CN109674491A - Ultrasonic imaging wide-beam transmission method and emission system - Google Patents
Ultrasonic imaging wide-beam transmission method and emission system Download PDFInfo
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- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
- A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
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Abstract
The present invention provides a kind of ultrasonic imaging wide-beam transmission methods, which comprises multiple focuses equidistantly arranged are set gradually along depth direction in transmitting line position；To emit line position as midpoint, each probe primitive symmetrically arranged two-by-two in its two sides is made to be respectively formed one group of probe primitive group, and each probe primitive group is made successively to focus on each set focus by distributing order；Wherein, the nearest probe primitive group in range transmission line position midpoint corresponds to focus with the shallowest depth, and the farthest probe primitive group in range transmission line position midpoint corresponds to focus with the deepest depth.Ultrasonic imaging wide-beam transmission method of the invention and emission system, broad beam transmitting may be implemented, and each focus on depth direction is successively focused on by symmetrically probe primitive, and make beam angle on depth direction and energy uniformity preferable, thus obtain it is close, in, far field grayscale and the preferable ultrasound image of resolution ratio consistency.
Description
Technical field
The invention belongs to medical ultrasound diagnostic imaging field more particularly to a kind of ultrasonic imaging wide-beam transmission methods and hair
Penetrate system.
Background technique
Ultrasonic imaging becomes clinic because of many advantages such as its non-invasive, real-time, easy to operate, cheap
On one of the diagnostic tool that is most widely used.The common functional mode of ultrasonic imaging is more including two-dimentional black and white (B) mode, frequency spectrum
General Le mode (PW/CW) and colorflow mode (CF/PDI).B-mode dependent on ultrasound echo signal amplitude carry out at
Picture, acquisition is tissue two-dimensional structure and shape information, and the more big then corresponding image pixel gray level value of echo signal intensity is bigger,
It is on the contrary then gray value is smaller；The basic principle of PW/CW and CF/PDI mode is all Doppler effect, all relies on ultrasonic echo
The phase of signal is imaged, and acquisition is the blood flow informations such as speed, direction, energy.
The core component of supersonic imaging apparatus includes: probe, probe plate, transmitting/receiver board, transmitting/reception control panel, wave
Beamformer, signal and image processing unit, display, groundwork process is: probe transmitting focusing ultrasonic beam, probe
Different primitives receive ultrasound and return super signal and amplify, be filtered into each channel, and channel level signal carries out wave beam
Synthesis obtains radiofrequency signal (RF signal), repeats above-mentioned scanning process until obtaining a frame radiofrequency signal of a routing density, penetrates
The demodulated filtering processing of frequency signal obtains orthogonal signalling (I/Q signal), and orthogonal signalling obtain image by processing, and image passes through
Post-processing is finally shown through display.
The usual scanning of early stage ultrasonic imaging can be only formed a piece-root grafting take-up of same position, thus picture frame frequency compared with
Low, the parallel beam technology occurred later realizes a scanning and obtains more piece-root grafting take-ups of close position, substantially increases figure
As frame frequency.In recent years, due to the development of electronic technology and computer technology, a scanning can form up to 16 piece-root grafting take-ups.
Conventional ultrasound usually emits single focus focused ultrasound beams when scanning is imaged, and causes energy and resolution ratio on depth direction uneven
Even, energy near Jiao Qu is higher, resolution ratio is preferable, and the energy other than Jiao Qu is lower, resolution ratio is poor；And single focus is poly-
Burnt ultrasonic beam is in strong-focusing in burnt zone position, and wave beam is relatively narrow, can not cover more piece-root grafting take-ups, is not particularly suited for more reception line
Parallel beam technology.In order to solve this problem, it needs to design a kind of wide-beam transmission method, transmitting sound field is covered more
Piece-root grafting take-up.
In existing technical solution one, notification number " CN101190133A ", denomination of invention " wide wave in ultrasonic diagnostic system
The launching technique and device of beam " discloses a kind of technology for realizing broad beam transmitting, and the program is by the transmitting aperture of ultrasonic probe
It is divided into N number of sub-aperture, and by focus transversally cutting is N number of sub- focus, N number of sub-aperture and N number of sub- focus is established and corresponded
Relationship, each sub-aperture have M array element, all focus on sub- focus corresponding with the aperture, impulse generator excitation ultrasound
N number of sub-aperture of probe obtains a transmitting sound field stretching in the transverse direction, and the transmitting sound field of N number of sub-aperture is respectively in its corresponding son
Superimposed after focal point, all sound fields for receiving line width wave beam can be covered by eventually forming one；Wherein, N and M is greater than 2
Integer.Method of the program by being superimposed sound field to probe division sub-aperture and after focusing each sub-aperture respectively, so that
The broad beams that transmitting unipolarity or the ultrasound machine launch energy of bipolarity transmitted waveform cover all reception line ranges become can
Energy.Transmitting aperture is divided into several sub-apertures by above scheme one, and each sub-aperture focuses on different transverse direction positions in same depth
The focus set, the corresponding wherein piece-root grafting take-up in position where each focus.Therefore, the purpose is to every time emitting
Sound field energy is evenly distributed in adjacent more piece-root grafting take-ups, guarantees that parallel received more piece-root grafting take-ups have more uniform energy
Amount, which still shows strong-focusing in focal position, although having stronger energy and preferable in the depth of focus
Resolution ratio, but energy then dies down other than the depth of focus and resolution ratio is deteriorated, performance be exactly on the image closely, in, the ash in far field
Rank and resolution ratio consistency are bad.
In existing technical solution two, notification number " CN101396282A ", " circular arc for ultrasonic imaging is wide for denomination of invention
Beam transmission method and apparatus " discloses another technology for realizing broad beam transmitting.Program setting focuses the parameter of circular arc,
And the parameter based on set focusing circular arc, the emission delay for calculating each array element in probe transmitting aperture control each array element transmitting
Ultrasonic wave.The program is focused using circular arc, strong-focusing emission delay calculation method is changed, so that wave beam is no longer focused to
A bit, to obtain broad beam.Prior art two becomes transmitting focus to focus circular arc, and the purpose is to the sound emitted every time
Field energy, which is evenly distributed to, to be focused on circular arc, increases launching beam width to guarantee that parallel received more piece-root grafting take-ups have more
Uniform energy；The technology is focusing circular arc depth with stronger energy and preferable resolution ratio, but deep focusing circular arc
Then energy dies down other than degree and resolution ratio is deteriorated, performance be exactly on the image closely, in, the grayscale in far field and resolution ratio consistency not
It is good.
Summary of the invention
In order to solve the above technical problems, the purpose of the present invention is to provide a kind of ultrasonic imaging wide-beam transmission method and hairs
Shooting method.
One of in order to achieve the above-mentioned object of the invention, an embodiment of the present invention provides a kind of ultrasonic imaging wide-beam transmission
Method, which comprises multiple focuses equidistantly arranged are set gradually along depth direction in transmitting line position；
To emit line position as midpoint, each probe primitive symmetrically arranged two-by-two in its two sides is made to be respectively formed one group of probe
Primitive group, and each probe primitive group is made successively to focus on each set focus by distributing order；
Wherein, the nearest probe primitive group in range transmission line position midpoint corresponds to focus with the shallowest depth, distance hair
The farthest probe primitive group in ray position midpoint corresponds to focus with the deepest depth.
As the further improvement of an embodiment of the present invention, the method also includes:
It is obtained according to the depth of the distance of probe primitive range transmission line and/or angle and the corresponding focus of probe primitive
Every group of probe primitive group is taken to correspond to the emission delay of transmission channel；
In imaging process, each probe primitive group is by transmission channel according to its corresponding emission delay transmitting ultrasound letter
Number and focus on the focus corresponding to it.
As the further improvement of an embodiment of the present invention, " according to the distance of probe primitive range transmission line and/or angle
The depth of degree and the corresponding focus of probe primitive obtains the emission delay that every group of probe primitive group corresponds to transmission channel " it is specific
Include:
If probe is linear array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and c is
The spread speed of ultrasonic wave.
As the further improvement of an embodiment of the present invention, " according to the distance of probe primitive range transmission line and/or angle
The depth of degree and the corresponding focus of probe primitive obtains the emission delay that every group of probe primitive group corresponds to transmission channel " it is specific
Include:
If probe is that arc battle array is popped one's head in, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt ((Fm+ROC) 2+ROC2-2* (Fm+ROC) * ROC*cos (θ)))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and ROC is the radius of curvature of probe primitive i, and θ is probe primitive
Deflection angle of the i from emission lines, c are the spread speed of ultrasonic wave.
As the further improvement of an embodiment of the present invention, " according to the distance of probe primitive range transmission line and/or angle
The depth of degree and the corresponding focus of probe primitive obtains the emission delay that every group of probe primitive group corresponds to transmission channel " it is specific
Include:
If probe is phased array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2-2*Fm*dx*cos (pi/2-θ)))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and θ is
Emission lines deflection angle, c are the spread speed of ultrasonic wave.
As the further improvement of an embodiment of the present invention, the method also includes:
If the emission delay obtained is negative, the emission delay delay (i) is converted into positive number,
Delay (i)=delay (i)+abs (min (delay)),
Wherein, min (delay) indicates to take the negative minimum in delay array, and abs () expression asks exhausted to the number in bracket
To value.
Another in order to solve foregoing invention purpose, an embodiment of the present invention provides a kind of ultrasonic imaging broad beam transmitting system
System multiple is equidistantly arranged for setting gradually along depth direction in transmitting line position the system comprises configuration module
Focus；
Focusing module, for emit line position as midpoint, making each probe primitive symmetrically arranged two-by-two in its two sides point
One group of probe primitive group is not formed, and it is burnt so that each probe primitive group is successively focused on each set by distributing order
Point；
Wherein, the nearest probe primitive group in range transmission line position midpoint corresponds to focus with the shallowest depth, distance hair
The farthest probe primitive group in ray position midpoint corresponds to focus with the deepest depth.
As the further improvement of an embodiment of the present invention, the system also includes: delay process module is used for basis
The distance of primitive range transmission line of popping one's head in and/or depth every group of probe base of acquisition of angle and the corresponding focus of probe primitive
Tuple corresponds to the emission delay of transmission channel；
In imaging process, each probe primitive group is by transmission channel according to its corresponding emission delay transmitting ultrasound letter
Number and focus on the focus corresponding to it.
As the further improvement of an embodiment of the present invention, the delay process module is specifically used for:
If probe is linear array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and c is
The spread speed of ultrasonic wave.
As the further improvement of an embodiment of the present invention, the delay process module is specifically used for:
If probe is that arc battle array is popped one's head in, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt ((Fm+ROC) 2+ROC2-2* (Fm+ROC) * ROC*cos (θ)))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and ROC is the radius of curvature of probe primitive i, and θ is probe primitive
Deflection angle of the i from emission lines, c are the spread speed of ultrasonic wave.
As the further improvement of an embodiment of the present invention, the delay process module is specifically used for:
If probe is phased array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2-2*Fm*dx*cos (pi/2-θ)))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and θ is
Emission lines deflection angle, c are the spread speed of ultrasonic wave.
As the further improvement of an embodiment of the present invention, the delay process module is specifically used for:
If the emission delay obtained is negative, the emission delay delay (i) is converted into positive number,
Delay (i)=delay (i)+abs (min (delay)),
Wherein, min (delay) indicates to take the negative minimum in delay array, and abs () expression asks exhausted to the number in bracket
To value.
Compared with prior art, the beneficial effects of the present invention are: ultrasonic imaging wide-beam transmission method of the invention and hair
System is penetrated, broad beam transmitting may be implemented, and each focus on depth direction is successively focused on by symmetrically probe primitive,
And make beam angle on depth direction and energy uniformity preferable, thus obtain it is close, in, far field grayscale it is consistent with resolution ratio
The preferable ultrasound image of property.
Detailed description of the invention
Fig. 1 is the flow diagram of the ultrasonic imaging wide-beam transmission method of an embodiment of the present invention；
Fig. 2 is the structural schematic diagram that probe primitive and focus correspond to focus in a specific example of the invention；
Fig. 3 is the flow diagram of the ultrasonic imaging wide-beam transmission method of better embodiment of the present invention；
Fig. 4 figure is that the transmitting sound field comparison of the transmitting sound field and one embodiment of the invention of traditional single focus type of focusing is illustrated
Figure；
Fig. 5 is the module diagram of ultrasonic imaging broad beam emission system in an embodiment of the present invention.
Specific embodiment
Below with reference to specific embodiment shown in the drawings, the present invention will be described in detail.But these embodiments are simultaneously
The present invention is not limited, structure that those skilled in the art are made according to these embodiments, method or functionally
Transformation is included within the scope of protection of the present invention.
As shown in Figure 1, providing a kind of ultrasonic imaging wide-beam transmission method, the method packet in an embodiment of the present invention
It includes: setting gradually multiple focuses equidistantly arranged along depth direction in transmitting line position；To emit line position as midpoint, make
The each probe primitive symmetrically arranged two-by-two in its two sides is respectively formed one group of probe primitive group, and makes each probe primitive group by row
Cloth sequence successively focuses on each set focus；Wherein, the nearest probe primitive group pair in range transmission line position midpoint
Focus with the shallowest depth is answered, the farthest probe primitive group in range transmission line position midpoint corresponds to coke with the deepest depth
Point.
As shown in Fig. 2, top filled box indicates probe primitive 10, vertical side in diagram in a specific example of the invention
Indicate that emission lines 20, filled circles indicate focus point 30 to the vertical dotted line of (i.e. depth direction), symmetrical primitive 10 of popping one's head in is by inclining
Oblique dotted line is connected to its same focus focused two-by-two.
Connect above-mentioned example, it is assumed that the probe primitive quantity of transmitting aperture is N, sets gradually M=floor along depth direction
(N/2) a focus arranged at equal interval, floor indicate to be rounded downwards, then the depth of m-th of focus is represented by Fm=Fstart
+ (m-1) * (Fend-Fstart)/(M-1), wherein Fstart indicates that first focus is to originate the position of focus, and Fend is indicated
The last one focus is to terminate the position of focus, and the value of m is 1 to any integer between M, and the quantity for primitive of popping one's head in is usually not
It is fixed, it can may be even number for odd number, in present embodiment, by being rounded downwards, each probe primitive can be realized
Pairing.
In specific example of the present invention, as shown in Fig. 2, the quantity of probe primitive is 18, symmetrically probe primitive divides two-by-two
It is one group, is divided into 9 groups of probe primitive groups, it is most shallow on depth direction correspondingly, 9 focuses of spaced set on depth direction
Focus be starting focus, most deep focus be terminate focus；Wherein, according to its position of arranging, the 1st probe primitive and the 18th
A probe primitive forms a probe primitive group, and focuses on the 9th focus with the deepest depth on depth direction, and the 9th
It pops one's head in primitive and the 10th probe primitive one probe primitive group of formation, and focuses on the shallowest depth the on depth direction
1 focus.
Further, as shown in connection with fig. 3, in better embodiment of the present invention, the method also includes: according to probe primitive
It is corresponding that the distance and/or angle of range transmission line and the depth of the corresponding focus of probe primitive obtain every group of probe primitive group
The emission delay of transmission channel；In imaging process, each probe primitive group is prolonged by transmission channel according to its corresponding transmitting
When transmitting ultrasonic signal and focus on the focus corresponding to it.
In better embodiment of the present invention, the factor for influencing emission delay further includes the type of probe, such as: linear array is visited
Head, arc battle array probe, phased array probe, are made a concrete analysis of below.
It in first embodiment of the invention, pops one's head in as linear array probe, then the corresponding emission delay of primitive of popping one's head in indicates are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2))/c；
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and c is
The spread speed of ultrasonic wave.
In second embodiment of the invention, pop one's head in as arc battle array probe, then the corresponding emission delay of primitive of popping one's head in indicates are as follows:
Delay (i)=(Fm-sqrt ((Fm+ROC)2+ROC2–2*(Fm+ROC)*ROC*cos(θ)))/c；
Wherein, Fm is the corresponding depth of focus of probe primitive i, and ROC is the radius of curvature of probe primitive i, and θ is probe primitive
Deflection angle of the i from emission lines, c are the spread speed of ultrasonic wave.
It in third embodiment of the invention, pops one's head in as phased array probe, then the corresponding emission delay of primitive of popping one's head in indicates are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2–2*Fm*dx*cos(π/2-θ)))/c；
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and θ is
Emission lines deflection angle, c are the spread speed of ultrasonic wave.
In practical application, the emission delay of acquisition is largely negative, at this point, for actual demand, if the transmitting obtained
Delay is negative, then the emission delay delay (i) is converted to positive number, i.e., is converted by following formula, delay (i)
=delay (i)+abs (min (delay))；
Wherein, min (delay) indicates to take the negative minimum in delay array, and abs () expression asks exhausted to the number in bracket
To value.
In imaging process, the emission delay calculated can be sent to hardware layer, hardware layer controls each probe primitive
Corresponding transmission channel goes out ultrasonic signal according to corresponding delay emission, reaches expected focusing effect.
As shown in connection with fig. 4, in a specific example of the invention, by the transmitting sound field of traditional single focus type of focusing and the present invention
The transmitting sound field of one specific example compares, it was found from diagram: the transmitting sound field of traditional single focus type of focusing is in " hourglass "
The strong-focusing of shape, the beam angle of Jiao Qu is narrow, energy is strong, good resolution, and Jiao Qu is outer, and beam angle broadens, energy dies down, divides
Resolution is deteriorated；And transmitting sound field of the invention is in weak focus, and although sacrificing the resolution ratio of a part of former burnt zone position, whole field
Beam angle, energy uniformity and resolution ratio consistency it is preferable.
As above, the mode that single focus on traditional depth direction focuses is become multiple-point focusing (similar to line by the present invention
Focus) mode, greatly improve the width of launching beam, transmitting sound field enabled to cover more piece-root graftings of parallel beam technology
Take-up, although sacrificing the image resolution ratio of a part of burnt zone position, improve it is close, in, the energy uniformity in far field with
Resolution ratio consistency improves the performance of ultrasound image to a certain extent.
As shown in connection with fig. 5, an embodiment of the present invention provides a kind of ultrasonic imaging broad beam emission system, the system packet
It includes: configuration module 100, Focusing module 200 and delay process module 300.
Configuration module 100 is used to set gradually multiple focuses equidistantly arranged along depth direction in transmitting line position.
Focusing module 200 is used to make each probe primitive symmetrically arranged two-by-two in its two sides to emit line position as midpoint
It is respectively formed one group of probe primitive group, and it is burnt so that each probe primitive group is successively focused on each set by distributing order
Point；Wherein, the nearest probe primitive group in range transmission line position midpoint corresponds to focus with the shallowest depth, range transmission line position
It sets the farthest probe primitive group in midpoint and corresponds to focus with the deepest depth.
Delay process module 300 is used for distance and/or angle and probe primitive according to probe primitive range transmission line
The depth of corresponding focus obtains the emission delay that every group of probe primitive group corresponds to transmission channel；In imaging process, each spy
Head primitive group emits ultrasonic signal according to its corresponding emission delay by transmission channel and focuses on the focus corresponding to it.
In better embodiment of the present invention, the factor for influencing emission delay further includes the type of probe, such as: linear array is visited
Head, arc battle array probe, phased array probe, are made a concrete analysis of below.
The delay process module 300 is specifically used for: if probe is linear array probe, the corresponding emission delay of primitive of popping one's head in
It indicates are as follows: delay (i)=(Fm-sqrt (Fm2+dx2))/c, wherein Fm is the corresponding depth of focus of probe primitive i, and dx is to visit
Head lateral distance of the primitive i from emission lines, c are the spread speed of ultrasonic wave.
If probe is that arc battle array is popped one's head in, the corresponding emission delay of primitive of popping one's head in is indicated are as follows: delay (i)=(Fm-sqrt
((Fm+ROC)2+ROC2- 2* (Fm+ROC) * ROC*cos (θ)))/c, wherein Fm is the corresponding depth of focus of probe primitive i, ROC
For the radius of curvature for the primitive i that pops one's head in, θ is probe deflection angle of the primitive i from emission lines, and c is the spread speed of ultrasonic wave.
If probe is phased array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows: delay (i)=(Fm-sqrt
(Fm2+dx2- 2*Fm*dx*cos (pi/2-θ)))/c, wherein Fm is the corresponding depth of focus of probe primitive i, and dx is probe primitive i
Lateral distance from emission lines, θ are emission lines deflection angle, and c is the spread speed of ultrasonic wave.
In practical application, the emission delay of acquisition is largely negative, at this point, for actual demand, preferably, described prolong
When processing module 300 be also used to: if obtain emission delay be negative, by the emission delay delay (i) conversion be positive
Number, i.e., converted, delay (i)=delay (i)+abs (min (delay)) by following formula；Wherein, min (delay)
It indicates to take the negative minimum in delay array, abs () expression seeks absolute value to the number in bracket.
Further, the emission delay that delay process module 300 is also used to calculate is sent to hardware layer, hardware layer control
The corresponding transmission channel of each probe primitive goes out ultrasonic signal according to corresponding delay emission, reaches expected focusing effect.
It is apparent to those skilled in the art that for convenience and simplicity of description, the system of foregoing description
Specific work process, can be with reference to the corresponding process in preceding method embodiment, details are not described herein.
In conclusion ultrasonic imaging wide-beam transmission method of the invention and emission system, may be implemented broad beam transmitting,
And each focus on depth direction is successively focused on by symmetrically probe primitive, and make the beam angle on depth direction
It is preferable with energy uniformity, thus obtain it is close, in, far field grayscale and the preferable ultrasound image of resolution ratio consistency.
For convenience of description, it is divided into various modules when description apparatus above with function to describe respectively.Certainly, implementing this
The function of each module can be realized in the same or multiple software and or hardware when invention.
Device embodiments described above are only schematical, wherein the module as illustrated by the separation member
It may or may not be physically separated, the component shown as module may or may not be physics mould
Block, it can it is in one place, or may be distributed on multiple network modules.It can be selected according to the actual needs
In some or all of the modules realize the purpose of present embodiment scheme.Those of ordinary skill in the art are not paying creation
Property labour in the case where, it can understand and implement.
It should be appreciated that although this specification is described in terms of embodiments, but not each embodiment only includes one
A independent technical solution, this description of the specification is merely for the sake of clarity, and those skilled in the art should will say
As a whole, the technical solution in each embodiment may also be suitably combined to form those skilled in the art can for bright book
With the other embodiments of understanding.
The series of detailed descriptions listed above only for feasible embodiment of the invention specifically
Protection scope bright, that they are not intended to limit the invention, it is all without departing from equivalent implementations made by technical spirit of the present invention
Or change should all be included in the protection scope of the present invention.
Claims (12)
1. a kind of ultrasonic imaging wide-beam transmission method, which is characterized in that the described method includes:
Multiple focuses equidistantly arranged are set gradually along depth direction in transmitting line position；
To emit line position as midpoint, each probe primitive symmetrically arranged two-by-two in its two sides is made to be respectively formed one group of probe primitive
Group, and each probe primitive group is made successively to focus on each set focus by distributing order；
Wherein, the nearest probe primitive group in range transmission line position midpoint corresponds to focus with the shallowest depth, range transmission line
The farthest probe primitive group in position midpoint corresponds to focus with the deepest depth.
2. ultrasonic imaging wide-beam transmission method according to claim 1, which is characterized in that the method also includes:
It is obtained according to the depth of the distance of probe primitive range transmission line and/or angle and the corresponding focus of probe primitive every
Group probe primitive group corresponds to the emission delay of transmission channel；
In imaging process, each probe primitive group emits ultrasonic signal simultaneously according to its corresponding emission delay by transmission channel
Focus on the focus corresponding to it.
3. ultrasonic imaging wide-beam transmission method according to claim 2, which is characterized in that " according to probe primitive distance
The distance and/or angle of emission lines and the depth of the corresponding focus of probe primitive obtain the corresponding transmitting of every group of probe primitive group
The emission delay in channel " specifically includes:
If probe is linear array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and c is ultrasound
The spread speed of wave.
4. ultrasonic imaging wide-beam transmission method according to claim 2, which is characterized in that " according to probe primitive distance
The distance and/or angle of emission lines and the depth of the corresponding focus of probe primitive obtain the corresponding transmitting of every group of probe primitive group
The emission delay in channel " specifically includes:
If probe is that arc battle array is popped one's head in, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt ((Fm+ROC)2+ROC2- 2* (Fm+ROC) * ROC*cos (θ)))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and ROC be the radius of curvature of primitive i of popping one's head in, θ be pop one's head in primitive i from
The deflection angle of emission lines, c are the spread speed of ultrasonic wave.
5. ultrasonic imaging wide-beam transmission method according to claim 2, which is characterized in that " according to probe primitive distance
The distance and/or angle of emission lines and the depth of the corresponding focus of probe primitive obtain the corresponding transmitting of every group of probe primitive group
The emission delay in channel " specifically includes:
If probe is phased array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2- 2*Fm*dx*cos (pi/2-θ)))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and θ is transmitting
Line deflection angle, c are the spread speed of ultrasonic wave.
6. according to ultrasonic imaging wide-beam transmission method described in any one in claim 3 to 5, which is characterized in that institute
State method further include:
If the emission delay obtained is negative, the emission delay delay (i) is converted into positive number,
Delay (i)=delay (i)+abs (min (delay)),
Wherein, min (delay) indicates to take the negative minimum in delay array, and abs () expression seeks absolute value to the number in bracket.
7. a kind of ultrasonic imaging broad beam emission system, which is characterized in that the system comprises:
Configuration module, for setting gradually multiple focuses equidistantly arranged along depth direction in transmitting line position；
Focusing module, for emit line position as midpoint, making each probe primitive difference shape symmetrically arranged two-by-two in its two sides
At one group of probe primitive group, and each probe primitive group is made successively to focus on each set focus by distributing order；
Wherein, the nearest probe primitive group in range transmission line position midpoint corresponds to focus with the shallowest depth, range transmission line
The farthest probe primitive group in position midpoint corresponds to focus with the deepest depth.
8. ultrasonic imaging broad beam emission system according to claim 7, which is characterized in that the system also includes: prolong
When processing module, for according to the distance and/or angle of probe primitive range transmission line and the corresponding focus of probe primitive
Depth obtains the emission delay that every group of probe primitive group corresponds to transmission channel；
In imaging process, each probe primitive group emits ultrasonic signal simultaneously according to its corresponding emission delay by transmission channel
Focus on the focus corresponding to it.
9. ultrasonic imaging broad beam emission system according to claim 8, which is characterized in that the delay process module tool
Body is used for:
If probe is linear array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and c is ultrasound
The spread speed of wave.
10. ultrasonic imaging broad beam emission system according to claim 8, which is characterized in that the delay process module
It is specifically used for:
If probe is that arc battle array is popped one's head in, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt ((Fm+ROC)2+ROC2- 2* (Fm+ROC) * ROC*cos (θ)))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and ROC be the radius of curvature of primitive i of popping one's head in, θ be pop one's head in primitive i from
The deflection angle of emission lines, c are the spread speed of ultrasonic wave.
11. ultrasonic imaging broad beam emission system according to claim 8, which is characterized in that the delay process module
It is specifically used for:
If probe is phased array probe, the corresponding emission delay of primitive of popping one's head in is indicated are as follows:
Delay (i)=(Fm-sqrt (Fm2+dx2- 2*Fm*dx*cos (pi/2-θ)))/c,
Wherein, Fm is the corresponding depth of focus of probe primitive i, and dx is probe lateral distance of the primitive i from emission lines, and θ is transmitting
Line deflection angle, c are the spread speed of ultrasonic wave.
12. according to the described in any item ultrasonic imaging broad beam emission systems of claim 9 to 11, which is characterized in that described to prolong
When processing module be specifically used for:
If the emission delay obtained is negative, the emission delay delay (i) is converted into positive number,
Delay (i)=delay (i)+abs (min (delay)),
Wherein, min (delay) indicates to take the negative minimum in delay array, and abs () expression seeks absolute value to the number in bracket.
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| PCT/CN2019/123867 WO2020164299A1 (en) | 2019-02-13 | 2019-12-09 | Wide beam emission method and emission system for ultrasonic imaging |
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Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110101411A (en) * | 2019-05-28 | 2019-08-09 | 飞依诺科技(苏州)有限公司 | Ultrasonic imaging space complex method and system |
| CN111184532A (en) * | 2020-04-09 | 2020-05-22 | 上海尽星生物科技有限责任公司 | Ultrasonic system and method of contact type flexible conformal ultrasonic probe |
| WO2020164299A1 (en) * | 2019-02-13 | 2020-08-20 | 飞依诺科技(苏州)有限公司 | Wide beam emission method and emission system for ultrasonic imaging |
| CN112034427A (en) * | 2020-09-09 | 2020-12-04 | 京东方科技集团股份有限公司 | Phased array multi-focus measurement method and device and storage medium |
| CN112263277A (en) * | 2020-11-17 | 2021-01-26 | 深圳开立生物医疗科技股份有限公司 | Ultrasonic Doppler blood flow imaging method, device, equipment and computer medium |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1529567A (en) * | 2001-12-12 | 2004-09-15 | ��ʽ��������ҽҩ | Ultrasonic diagnostic apparatus |
| CN101190133A (en) * | 2006-11-28 | 2008-06-04 | 深圳迈瑞生物医疗电子股份有限公司 | Method and device for transmitting wide wave beam in ultrasound wave diagnosis system |
| CN101396282A (en) * | 2007-09-29 | 2009-04-01 | 深圳迈瑞生物医疗电子股份有限公司 | Arc wide-beam transmission method and device for ultrasonic image-forming |
| CN101770028A (en) * | 2009-12-31 | 2010-07-07 | 深圳市蓝韵实业有限公司 | Aspheric focus method of using ultrasonic probe to transmit pulse |
| CN102326093A (en) * | 2009-02-20 | 2012-01-18 | 皇家飞利浦电子股份有限公司 | Utilize the ultrasonic imaging of changeable refractive index lens |
| WO2012018391A2 (en) * | 2010-08-02 | 2012-02-09 | Guided Therapy Systems, Llc | Methods and systems for treating plantar fascia |
Family Cites Families (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5677491A (en) * | 1994-08-08 | 1997-10-14 | Diasonics Ultrasound, Inc. | Sparse two-dimensional transducer array |
| JP2002209905A (en) * | 2001-01-22 | 2002-07-30 | Hitachi Medical Corp | Ultrasonic therapy probe and ultrasonic therapy apparatus |
| CN102809610B (en) * | 2012-06-04 | 2014-08-13 | 北京航空航天大学 | Phased array ultrasonic testing method based on improved dynamic depth focusing |
| CN104434218B (en) * | 2014-12-15 | 2017-01-11 | 飞依诺科技(苏州)有限公司 | Real-time calculation method and device of focusing delays for ultrasonic beam-forming |
| CN109674491A (en) * | 2019-02-13 | 2019-04-26 | 飞依诺科技(苏州)有限公司 | Ultrasonic imaging wide-beam transmission method and emission system |
-
2019
- 2019-02-13 CN CN201910112435.8A patent/CN109674491A/en not_active Withdrawn
- 2019-12-09 WO PCT/CN2019/123867 patent/WO2020164299A1/en active Application Filing
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1529567A (en) * | 2001-12-12 | 2004-09-15 | ��ʽ��������ҽҩ | Ultrasonic diagnostic apparatus |
| CN101190133A (en) * | 2006-11-28 | 2008-06-04 | 深圳迈瑞生物医疗电子股份有限公司 | Method and device for transmitting wide wave beam in ultrasound wave diagnosis system |
| CN101396282A (en) * | 2007-09-29 | 2009-04-01 | 深圳迈瑞生物医疗电子股份有限公司 | Arc wide-beam transmission method and device for ultrasonic image-forming |
| CN102326093A (en) * | 2009-02-20 | 2012-01-18 | 皇家飞利浦电子股份有限公司 | Utilize the ultrasonic imaging of changeable refractive index lens |
| CN101770028A (en) * | 2009-12-31 | 2010-07-07 | 深圳市蓝韵实业有限公司 | Aspheric focus method of using ultrasonic probe to transmit pulse |
| WO2012018391A2 (en) * | 2010-08-02 | 2012-02-09 | Guided Therapy Systems, Llc | Methods and systems for treating plantar fascia |
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2020164299A1 (en) * | 2019-02-13 | 2020-08-20 | 飞依诺科技(苏州)有限公司 | Wide beam emission method and emission system for ultrasonic imaging |
| CN110101411A (en) * | 2019-05-28 | 2019-08-09 | 飞依诺科技(苏州)有限公司 | Ultrasonic imaging space complex method and system |
| WO2020238143A1 (en) * | 2019-05-28 | 2020-12-03 | 飞依诺科技(苏州)有限公司 | Ultrasound imaging spatial compositing method and system |
| CN111184532A (en) * | 2020-04-09 | 2020-05-22 | 上海尽星生物科技有限责任公司 | Ultrasonic system and method of contact type flexible conformal ultrasonic probe |
| CN112034427A (en) * | 2020-09-09 | 2020-12-04 | 京东方科技集团股份有限公司 | Phased array multi-focus measurement method and device and storage medium |
| CN112034427B (en) * | 2020-09-09 | 2023-10-27 | 京东方科技集团股份有限公司 | Phased array multi-focus measurement method, device and storage medium |
| CN112263277A (en) * | 2020-11-17 | 2021-01-26 | 深圳开立生物医疗科技股份有限公司 | Ultrasonic Doppler blood flow imaging method, device, equipment and computer medium |
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|---|---|
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