velocity in text prompt area-of-interest, minimum value, intermediate value and/or average value can also be exported in the display interface.Such as, in text display area 99, maximum value (i.e. speed maximum value in current time entire sample boxes), the minimum value of blood flow velocity present frame (i.e. speed minimum value in current time entire sample boxes), the intermediate value of blood flow velocity present frame (i.e. speed intermediate value in current time entire sample boxes) and the blood flow velocity present frame average value (i.e. speed average in current time entire sample boxes) of blood flow velocity present frame in the second area-of-interest 95 are shown.

When the corresponding maximum movement speed curve time spectrum in the multiple concern positions of Overlapping display, mode above is referred to by highlighting or colour-coded distinguishes the corresponding maximum movement speed curve spectrum in the different concern positions of display.

Include: in step S200 in a wherein variant embodiment based on embodiment shown in fig. 6

Image processing module obtains the Doppler frequency spectrum of multiple angle directions, Doppler frequency spectrum is for characterizing blood flow velocity according to ultrasonic signal；

In step S410, image processing module obtains the maximum value of blood flow velocity by searching for the maximum value in the Doppler frequency spectrum of multiple angle directions, to determine concern position in the step s 420.And the mode for searching the maximum value in the Doppler frequency spectrum of multiple angle directions uses the envelope value of the Doppler frequency spectrum of more multiple angle directions.Further, in step S600, show that Doppler frequency spectrum changes with time at concern position according to time change sequence, to form movement velocity curve spectrum.It will be significantly simpler in this way, it is convenient, without doing excessive improvement to hardware.

Fig. 5 is the flow diagram of the ultrasonic imaging method of the present embodiment one embodiment.Although these steps are not that the inevitable sequence according to arrow instruction successively executes it should be understood that each step in the flow chart of Fig. 5 is successively shown according to the instruction of arrow.Unless expressly stating otherwise herein, there is no stringent sequences to limit for the execution of these steps, can execute in the other order.And, at least part step in Fig. 5 may include multiple sub-steps or multiple stages, these sub-steps or stage are not necessarily to execute completion in synchronization, but it can execute at different times, its execution sequence, which is also not necessarily, successively to be carried out, but can be executed at least part of the sub-step or stage of other steps or other steps or alternately be executed parallel.Fig. 6 and Fig. 9, Figure 10 are all based on the extension embodiment of Fig. 5.

Above implementation of each embodiment in illustrating only just for corresponding steps is expounded, then in the case where logic does not contradict, above-mentioned each embodiment be can be combined with each other and form new technical solution, and the new technical solution is still in the open scope of present embodiment.

Through the above description of the embodiments, those skilled in the art can be understood that above-described embodiment method can be realized by means of software and necessary general hardware platform, it can certainly the former be more preferably embodiment by hardware, but in many cases.Based on this understanding, substantially the part that contributes to existing technology can be embodied in the form of software products technical solution of the present invention in other words, the computer software product is carried in a non-volatile computer readable storage medium (such as ROM, magnetic disk, CD, server cloud space), it uses including some instructions so that a terminal device (can be mobile phone, computer, server or the network equipment etc.) execute method described in each embodiment of the present invention.

The switching command that user is received by operation control module composes display pattern into maximum movement speed curve, and image processing module is also used to pay close attention to position accordingly by searching for the maximum value of blood flow velocity to obtain, maximum movement speed curve spectrum is presented.In maximum movement speed curve spectrum in the present embodiment, the form of expression of movement velocity map can be used, such as, when concern position has been determined, a segment signal is chosen, Fourier transformation is done, obtain blood flow frequency spectrum, interior at the time of this segment signal of this spectrogram representation, blood flow is with the variation of frequency, and this frequency is that Doppler frequency represents the velocity magnitude of blood flow.Therefore can regard as at this moment, blood flow The distribution map of the quantity of the red blood cell of middle friction speed.It is then followed by according to the corresponding concern position of maximum value screened again, choose next segment signal, the distributed number figure of the red blood cell of the blood flow friction speed at this moment is generated again, then the distribution map at each moment is longitudinally shown according to grayscale form, successively just forms the blood flow frequency spectrum of the maximum movement speed curve spectrum for characterizing the present embodiment according to Time alignment.

Doppler echocardiography can measure the maximum speed of blood flow, be usually applied to the quantitative Diagnosis of valve stenosis and arteriosclerotic lesion etc..It is an important quantitative analysis function in medical ultrasound image.What traditional frequency spectrum Doppler obtained is frequency spectrum of the blood flow along transonic direction velocity component.It is not actual speed spectrum distribution, and is influenced by gimmick, and blood vessel and the angle in transonic direction are also difficult to be consistent when scanning every time, therefore cause the precision of measurement and repeatability poor, is unable to get most high speed angle value.Although can estimate the maximum value of blood flow by angle correction, this mode can only be directed to laminar flow.For more complicated position, such as heart, at carotid sinus, it is not available angle correction.Even if, such as arteria carotis communis, vertebral artery etc., being influenced angle correction still by gimmick will cause biggish error in long and straight blood vessel.Maximum speed is unable to measure present invention is generally directed to above-mentioned frequency spectrum Doppler and angle correction bring error is improved.Frequency spectrum Doppler can also be done using Multi-angle ultrasound wave transmitting received signal.After over-angle is fitted, frequency spectrum Doppler can show frequency spectrum of the blood flow on practical flow direction, available accurately to obtain peak flow rate (PFR).In addition, the available blood flow of the ultrasound emission method of reseptance of multi-angle casts figure, it is particularly possible to blood flow maximum position is searched out by calculating, so as to show the blood flow frequency spectrum on maximum blood flow velocity position.

The embodiments described above only express several embodiments of the present invention, and the description thereof is more specific and detailed, and but it cannot be understood as limitations on the scope of the patent of the present invention.It should be pointed out that for those of ordinary skill in the art, without departing from the inventive concept of the premise, various modifications and improvements can be made, and these are all within the scope of protection of the present invention.Therefore, the scope of protection of the patent of the invention shall be subject to the appended claims.

Claims (31)

1. A kind of display methods of supersonic blood movement spectrum comprising:

   The ultrasonic signal in scanning target is obtained by probe；

   Based on the ultrasonic signal, the blood flow velocity in the scanning target in vascular is obtained；

   According to the ultrasonic signal, at least part of ultrasound image of the scanning target is obtained；

   Obtain the concern position being located in the vascular；

   The associated coordinates system of speed and time is drawn in viewing area；

   In the associated coordinates system, the variation of the value of blood flow velocity at the concern position is shown according to the variation sequence of time, obtains movement velocity curve spectrum associated with the concern position；

   The concern position is marked on the ultrasound image.
2. The display methods of supersonic blood movement spectrum according to claim 1, wherein include: in the ultrasonic signal obtained by probe in scanning target

   The ultrasonic signal of multiple angles in scanning target is obtained by probe, the ultrasonic signal of the multiple angle belongs to different receiving angle or launch angle, according to the corresponding different angle of super wave signal, it is stored as at least one set of data frame collection relevant to angle；With,

   Described to be based on the ultrasonic signal, obtaining the blood flow velocity in the scanning target in vascular includes:

   Based on the data frame collection for adhering to different angle separately, the corresponding velocity component of at least two different angles is obtained；

   According to velocity component relevant at least two angles, the blood flow velocity is obtained.
3. The display methods of supersonic blood movement spectrum according to claim 1, wherein, the concern position includes at least two, in the associated coordinates system, the variation that the value of blood flow velocity at the concern position is shown according to the variation sequence of time, obtaining movement velocity curve spectrum associated with the concern position includes:

   Described at least two variations for paying close attention to the value of blood flow velocity at position are shown under the same associated coordinates system, while according to the variation of time sequence, obtain movement velocity curve associated at least two concern position respectively.
4. The display methods of supersonic blood movement spectrum according to claim 1, wherein the concern position includes at least one of following situations: the position where cursor position, user's selected location and blood flow velocity maximum value.
5. The display methods of supersonic blood movement spectrum according to claim 1, wherein, in the method when showing the ultrasound image, particle projectile is generated, the color coding and/or length of the particle projectile are related to the value of specific location blood flow velocity in the vascular；

   It shows that the particle projectile changes with time on the ultrasound image, the movement of blood flow in the vascular is dynamically showed to the Dynamically Announce by particle projectile.
6. The display methods of supersonic blood movement spectrum according to claim 5, wherein described to be based on the ultrasonic signal, obtaining the blood flow velocity in the scanning target in vascular includes；

   At least part based on ultrasonic signal obtains the first blood flow velocity in the scanning target in vascular,

   At least part based on ultrasonic signal obtains the second blood flow velocity in the scanning target in vascular；

   Show that the particle projectile, the color coding and/or length of the particle projectile are related to the value of the first blood flow velocity of specific location in the vascular on the ultrasound image；

   It is composed in the movement velocity curve, the value that display records the second blood flow velocity at the concern position changes with time.
7. The display methods of supersonic blood movement spectrum according to claim 4, wherein the blood flow velocity maximum value includes at least following one:

   Maximum value in the Doppler frequency of angle or Doppler frequency spectrum；

   Maximum value in the Doppler frequency of different angle or Doppler frequency spectrum；

   For the maximum value being fitted along the Doppler frequency of multiple angles or Doppler frequency spectrum in blood flow velocity vector obtained；With,

   The maximum value in the blood flow velocity vector obtained is calculated based on adjacent two frame or multiple frames of ultrasonic image,

   Wherein, the launch angle of ultrasonic beam or the receiving angle of ultrasound echo signal be the angle ranging from.
8. The display methods of supersonic blood movement spectrum according to claim 6, wherein the concern position being located in the vascular that obtains includes:

   Search the maximum value in first blood flow velocity；

   The concern position is determined according to the maximum value position in first blood flow velocity.
9. The display methods of supersonic blood according to claim 1 movement spectrum obtains the concern position one of in the following manner, and show the movement velocity curve spectrum wherein if when the concern position includes the position where blood flow velocity maximum value:

   Multiple target points are extracted in vascular in area-of-interest in current time corresponding blood flow velocity, determine the maximum value in current time blood flow velocity, by the target point where the maximum value in current time blood flow velocity, it is considered as the first concern position, in movement velocity curve spectrum, the corresponding blood flow velocity in association display first concern position at the position where current time；With,

   Extract in preset time period in vascular in area-of-interest multiple target points corresponding blood at various moments Flow velocity degree, determine the maximum value of blood flow velocity in the preset time period, by the target point where the maximum value of blood flow velocity in the preset time period, it is considered as the second concern position, in movement velocity curve spectrum, it is located at the second concern position corresponding blood flow velocity in the preset time period of association display in the preset time period.
10. The display methods of supersonic blood movement spectrum according to claim 3, wherein the concern position being located in the vascular that obtains includes:

    By searching for the maximum value of blood flow velocity in the first area-of-interest, a concern position is obtained；

    By searching for the maximum value of blood flow velocity in the second area-of-interest, another concern position is obtained.
11. The display methods of supersonic blood movement spectrum according to claim 1 or 2, wherein the concern position being located in the vascular that obtains includes:

    Search the maximum value in the blood flow velocity；

    Determine that the concern position, the concern position correspond to the position where the maximum value.
12. The display methods of supersonic blood movement spectrum according to claim 1, wherein, if the concern position includes the position where blood flow velocity maximum value, the concern position at any time the variation of variable and change or the concern position immobilizes within a preset period of time.
13. The display methods of the movement spectrum of the supersonic blood according to claim 9 or 12, wherein the preset time period is greater than or equal to a cardiac cycle.
14. The display methods of supersonic blood according to claim 1 movement spectrum, wherein if the concern position includes the position where blood flow velocity maximum value, the historical movement track of the concern position is drawn on the ultrasound image.
15. The display methods of supersonic blood movement spectrum according to claim 1, wherein the variation of the concern position or the label concern position is marked in movement velocity curve spectrum.
16. The display methods of supersonic blood movement spectrum according to claim 11, wherein in the movement velocity curve spectrum, correspond to the map part of the different concern positions come separator using color or instruction icon.
17. The display methods of supersonic blood movement spectrum according to claim 1, wherein in the method further include:

    Identify shift position of the cursor in area-of-interest or movement velocity curve spectrum；

    When the shift position is close to or at the concern position, the part map in the movement velocity curve spectrum is highlighted, the part map is associated with the concern position；

    When the part figure time spectrum that the shift position is composed close to or at the movement velocity curve, the concern position in the area-of-interest is highlighted, highlighted concern position is associated with the part map.
18. The display methods of supersonic blood movement spectrum according to claim 1, wherein the method also includes:

    Obtain the regional choice instruction that user makes on the ultrasound image；

    It is instructed according to the regional choice, determines the area-of-interest.
19. The display methods of supersonic blood movement spectrum according to claim 1, wherein the method also includes:

    Export maximum value, minimum value, intermediate value and/or the average value of blood flow velocity in text prompt area-of-interest.
20. The display methods of supersonic blood movement spectrum according to claim 11, wherein described to be based on the ultrasonic signal, obtaining the blood flow velocity in the scanning target in vascular includes:

    According to ultrasonic signal, the Doppler frequency spectrum of multiple angle directions is obtained；

    The maximum value searched in the blood flow velocity, determines that the concern position includes:

    By searching for the maximum value in the Doppler frequency spectrum of multiple angle directions, the maximum value of the blood flow velocity is obtained, pays close attention to position to determine；

    It is described in the associated coordinates system, the variation of the value of blood flow velocity at the concern position is shown according to the variation sequence of time, obtaining movement velocity curve spectrum associated with the concern position includes, in movement velocity curve spectrum, show that Doppler frequency spectrum changes with time at the concern position according to time change sequence.
21. A kind of ultrasonic image-forming system characterized by comprising

    Probe；

    Transmit circuit, for motivating described pop one's head in scanning objective emission ultrasonic beam；

    Circuit and Beam synthesis module are received, for receiving the echo of the ultrasonic beam, obtains the ultrasonic signal in scanning target；

    Image processing module, for being based on the ultrasonic signal, obtain the blood flow velocity in the scanning target in vascular, according to the ultrasonic signal, obtain at least part of ultrasound image of the scanning target, the concern position being located in the vascular is obtained, the associated coordinates system of speed and time is drawn in viewing area；And

    Display, for showing the variation of the value of blood flow velocity at the concern position according to the variation sequence of time in the associated coordinates system, movement velocity curve spectrum associated with the concern position is obtained, and show ultrasound image, the concern position is marked on the ultrasound image.
22. Ultrasonic image-forming system according to claim 21, wherein by probe obtain from The ultrasonic signal of multiple angles in target is scanned, the ultrasonic signal of the multiple angle belongs to different receiving angle or launch angle；

    Image processing module is also used to be stored as at least one set of data frame collection relevant to angle according to the corresponding different angle of super wave signal, based on the data frame collection for adhering to different angle separately, obtains the corresponding velocity component of at least two different angles；According to velocity component relevant at least two angles, the blood flow velocity is obtained.
23. Ultrasonic image-forming system according to claim 21, wherein, the concern position includes at least two, using display under the same associated coordinates system, the variation for showing the value of blood flow velocity at least two concern position according to the variation sequence of time simultaneously obtains movement velocity curve associated at least two concern position respectively.
24. Ultrasonic image-forming system according to claim 21, wherein the concern position includes at least one of following situations: the position where cursor position, user's selected location and blood flow velocity maximum value.
25. Ultrasonic image-forming system according to claim 21, wherein, when showing ultrasound image using display, generate particle projectile, the color of the particle projectile encodes and/or length is related to the value of specific location blood flow velocity in the vascular, it shows that the particle projectile changes with time on the ultrasound image, the movement of blood flow in the vascular is dynamically showed to the Dynamically Announce by particle projectile.
26. Ultrasonic image-forming system according to claim 25, wherein, described image processing module is also used at least part based on ultrasonic signal, obtain the first blood flow velocity in the scanning target in vascular, at least part based on ultrasonic signal obtains the second blood flow velocity in the scanning target in vascular；Show that the particle projectile, the color coding and/or length of the particle projectile are related to the value of the first blood flow velocity of specific location in the vascular on the ultrasound image；It is composed in the movement velocity curve, the value that display records the second blood flow velocity at the concern position changes with time.
27. Ultrasonic image-forming system according to claim 26, wherein described image processing module is also used to search the maximum value in first blood flow velocity, determines the concern position according to the maximum value position in first blood flow velocity.
28. Ultrasonic image-forming system according to claim 23, wherein, described image processing module is also used to obtain a concern position by searching for the maximum value of blood flow velocity in the first area-of-interest, by searching for the maximum value of blood flow velocity in the second area-of-interest, another concern position is obtained.
29. Ultrasonic image-forming system according to claim 21, wherein if the concern position includes the position where blood flow velocity maximum value, the concern position at any time the variation of variable and change, or Concern position described in person immobilizes within a preset period of time.
30. Ultrasonic image-forming system according to claim 29, wherein the preset time period is greater than or equal to a cardiac cycle.
31. Ultrasonic image-forming system according to claim 21, wherein in the movement velocity curve spectrum, correspond to the map part of the different concern positions come separator using color or instruction icon.