CN103126721A - Method and device for compound ultrasonic imaging based on multiple focuses and multiple ultrasonic velocities - Google Patents

Method and device for compound ultrasonic imaging based on multiple focuses and multiple ultrasonic velocities Download PDF

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CN103126721A
CN103126721A CN2013100691518A CN201310069151A CN103126721A CN 103126721 A CN103126721 A CN 103126721A CN 2013100691518 A CN2013100691518 A CN 2013100691518A CN 201310069151 A CN201310069151 A CN 201310069151A CN 103126721 A CN103126721 A CN 103126721A
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focus
ultrasonoscopy
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陈惠人
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Vinno Technology Suzhou Co Ltd
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Abstract

The invention provides a method and a device for compound ultrasonic imaging based on multiple focuses and multiple ultrasonic velocities. The method includes: configuring k emission focuses f1-fk and n different ultrasonic velocities c1-cn; on the basis of the n different ultrasonic velocities c1-cn, computing to obtain an optimal ultrasonic velocity corresponding to each emission focus region; and on the basis of the emission focuses f1-fk and the corresponding optimal ultrasonic velocities thereof, scanning target tissue to obtain k-frame primary ultrasonic images F()-F(), and stitching the obtained k-frame primary ultrasonic images to obtain a final ultrasonic image F. By the method and the device, distortion and clutter artifacts of ultrasonic images are reduced effectively, and resolution and authenticity of the ultrasonic images are improved.

Description

ULTRASONIC COMPLEX formation method and device based on multifocal point, many velocities of wave
Technical field
The present invention relates to the ultrasonic diagnosis art, relate in particular to a kind of ULTRASONIC COMPLEX formation method and device based on multifocal point, many velocities of wave.
Background technology
Ultrasonic diagnosis (Ultrasonic Diagnosis) is a kind of diagnostic method that ultrasonic detecting technology is applied to human body, and its data by measuring physiology or organizational structure and form are to find disease.
At present, when diasonograph carries out tissue scanning imaging, think that tissue is uniformity, therefore, the spread speed of ultrasound wave in human body generally is set as fixed value (1540m/s), ultrasonic image-forming system calculates delay and the focusing of launching beam and received beam according to this fixed speed, and finally carries out imaging.Yet, tissue generally comprises skin, fat, muscle, body of gland etc. from depth direction, and the spread speed of ultrasound wave in above-mentioned tissue is not quite similar, so just can cause fixedly velocity of wave and the actual speed of ultrasound wave in tissue preset inconsistent, further cause the distortion of ultra sonic imaging, the pseudomorphism that even increases ultrasonoscopy or clutter noise, thereby reduce resolution and the diagnosticability of ultrasonoscopy.
Summary of the invention
The technical problem of solution required for the present invention is to provide a kind of ULTRASONIC COMPLEX formation method based on multifocal point, many velocities of wave, to optimize the image quality of ultrasonoscopy.
Correspondingly, the present invention also provides a kind of ULTRASONIC COMPLEX imaging device based on multifocal point, many velocities of wave.
For solving the problems of the technologies described above, the technical solution used in the present invention is:
A kind of ULTRASONIC COMPLEX formation method based on multifocal point, many velocities of wave comprises the steps:
S1, k emission focus f of configuration 1~ f kAnd the different ultrasonic velocity c of n kind 1~ c n
S2, based on the different ultrasonic velocity c of described n kind 1~ c n, calculate to obtain the best ultrasonic velocity corresponding to each emission focus area
Figure 2013100691518100002DEST_PATH_IMAGE001
~
S3, based on emission focus f 1~ f kAnd corresponding best ultrasonic velocity ~ Destination organization is carried out scanning, with obtain the elementary ultrasonoscopy F of k frame (
Figure 2013100691518100002DEST_PATH_IMAGE003
) ~ F (
Figure 153514DEST_PATH_IMAGE002
);
S4, the elementary ultrasonoscopy of k frame that gets is spliced, to obtain final ultrasonoscopy F, its splicing principle is: if image-region mainly is positioned at focus f xThe place, F=F ( ); If image-region is positioned at focus f yAnd focus f zSplicing place, F=k * F (
Figure 2013100691518100002DEST_PATH_IMAGE005
)+(1-k) * F (
Figure 127603DEST_PATH_IMAGE006
); Wherein, 1≤x≤k, 1≤y≤k, 1≤z≤k, k 〉=2.
In certain embodiments of the invention, above-mentioned steps S2 specifically comprises:
S21, from emission focus f 1~ f kIn choose arbitrarily one the emission focus, and based on this emission focus obtain respectively corresponding to ultrasonic velocity c 1~ c nUltrasonoscopy F (c 1) ~ F (c n);
S22, respectively launch focus f according to what the user set 1~ f kThe position, respectively at ultrasonoscopy F (c 1) ~ F (c n) in mark off the zone corresponding to the ROI of each focus;
S23, calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 417770DEST_PATH_IMAGE001
~
Figure 360318DEST_PATH_IMAGE002
, its computing formula is:
P j(
Figure 2013100691518100002DEST_PATH_IMAGE007
)=
Figure 735936DEST_PATH_IMAGE008
Wherein, 1≤i≤n, 1≤j≤k.
In other embodiment of the present invention, above-mentioned steps S2 specifically comprises:
S21 ', traversal adopt k emission focus f 1~ f kAnd n kind ultrasonic velocity c 1~ c n, to obtain k * n frame ultrasonoscopy F j(c i);
S22 ', the emission focus f that sets according to the user jThe position, one by one at ultrasonoscopy F j(c 1) ~ F j(c n) in mark off emission focus f jCorresponding ROI zone;
S23 ', calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 94236DEST_PATH_IMAGE001
~
Figure 566806DEST_PATH_IMAGE002
, its computing formula is:
P j(
Figure 352359DEST_PATH_IMAGE007
)=
Figure 277590DEST_PATH_IMAGE008
Wherein, 1≤i≤n, 1≤j≤k.
Corresponding to said method, a kind of ULTRASONIC COMPLEX imaging device provided by the invention, it comprises:
Dispensing unit, be used for k of configuration and launch focus f 1~ f kAnd the different ultrasonic velocity c of n kind 1~ c n
Best velocity of wave acquiring unit, be used for based on the different ultrasonic velocity c of described n kind 1~ c n, calculate to obtain the best ultrasonic velocity corresponding to each emission focus area
Figure 501898DEST_PATH_IMAGE001
~
Figure 781305DEST_PATH_IMAGE002
Image acquisition unit, be used for based on emission focus f 1~ f kAnd corresponding best ultrasonic velocity
Figure 65656DEST_PATH_IMAGE001
~ Destination organization is carried out scanning, with obtain the elementary ultrasonoscopy F of k frame (
Figure 178286DEST_PATH_IMAGE003
) ~ F (
Figure 297552DEST_PATH_IMAGE002
);
The image mosaic unit, be used for the elementary ultrasonoscopy of k frame that gets is spliced, to obtain final ultrasonoscopy F, its splicing principle is: if image-region mainly is positioned at focus f xThe place, F=F (
Figure 752804DEST_PATH_IMAGE004
); If image-region is positioned at focus f yAnd focus f zSplicing place, F=k * F (
Figure 590310DEST_PATH_IMAGE005
)+(1-k) * F (
Figure 156420DEST_PATH_IMAGE006
); Wherein, 1≤x≤k, 1≤y≤k, 1≤z≤k, k 〉=2.
In certain embodiments of the invention, described best velocity of wave acquiring unit specifically is used for:
From emission focus f 1~ f kIn choose arbitrarily one the emission focus, and based on this emission focus obtain respectively corresponding to ultrasonic velocity c 1~ c nUltrasonoscopy F (c 1) ~ F (c n);
Respectively launch focus f according to what the user set 1~ f kThe position, respectively at ultrasonoscopy F (c 1) ~ F (c n) in mark off the zone corresponding to the ROI of each focus;
Calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 130192DEST_PATH_IMAGE001
~
Figure 756346DEST_PATH_IMAGE002
, its computing formula is:
P j(
Figure 81148DEST_PATH_IMAGE007
)=
Figure 185370DEST_PATH_IMAGE008
Wherein, 1≤i≤n, 1≤j≤k.
In other embodiment of the present invention, described best velocity of wave acquiring unit specifically is used for:
Traversal adopts k emission focus f 1~ f kAnd n kind ultrasonic velocity c 1~ c n, to obtain k * n frame ultrasonoscopy F j(c i);
Emission focus f according to user's setting jThe position, one by one at ultrasonoscopy F j(c 1) ~ F j(c n) in mark off emission focus f jCorresponding ROI zone;
Calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 279228DEST_PATH_IMAGE001
~ , its computing formula is:
P j(
Figure 685119DEST_PATH_IMAGE007
)= Wherein, 1≤i≤n, 1≤j≤k.
The invention has the beneficial effects as follows: by configuring a plurality of emission focuses, multiple different ultrasonic propagation velocities, and each launches the corresponding best ultrasonic propagation velocity of focus to calculate acquisition, and obtain the multiframe ultrasonoscopy based on each focus and best ultrasonic propagation velocity thereof, then the multiframe ultrasonoscopy is spliced to obtain final ultrasonoscopy.The present invention has effectively reduced the distortion factor and the clutter pseudomorphism of ultra sonic imaging, thereby has improved resolution and the verity of ultrasonoscopy, and then helps clinical actual diagnosis.
Description of drawings
Fig. 1 a is the schematic diagram of diasonograph launching circuit of the present invention;
Fig. 1 b is the schematic diagram of diasonograph receiving loop of the present invention;
Fig. 2 is the basic flow sheet of ULTRASONIC COMPLEX formation method in one embodiment of the invention;
Fig. 3 is the particular flow sheet of step S2 in the ULTRASONIC COMPLEX formation method in first embodiment of the invention;
Fig. 4 shows the ROI zone of dividing each focus in first embodiment of the invention in ultrasonoscopy;
Fig. 5 is the particular flow sheet of step S2 in the ULTRASONIC COMPLEX formation method in second embodiment of the invention;
Fig. 6 shows the ROI zone of dividing each focus in second embodiment of the invention in ultrasonoscopy;
Fig. 7 is the cell schematics of ULTRASONIC COMPLEX imaging device in one embodiment of the invention.
The specific embodiment
Describe the present invention below with reference to the specific embodiment shown in the drawings.
At first, please refer to shown in Fig. 1 a, Fig. 1 b, it has illustrated the process that in the diasonograph, signal sends and receives substantially.Wherein, the transmitter control station of diasonograph is input to probe by radiating circuit with high-voltage signal, and probe utilizes the electroacoustic transition effects that the high pressure of input is converted to ultrasound wave, and ultrasound wave enters the tissue of being diagnosed.Afterwards, the ultrasonic echo signal of tissue is converted into the signal of telecommunication via probe, pass through again amplifier and analog-digital converter (A/D) and convert digital signal to, the wave beam synthesis module superposes the echo-signal of many primitives and obtains radiofrequency signal, after the signal processing modules such as demodulation, directly send into image processing module, finally show through after Coordinate Conversion.Because improvement of the present invention does not lie in hardware, therefore no longer the hardware components of diasonograph is described in detail.
Please refer to Fig. 2 ~ shown in Figure 6, it is the specific embodiment that the present invention is based on the ULTRASONIC COMPLEX formation method of multifocal point, many velocities of wave.Wherein, as shown in Figure 2, the method comprises the steps:
S1, k emission focus f of configuration 1~ f kAnd the different ultrasonic velocity c of n kind 1~ c n
S2, based on the different ultrasonic velocity c of described n kind 1~ c n, obtain the best ultrasonic velocity of launching focus area corresponding to each according to adaptive algorithm
Figure 796294DEST_PATH_IMAGE001
~
Figure 741729DEST_PATH_IMAGE002
In conjunction with Fig. 3, shown in Figure 4, in an embodiment of the present invention, above-mentioned steps S2 specifically comprises:
S21, from emission focus f 1~ f kIn choose arbitrarily one the emission focus, and based on this emission focus obtain respectively corresponding to ultrasonic velocity c 1~ c nUltrasonoscopy F (c 1) ~ F (c n), wherein, F (c 1) ~ F (c n) expression utilizes respectively c 1~ c nPostpone and the different ultrasonoscopy of n frame that focuses on calculating and then imaging;
S22, respectively launch focus f according to what the user set 1~ f kThe position, respectively at ultrasonoscopy F (c 1) ~ F (c n) in mark off the zone corresponding to the ROI of each focus; Wherein, ROI_1 is corresponding to focus f 1, ROI_2 is corresponding to focus f 2, ROI_3 is corresponding to focus f 3, by that analogy, ROI_k is corresponding to focus f k
S23, calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 709685DEST_PATH_IMAGE001
~ , its computing formula is:
P j(
Figure 189525DEST_PATH_IMAGE007
)=
Figure 257975DEST_PATH_IMAGE008
Wherein, 1≤i≤n, 1≤j≤k.
Below enumerate the algorithm of two kinds of computed image energy, but be not limited only to this two kinds of algorithms.Continue with reference to shown in Figure 4, the first algorithm is: a ROI district inclusion ultrasonic scanning line V who supposes a frame ultrasonoscopy 0, V 1, V 2..., V m-1, V m, scanning line V j(0≤j≤m) in this ROI zone by sampled point S j0, S j1, S j2..., S jlForm G j0, G j1, G j2..., G jlExpression sampled point S j0, S j1, S j2..., S jlCorresponding image pixel (gray scale) value, remember that the energy P of this ultrasonoscopy in this ROI zone is:
；
Another kind of algorithm is: a ROI district inclusion ultrasonic scanning line V who supposes equally a frame ultrasonoscopy 0, V 1, V 2..., V m-1, V m, scanning line V j(0≤j≤m) in this ROI zone by sampled point S j0, S j1, S j2..., S jlForm, thus, we can obtain data point S 0, S 1, S 2..., S m-1, S m,
Wherein:
Figure 2013100691518100002DEST_PATH_IMAGE011
0≤j≤m, afterwards, to data point S 0, S 1, S 2..., S m-1, S mMake Fourier transform, and the spectral line that obtains after conversion is obtained the energy P of this ultrasonoscopy in this ROI zone in frequency range [f1, f2] upper integral, wherein frequency f 1 and f2 are preset value.
In conjunction with Fig. 5, shown in Figure 6, in an embodiment of the present invention, above-mentioned steps S2 specifically comprises:
S21 ', traversal adopt k emission focus f 1~ f kAnd n kind ultrasonic velocity c 1~ c n, to obtain k * n frame ultrasonoscopy F j(c i); That is to say F j(c 1), F j(c 2), F j(c 3) ..., F j(c n) be illustrated in focus f jUtilize respectively c 1~ c nPostpone and the different ultrasonoscopy of n frame that focuses on calculating and then imaging;
S22 ', the emission focus f that sets according to the user j(position of 0≤j≤k) is one by one at ultrasonoscopy F j(c 1) ~ F j(c n) in mark off emission focus f jCorresponding ROI zone; Particularly, at ultrasonoscopy F 1(c 1), F 1(c 2) ..., F 1(c n) on all mark off regional ROI_1, at ultrasonoscopy F 2(c 1), F 2(c 2) ..., F 2(c n) on all mark off regional ROI_2, by that analogy, at ultrasonoscopy F k(c 1), F k(c 2) ..., F k(c n) on all mark off regional ROI_k, wherein, ROI_1 is corresponding to focus f 1, ROI_2 is corresponding to focus f 2, ROI_K is corresponding to focus f k
S23 ', calculate the image energy P in each ROI zone j(c i) (algorithm as mentioned), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 917944DEST_PATH_IMAGE001
~
Figure 105342DEST_PATH_IMAGE002
, its computing formula is:
P j(
Figure 90616DEST_PATH_IMAGE007
)=
Figure 338058DEST_PATH_IMAGE008
Wherein, 1≤i≤n, 1≤j≤k.
Getting the best ultrasonic propagation velocity of each focus area
Figure 408782DEST_PATH_IMAGE001
~
Figure 399872DEST_PATH_IMAGE002
After, can enter step S3:
S3, based on emission focus f 1~ f kAnd corresponding best ultrasonic velocity
Figure 239652DEST_PATH_IMAGE001
~
Figure 720312DEST_PATH_IMAGE002
Destination organization is carried out scanning, with obtain the elementary ultrasonoscopy F of k frame (
Figure 950436DEST_PATH_IMAGE003
) ~ F ( );
S4, the elementary ultrasonoscopy of k frame that gets is spliced, to obtain final ultrasonoscopy F, its splicing principle is: if image-region mainly is positioned at focus f xThe place, F=F ( ); If image-region is positioned at focus f yAnd focus f zSplicing place, F=k * F (
Figure 93994DEST_PATH_IMAGE005
)+(1-k) * F (
Figure 76993DEST_PATH_IMAGE006
); Wherein, 1≤x≤k, 1≤y≤k, 1≤z≤k, k 〉=2.Certainly, above-mentioned is only a kind of exemplary embodiment, and in other examples of the present invention, ultrasonoscopy also can splice according to other modes.
Next, please refer to shown in Figure 7ly, it is the cell schematics of the ULTRASONIC COMPLEX imaging device of the multifocal point of the present invention, many spread speeds.Wherein, device embodiment described herein is only schematically, and the concrete technical characterictic in device embodiment of the present invention, function, technique effect etc., please refer to the embodiment of the method for putting down in writing in literary composition, is hereinafter no longer given unnecessary details.
In embodiments of the present invention, described device comprises:
Dispensing unit 10, be used for k of configuration and launch focus f 1~ f kAnd the different ultrasonic velocity c of n kind 1~ c n
Best velocity of wave acquiring unit 20, be used for based on the different ultrasonic velocity c of described n kind 1~ c n, calculate to obtain the best ultrasonic velocity corresponding to each emission focus area
Figure 409886DEST_PATH_IMAGE001
~
Image acquisition unit 30, be used for based on emission focus f 1~ f kAnd corresponding best ultrasonic velocity ~
Figure 251437DEST_PATH_IMAGE002
Destination organization is carried out scanning, with obtain the elementary ultrasonoscopy F of k frame (
Figure 184758DEST_PATH_IMAGE003
) ~ F (
Figure 791320DEST_PATH_IMAGE002
);
Image mosaic unit 40, be used for the elementary ultrasonoscopy of k frame that gets is spliced, to obtain final ultrasonoscopy F, its splicing principle is: if image-region mainly is positioned at focus f xThe place, F=F (
Figure 50263DEST_PATH_IMAGE004
); If image-region is positioned at focus f yAnd focus f zSplicing place, F=k * F ( )+(1-k) * F (
Figure 416970DEST_PATH_IMAGE006
); Wherein, 1≤x≤k, 1≤y≤k, 1≤z≤k, k 〉=2.
In sum, method of the present invention and device are by a plurality of emission focuses of configuration, multiple different ultrasonic propagation velocities, and each launches the corresponding best ultrasonic propagation velocity of focus to calculate acquisition, and obtain the multiframe ultrasonoscopy based on each focus and best ultrasonic propagation velocity thereof, then the multiframe ultrasonoscopy is spliced to obtain final ultrasonoscopy.The present invention has effectively reduced the distortion factor and the clutter pseudomorphism of ultra sonic imaging, thereby has improved resolution and the verity of ultrasonoscopy, and then helps clinical actual diagnosis.
Be to be understood that, although this description is described according to embodiment, but be not that each embodiment only comprises an independently technical scheme, this narrating mode of description is only for clarity sake, those skilled in the art should make description as a whole, technical scheme in each embodiment also can through appropriate combination, form other embodiments that it will be appreciated by those skilled in the art that.
Above listed a series of detailed description is only illustrating for feasibility embodiment of the present invention; they are not to limit protection scope of the present invention, all disengaging within equivalent embodiment that skill spirit of the present invention does or change all should be included in protection scope of the present invention.

Claims (6)

1. the ULTRASONIC COMPLEX formation method based on multifocal point, many velocities of wave, is characterized in that, the method comprises the steps:
S1, k emission focus f of configuration 1~ f kAnd the different ultrasonic velocity c of n kind 1~ c n
S2, based on the different ultrasonic velocity c of described n kind 1~ c n, calculate to obtain the best ultrasonic velocity corresponding to each emission focus area
Figure 2013100691518100001DEST_PATH_IMAGE002
~
S3, based on emission focus f 1~ f kAnd corresponding best ultrasonic velocity
Figure 215618DEST_PATH_IMAGE002
~
Figure 843040DEST_PATH_IMAGE004
Destination organization is carried out scanning, with obtain the elementary ultrasonoscopy F of k frame (
Figure 2013100691518100001DEST_PATH_IMAGE006
) ~ F (
Figure 462240DEST_PATH_IMAGE004
);
S4, the elementary ultrasonoscopy of k frame that gets is spliced, to obtain final ultrasonoscopy F, its splicing principle is: if image-region mainly is positioned at focus f xThe place, F=F (
Figure 2013100691518100001DEST_PATH_IMAGE008
); If image-region is positioned at focus f yAnd focus f zSplicing place, F=k * F (
Figure 2013100691518100001DEST_PATH_IMAGE010
)+(1-k) * F (
Figure 2013100691518100001DEST_PATH_IMAGE012
); Wherein, 1≤x≤k, 1≤y≤k, 1≤z≤k, k 〉=2.
2. method according to claim 1, is characterized in that, step S2 specifically comprises:
S21, from emission focus f 1~ f kIn choose arbitrarily one the emission focus, and based on this emission focus obtain respectively corresponding to ultrasonic velocity c 1~ c nUltrasonoscopy F (c 1) ~ F (c n);
S22, respectively launch focus f according to what the user set 1~ f kThe position, respectively at ultrasonoscopy F (c 1) ~ F (c n) in mark off the zone corresponding to the ROI of each focus;
S23, calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 870219DEST_PATH_IMAGE002
~
Figure 69119DEST_PATH_IMAGE004
, its computing formula is:
P j(
Figure 2013100691518100001DEST_PATH_IMAGE014
)=
Figure 2013100691518100001DEST_PATH_IMAGE016
Wherein, 1≤i≤n, 1≤j≤k.
3. method according to claim 1, is characterized in that, step S2 specifically comprises:
S21 ', traversal adopt k emission focus f 1~ f kAnd n kind ultrasonic velocity c 1~ c n, to obtain k * n frame ultrasonoscopy F j(c i);
S22 ', the emission focus f that sets according to the user jThe position, one by one at ultrasonoscopy F j(c 1) ~ F j(c n) in mark off emission focus f jCorresponding ROI zone;
S23 ', calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 610434DEST_PATH_IMAGE002
~
Figure 603798DEST_PATH_IMAGE004
, its computing formula is:
P j(
Figure 171177DEST_PATH_IMAGE014
)=
Figure 908189DEST_PATH_IMAGE016
；
Wherein, 1≤i≤n, 1≤j≤k.
4. the ULTRASONIC COMPLEX imaging device based on multifocal point, many velocities of wave, is characterized in that, comprising:
Dispensing unit, be used for k of configuration and launch focus f 1~ f kAnd the different ultrasonic velocity c of n kind 1~ c n
Best velocity of wave acquiring unit, be used for based on the different ultrasonic velocity c of described n kind 1~ c n, calculate to obtain the best ultrasonic velocity corresponding to each emission focus area
Figure 493891DEST_PATH_IMAGE002
~
Image acquisition unit, be used for based on emission focus f 1~ f kAnd corresponding best ultrasonic velocity
Figure 165361DEST_PATH_IMAGE002
~
Figure 253533DEST_PATH_IMAGE004
Destination organization is carried out scanning, with obtain the elementary ultrasonoscopy F of k frame (
Figure 897004DEST_PATH_IMAGE006
) ~ F (
Figure 28908DEST_PATH_IMAGE004
);
The image mosaic unit, be used for the elementary ultrasonoscopy of k frame that gets is spliced, to obtain final ultrasonoscopy F, its splicing principle is: if image-region mainly is positioned at focus f xThe place, F=F (
Figure 757830DEST_PATH_IMAGE008
); If image-region is positioned at focus f yAnd focus f zSplicing place, F=k * F ( )+(1-k) * F (
Figure 413250DEST_PATH_IMAGE012
); Wherein, 1≤x≤k, 1≤y≤k, 1≤z≤k, k 〉=2.
5. device according to claim 4, is characterized in that, described best velocity of wave acquiring unit specifically is used for:
From emission focus f 1~ f kIn choose arbitrarily one the emission focus, and based on this emission focus obtain respectively corresponding to ultrasonic velocity c 1~ c nUltrasonoscopy F (c 1) ~ F (c n);
Respectively launch focus f according to what the user set 1~ f kThe position, respectively at ultrasonoscopy F (c 1) ~ F (c n) in mark off the zone corresponding to the ROI of each focus;
Calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 247214DEST_PATH_IMAGE002
~
Figure 197853DEST_PATH_IMAGE004
, its computing formula is:
P j(
Figure 630758DEST_PATH_IMAGE014
)= Wherein, 1≤i≤n, 1≤j≤k.
6. device according to claim 4, is characterized in that, described best velocity of wave acquiring unit specifically is used for:
Traversal adopts k emission focus f 1~ f kAnd n kind ultrasonic velocity c 1~ c n, to obtain k * n frame ultrasonoscopy F j(c i);
Emission focus f according to user's setting jThe position, one by one at ultrasonoscopy F j(c 1) ~ F j(c n) in mark off emission focus f jCorresponding ROI zone;
Calculate the image energy P in each ROI zone j(c i), and best ultrasonic velocity corresponding to each emission focus area definite according to drawn image energy
Figure 253686DEST_PATH_IMAGE002
~
Figure 691621DEST_PATH_IMAGE004
, its computing formula is:
P j( )=
Figure 397857DEST_PATH_IMAGE016
；
Wherein, 1≤i≤n, 1≤j≤k.
CN2013100691518A 2013-03-05 2013-03-05 Method and device for compound ultrasonic imaging based on multiple focuses and multiple ultrasonic velocities Pending CN103126721A (en)

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CN110930465A (en) * 2019-11-29 2020-03-27 京东方科技集团股份有限公司 Ultrasonic imaging method and equipment
WO2021103493A1 (en) * 2019-11-27 2021-06-03 深圳开立生物医疗科技股份有限公司 Shear wave-based imaging method, system and apparatus

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