CN105572049B - Optoacoustic quantifies elastograph imaging method and device - Google Patents
Optoacoustic quantifies elastograph imaging method and device Download PDFInfo
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- G—PHYSICS
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/1702—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/1702—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids
- G01N2021/1706—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids in solids
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/1702—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids
- G01N2021/1708—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids with piezotransducers
Abstract
The invention discloses a kind of optoacoustics to quantify elastograph imaging method and device, the method includes：Laser sends out pulse laser, which is focused by condenser lens, is impinged upon on tissue sample, inspires photoacoustic signal, and photoacoustic signal is received after the coupling liquid of coupling slot by ultrasonic detector；The photoacoustic signal that ultrasonic detector receives is acquired after amplifier amplifies by oscillograph, and by signal message storage to computer, computer-controlled stepper motor moves tissue sample point by point, and X Y two dimensional surface scanning areas are formed on corresponding tissue sample；After oscillograph has acquired whole signals, the tissue sample that computer calculates each point quantifies elasticity modulus；According to the quantitative elasticity modulus of calculating, the quantitative elastic two dimensional image of tissue sample is reconstructed；Described device includes photo-acoustic excitation source, signal acquisition/transmission/reconstruction component, coupling slot, stepper motor and X Y two-dimensional scanning platforms.Lossless, high-resolution tissue elasticity quantitative measurment and imaging may be implemented in the present invention.
Description
Technical field
The present invention relates to a kind of elastograph imaging method and device, especially a kind of optoacoustic quantifies elastograph imaging method and dress
It sets, belongs to technical field of biomedical detection.
Background technology
The pathological change of tissue can pass through analysis often with the variation of its engineering properties especially elasticity modulus
The physical parameter of tissue realizes the lesion detection of tissue.Currently, having predicted the method for tissue disease by the elasticity for detecting tissue
Through widely being received by doctor and iconography researcher, the detection of lossless hepatic sclerosis is such as realized using the method for Ultrasonic elasticity detection
Method has been applied to the parameter detecting of clinical disease.
Existing quantitative elastomeric check method is mainly static ultrasound elastomeric check and ultrasonic shear wave elastogram.It is static
Using static or quasi-static tissue excitation method, the artificial power using known dimensions squeezes tissue is Ultrasonic elasticity detection method
Tissue generates deformation, and the displacement in tissue is obtained using ultrasonic imaging, is equal to (power/displacement) according to elasticity modulus,
Quantitative elasticity modulus can be obtained.The disadvantages of this method is, is pure elastomer by organization modeling, and ignoring tissue has viscoelastic properties
The fact, inevitably cause measurement result inaccurate.Power applied to the organization is in the tissue in this method simultaneously
Distribution is influenced by tissue sample shape and motivator, causes measurement result and actual value deviation larger.Ultrasonic shear wave
Elastogram encourages shearing wave using ultrasound nonlinear effect caused by focal point is focused, by measuring shearing wave in the tissue
Spread speed obtain tissue elasticity modulus.This method is mainly used in the elasticity of the big histoorgan of such as mammary gland and thyroid gland
Detection detects the shortcomings of inaccurate there are launching efficiency is relatively low to small lesion area, and focal zone energy is excessively high leads to temperature liter
Height causes the change of damage or search coverage physiological property inevitable biological tissue.Simultaneously.Current elasticity is quantitatively examined
Survey and imaging can mainly be realized in big organ, for vascular diseases elastogram also rest on imaging strain figure and nothing
Method realizes the degree of quantitative elastogram.The optoacoustic quantitative measurment of tissue elasticity modulus proposed in this paper can be real with imaging method
The quantitative elasticity measurement in existing lossless small lesion area and imaging have incomparable compared with existing elasticity measurement and imaging technique
Superiority.
Currently, detecting tissue elasticity in China using photoacoustic method it has been reported that such as the invention disclosed on the 7th of September in 2011
Patent：Photoacoustic elastic imaging method and device, applicant：South China Normal University, the applying date：On January 14th, 2011, application number：
201110008213.5, it is excited which employs the continuous light source of intensity modulated and generates photoacoustic signal, by measuring the signal and adjusting
Phase difference and point by point scanning between signal processed can reconstruct the elasticity distribution image of detection tissue sample.But in the above method
In, the quantitative measurment for realizing tissue elasticity modulus is had not been able to, that is, the absolute value of elasticity modulus cannot be obtained, phase can only be provided
To value, the accuracy of this method measurement result in practical applications is reduced.
Invention content
The purpose of the present invention is to solve the defect of the above-mentioned prior art, provides a kind of optoacoustic and quantify elastogram side
Lossless, high-resolution tissue elasticity quantitative measurment and imaging may be implemented in method, this method.
Another object of the present invention is to provide a kind of optoacoustics for realizing the above method to quantify elastogram device.
The purpose of the present invention can be reached by adopting the following technical scheme that：
Optoacoustic quantifies elastograph imaging method, the described method comprises the following steps：
1) tissue sample is placed in X-Y two-dimensional scanning platforms, and be immersed in the coupling liquid of coupling slot；It will focus saturating
Mirror is arranged right over tissue sample, and the height for adjusting condenser lens makes the focus of condenser lens without departing from tissue sample table
Face；Ultrasonic detector is directed at tissue sample, and the lower end of ultrasonic detector is made to enter in the coupling liquid of coupling slot；
2) laser sends out pulse laser, which is focused by condenser lens, is impinged upon on tissue sample, is inspired
Photoacoustic signal, photoacoustic signal are received after the coupling liquid of coupling slot by ultrasonic detector；
3) photoacoustic signal that ultrasonic detector receives is acquired after amplifier amplifies by oscillograph, and oscillograph is by acquisition
To in computer, computer-controlled stepper motor moves tissue sample point by point for signal message storage, shape on corresponding tissue sample
At X-Y two dimensional surface scanning areas, stepper motor is often mobile primary, and oscillograph just carries out a signal acquisition；
4) after oscillograph has acquired whole signals, computer once integrates the signal of each point the time, obtains group
The function of time of tissue samples surface vibration displacement；Obtain tissue sample surface vibration displacement from it is above freezing rise to its maximum value when it is required
Time, the tissue sample that each point is calculated using the time quantify elasticity modulus；According to the quantitative elasticity modulus of calculating, group is reconstructed
The quantitative elastic two dimensional image of tissue samples.
As a preferred embodiment, in step 1), in the coupling liquid for making the lower end of ultrasonic detector enter coupling slot
Specially：The lower end of ultrasonic detector is set to enter at the coupling liquid depth 5-8mm of coupling slot.
As a preferred embodiment, in step 3), the computer-controlled stepper motor moves tissue sample and refers to point by point：
Computer moves tissue sample point by point using Labview programs control stepper motor；In step 4), the computer is by each point
Signal carries out primary integral to the time：Computer once accumulates the signal of each point the time using Matlab programs
Point.
As a preferred embodiment, in step 4), the tissue sample for calculating each point quantifies elasticity modulus, under
Formula：
Wherein, ρ is biological tissue density, and R is laser facula radius, tmaxIt is tissue sample surface vibration displacement from above freezing
Required time when rising to its maximum value.
Another object of the present invention can be reached by adopting the following technical scheme that：
Optoacoustic quantifies elastogram device, and described device includes photo-acoustic excitation source, signal acquisition/transmission/reconstruction component, coupling
Slot, stepper motor and X-Y two-dimensional scanning platforms are closed, the photo-acoustic excitation source includes laser and condenser lens；The signal is adopted
Collection/transmission/reconstruction component includes ultrasonic detector, amplifier, oscillograph and computer, and the ultrasonic detector, shows amplifier
Wave device and computer are sequentially connected, and the computer is equipped with acquisition control and signal processing system；The stepper motor and meter
Calculation machine is connected, and the X-Y two-dimensional scanning platforms are placed in coupling slot, and coupling liquid is full of in the coupling slot；
When test, tissue sample is placed in X-Y two-dimensional scanning platforms, and is immersed in the coupling liquid of coupling slot；It is described
Condenser lens is arranged right over tissue sample, and the focus of condenser lens is without departing from tissue sample surface, the laser hair
The pulse laser gone out is focused by condenser lens, is impinged upon on tissue sample；The ultrasonic detector is directed at tissue sample, and ultrasound
The lower end of detector enters in the coupling liquid of coupling slot, receives the photoacoustic signal that tissue sample is inspired；The computer control
Stepper motor processed moves tissue sample point by point.
As a preferred embodiment, described device further includes that instrument fixes/fixing device component, and the instrument fixes/
Support device assembly is for fixing/supporting X-Y two-dimensional scanning platforms, condenser lens and ultrasonic detector.
As a preferred embodiment, the ultrasonic detector is hydrophone, response frequency 200KHz-15MHz, diameter
For 1mm；The piezoelectricity converting member of ultrasonic detector is the gold electrode PVDF membrane that a thickness is 28 μm, receives optoacoustic letter
Number when, the gold electrode PVDF membrane be aligned tissue sample.
As a preferred embodiment, the sample rate of the oscillograph is 2.5GHz, the acquisition control of the computer installation
And signal processing system is formed using Labview and Matlab programmings.
As a preferred embodiment, the pulse laser wavelength that the laser is sent out is 400~2500nm, and pulse width is
1~50ns, repetition rate are 1Hz~5KHz.
As a preferred embodiment, the coupling liquid in the coupling slot is water, monitors water temperature, makes water temperature and tissue sample
Temperature is consistent.
The present invention has following advantageous effect compared with the existing technology：
1, the present invention once integrates the signal of oscillograph acquisition the time, obtains tissue sample surface vibration displacement
The function of time, obtain tissue sample surface vibration displacement from it is above freezing rise to its maximum value when the time required to, utilize time meter
It calculates tissue and quantifies elasticity modulus, compared with the method that existing relative resilient measures, as reference without normal structure, have more
High accuracy.
2, the present invention sends out pulse laser using laser, which is focused by condenser lens, impinges upon tissue sample
On product, photoacoustic signal is inspired, to carry out carrying out tissue elasticity detection, compared with traditional Ultrasonic elasticity detection method, tool
Specificity and high resolution in a organized way.
3, the ultrasonic detector that the present invention uses is hydrophone, response frequency 200KHz-15MHz, a diameter of 1mm,
Have the advantages that detectivity is high, is limited without bandwidth, to ensure that the ability of highly sensitive detection.
4, the method that optoacoustic of the invention quantifies elastomeric check has the ability quickly detected, realizes the device knot of this method
Structure is simple, easy to use, can be widely applied in the elastogram of tissue, is convenient for industrialization.
Description of the drawings
Fig. 1 is that the optoacoustic of the embodiment of the present invention 1 quantifies the structural schematic diagram of elastogram device.
Fig. 2 is the dependence curve figure of the displacement versus time of the embodiment of the present invention 1.
Fig. 3 is the schematic diagram of the Agar samples a of the embodiment of the present invention 2.
Fig. 4 is the schematic diagram of the Agar samples b of the embodiment of the present invention 2.
Fig. 5 is the photoacoustic image of the Agar samples a of the embodiment of the present invention 2.
Fig. 6 is the photoacoustic image of the Agar samples b of the embodiment of the present invention 2.
Fig. 7 is the optoacoustic elastic image of the Agar samples a of the embodiment of the present invention 2.
Fig. 8 is the optoacoustic elastic image of the Agar samples b of the embodiment of the present invention 2.
Fig. 9 is the elasticity modulus curve graph at Fig. 3 and Fig. 4 dotted lines.
Wherein, 1- coupling slots, 2- stepper motors, 3- lasers, 4- condenser lenses, 5- ultrasonic detectors, 6- amplifiers, 7-
Oscillograph, 8- computers, 9- tissue samples.
Specific implementation mode
Present invention will now be described in further detail with reference to the embodiments and the accompanying drawings, but embodiments of the present invention are unlimited
In this.
Embodiment 1：
As shown in Figure 1, the optoacoustic of the present embodiment quantify elastogram device include photo-acoustic excitation source, signal acquisition/transmission/
Rebuild component, coupling slot 1, stepper motor 2, X-Y two-dimensional scanning platforms and instrument fix/fixing device component (do not show in figure
Go out), the photo-acoustic excitation source includes laser 3 and condenser lens 4；Signal acquisition/transmission/reconstruction the component includes that ultrasound is visited
Survey device 5, amplifier 6, oscillograph 7 and computer 8, the ultrasonic detector 5, amplifier 6, oscillograph 7 and computer 8 phase successively
Even；The sample rate of the oscillograph 7 is 2.5GHz；The computer 8 is equipped with acquisition control and signal processing system, the system
It is formed using Labview and Matlab programmings；The stepper motor 2 is connected with computer 8, and the X-Y two-dimensional scans are flat
Platform is placed in coupling slot 1, and coupling liquid is full of in the coupling slot 1；
The ultrasonic detector 5 is hydrophone, response frequency 200KHz-15MHz, a diameter of 1mm；Ultrasonic detector
Piezoelectricity converting member be a thickness be 28 μm of gold electrode PVDF membrane.
The instrument is fixed/fixing device component for fix/support X-Y two-dimensional scanning platforms, condenser lens 4 and
Ultrasonic detector 5.
It realizes that the optoacoustic of the present embodiment quantifies elastograph imaging method, mainly uses following principle：
Tissue is irradiated with a laser generation shearing wave, and equation is：
Wherein, uzIt is also to be generated after tissue is energized in the displacement in the directions z, that is, excitation line direction, to be shearing wave displacement
Displacement when photoacoustic signal.For shear-wave velocity, μ is modulus of shearing, and v=μ/ρ are dynamic shearing viscosity, Fz
For photic thermoelastic radiant force.In focal position of laser,M=β0αI0, β0For coefficient of thermal expansion, α
For the absorption coefficient of tissue, I0For laser intensity.R be position independent variable, R be laser facula radius, φ (t) be laser intensity with
Time-varying relationship, pulse width t0。
According to the solution of ODE, and carries out Hankel transform and obtain：
Above equation is write as the form of Green's function：
This shear displacemant is the displacement of biological tissue surface when generating photoacoustic signal simultaneously.
Because meeting between photoacoustic signal and displacement：
Consider that temperature change is to change slowly the time at laser spot, by carrying out situational variables to above formula：
Photoacoustic spectrum changes from zero to its maximum value elapsed time and meets tmax=R/ct, modulus of shearing μ meets μ
=ρ (R/tmax)2；Wherein, ρ is biological tissue density, can be taken as 1100kg/m3, closed by using elasticity modulus and modulus of shearing
It is E=2 μ (1+ η), wherein η is that biological tissue's Poisson's ratio is taken as 0.499 since biological tissue is incompressible, to acquisition group
The quantitative elasticity modulus size knitted：
Therefore, the optoacoustic of the present embodiment quantifies elastograph imaging method and includes the following steps：
1) tissue sample 9 is placed in X-Y two-dimensional scanning platforms, and be immersed in the coupling liquid of coupling slot 1；It will focus
The setting of lens 4 is right over tissue sample 9, and the height for adjusting condenser lens 4 makes the focus of condenser lens 4 without departing from tissue sample
9 surface of product；Ultrasonic detector 5 is directed at tissue sample 9, i.e., gold electrode PVDF membrane is directed at tissue sample 9, and makes to surpass
During the lower end of detector of sound 5 enters at the coupling liquid depth about 5-8mm of coupling slot 1, coupling liquid is water, monitors water temperature, makes water temperature
It is consistent with the temperature of tissue sample 9；
2) laser 3 sends out pulse laser, the pulse laser wavelength sent out be 400~2500nm, pulse width be 1~
50ns, repetition rate are 1Hz~5KHz, which is focused by condenser lens 4, impinged upon on tissue sample 9, excite light extraction
Acoustical signal, photoacoustic signal are received after the coupling liquid of coupling slot 1 by ultrasonic detector 5；
3) photoacoustic signal that ultrasonic detector 5 receives is acquired, oscillograph 7 will be adopted after the amplification of amplifier 6 by oscillograph 7
In the signal message storage to computer 8 of collection, computer 8 utilizes the point-by-point mobile tissue sample of Labview programs control stepper motor 2
Product 9 form X-Y two dimensional surface scanning areas on corresponding tissue sample 9, and stepper motor 2 is often mobile primary, oscillograph 7 just into
Signal acquisition of row；
4) after oscillograph 7 has acquired whole signals, computer 8 carries out the time signal of each point using Matlab programs
Primary integral, obtains the function of time of tissue sample surface vibration displacement；Tissue sample surface vibration displacement is obtained from liter above freezing
The time required to when its maximum value, as shown in Fig. 2, giving four kinds of displacements in figure with the variation relation of time, different bullets
Property modulus, displacement reach maximum value needed for time be different；By above-mentioned formula (6), each point is calculated using the time
Tissue sample quantifies elasticity modulus；According to the quantitative elasticity modulus of calculating, the quantitative elastic two dimensional image of tissue sample is reconstructed.
Embodiment 2：
The present embodiment is the experiment carried out using Agar samples, is mainly included the following steps that：
1) ink that 10% is added in the agar of a concentration of 20g/L makes square sample, is made among it a concentration of
The agar of 15g/L is simultaneously added 3% ink and makes square circular sample, and this results in the Agar samples a in Fig. 3；A concentration of
The ink that 10% is added in the agar of 30g/L makes square sample, and the agar of a concentration of 25g/L and addition are made among it
3% ink makes square circular sample, and this results in the Agar samples b in Fig. 4；
2) start laser, output pulse laser wavelength is 532nm, and pulsewidth 10ns, repetition rate is 15Hz；The pulse
Laser is radiated at after being focused by condenser lens on Agar samples a and b, and Agar samples a and b are inspired photoacoustic signal, optoacoustic
Signal is received after the coupling liquid in coupling slot by ultrasonic detector；
3) photoacoustic signal that ultrasonic detector receives is transmitted to oscillograph progress data and adopts after amplifier amplifies
Collection, oscillograph by data transmission and are stored into computer again, and corresponding formed on sample of computer-controlled stepper motor is swept
Retouch region；
4) after having acquired whole signals, the data of acquisition are first normalized, maximum value projection method and elasticity is then used to project
Method rebuilds photoacoustic image and optoacoustic elastic image, and Fig. 5 and Fig. 6 are the photoacoustic image of Agar samples a and b respectively, it can be seen that aobvious
The background agar photoacoustic imaging shown is almost without contrast, and the photoacoustic imaging of intermediate border circular areas is also almost without contrast；Fig. 7
It is the optoacoustic elastic image of Agar samples a and b respectively with Fig. 8, it can be seen that the optoacoustic elastic image of display then shows big pair
Than degree, this illustrates the necessity of optoacoustic elastogram；Agaroid at Fig. 3 and Fig. 4 dotted lines is shown in a and b in Fig. 9 respectively
The elasticity number of product, it can be seen that the significant change of elasticity number.
In conclusion the present invention, which proposes a kind of new tissue, quantifies elasticity modulus measurement method, with existing opposite bullet
Property measure method compare, without normal structure as reference, have higher accuracy；Tissue bullet is carried out using laser is focused
Property detection, compared with traditional Ultrasonic elasticity detection method, have tissue specificity and high resolution；The supersonic sounding of use
Device is hydrophone, has the advantages that detectivity is high, is limited without bandwidth, to ensure that the ability of highly sensitive detection.
The above, patent preferred embodiment only of the present invention, but the protection domain of patent of the present invention is not limited to
This, any one skilled in the art is in the range disclosed in patent of the present invention, according to the skill of patent of the present invention
Art scheme and its inventive concept are subject to equivalent substitution or change, belong to the protection domain of patent of the present invention.
Claims (10)
1. optoacoustic quantifies elastograph imaging method, it is characterised in that：It the described method comprises the following steps：
1) tissue sample is placed in X-Y two-dimensional scanning platforms, and be immersed in the coupling liquid of coupling slot；Condenser lens is set
The height set right over tissue sample, and adjust condenser lens makes the focus of condenser lens without departing from tissue sample surface；It will
Ultrasonic detector is directed at tissue sample, and the lower end of ultrasonic detector is made to enter in the coupling liquid of coupling slot；
2) laser sends out pulse laser, which is focused by condenser lens, is impinged upon on tissue sample, and optoacoustic is inspired
Signal, photoacoustic signal are received after the coupling liquid of coupling slot by ultrasonic detector；
3) photoacoustic signal that ultrasonic detector receives is acquired after amplifier amplifies by oscillograph, and oscillograph is by the signal of acquisition
In information storage to computer, computer-controlled stepper motor moves tissue sample point by point, and X-Y is formed on corresponding tissue sample
Two dimensional surface scanning area, stepper motor is often mobile primary, and oscillograph just carries out a signal acquisition；
4) after oscillograph has acquired whole signals, computer once integrates the signal of each point the time, obtains tissue sample
The function of time of product surface vibration displacement；Obtain tissue sample surface vibration displacement from it is above freezing rise to its maximum value when taken
Between, the tissue sample that each point is calculated using the time quantifies elasticity modulus；According to the quantitative elasticity modulus of calculating, tissue is reconstructed
The quantitative elastic two dimensional image of sample.
2. optoacoustic according to claim 1 quantifies elastograph imaging method, it is characterised in that：It is described to make ultrasound in step 1)
The lower end of detector enters in the coupling liquid of coupling slot：Keep the coupling liquid that the lower end of ultrasonic detector enters coupling slot deep
It spends at 5-8mm.
3. optoacoustic according to claim 1 quantifies elastograph imaging method, it is characterised in that：In step 3), the computer
Control stepper motor moves tissue sample and refers to point by point：Computer moves group point by point using Labview programs control stepper motor
Tissue samples；In step 4), the signal of each point is carried out primary integral to the time and refers to by the computer：Computer utilizes Matlab
Program once integrates the signal of each point the time.
4. optoacoustic according to claim 1 quantifies elastograph imaging method, it is characterised in that：It is described to calculate respectively in step 4)
The tissue sample of point quantifies elasticity modulus, using following formula：
Wherein, ρ is biological tissue density, and R is laser facula radius, tmaxIt is risen to from above freezing for tissue sample surface vibration displacement
The time required to when its maximum value.
5. optoacoustic quantifies elastogram device, it is characterised in that：Described device includes photo-acoustic excitation source, signal acquisition/transmission/weight
Component, coupling slot, stepper motor and X-Y two-dimensional scanning platforms are built, the photo-acoustic excitation source includes laser and condenser lens；Institute
It includes ultrasonic detector, amplifier, oscillograph and computer to state signal acquisition/transmission/reconstruction component, the ultrasonic detector,
Amplifier, oscillograph and computer are sequentially connected, and the computer is equipped with acquisition control and signal processing system；The stepping
Motor is connected with computer, and the X-Y two-dimensional scanning platforms are placed in coupling slot, and coupling liquid is full of in the coupling slot；
When test, tissue sample is placed in X-Y two-dimensional scanning platforms, and is immersed in the coupling liquid of coupling slot；The focusing
Lens are arranged right over tissue sample, and the focus of condenser lens is without departing from tissue sample surface, what the laser was sent out
Pulse laser is focused by condenser lens, is impinged upon on tissue sample；The ultrasonic detector is directed at tissue sample, and supersonic sounding
The lower end of device enters in the coupling liquid of coupling slot, receives the photoacoustic signal that tissue sample is inspired；What ultrasonic detector received
Photoacoustic signal is acquired after amplifier amplifies by oscillograph, and oscillograph is calculated in the signal message storage to computer of acquisition
Machine control stepper motor moves tissue sample point by point, and X-Y two dimensional surface scanning areas, stepping electricity are formed on corresponding tissue sample
Machine is often mobile primary, and oscillograph just carries out a signal acquisition；After oscillograph has acquired whole signals, computer is by the letter of each point
Number the time is once integrated, obtains the function of time of tissue sample surface vibration displacement；Obtain tissue sample surface vibration
Displacement from it is above freezing rise to its maximum value when the time required to, the tissue sample that each point is calculated using the time quantifies elasticity modulus；Root
According to the quantitative elasticity modulus of calculating, the quantitative elastic two dimensional image of tissue sample is reconstructed.
6. optoacoustic according to claim 5 quantifies elastogram device, it is characterised in that：Described device further includes that instrument is solid
Fixed/fixing device component, the instrument are fixed, and/fixing device component is for fixing/supports X-Y two-dimensional scanning platforms, focuses thoroughly
Mirror and ultrasonic detector.
7. optoacoustic according to claim 5 or 6 quantifies elastogram device, it is characterised in that：The ultrasonic detector is
Hydrophone, response frequency 200KHz-15MHz, a diameter of 1mm；The piezoelectricity converting member of ultrasonic detector is that a thickness is
28 μm of gold electrode PVDF membrane, when receiving photoacoustic signal, which is directed at tissue sample.
8. optoacoustic according to claim 5 or 6 quantifies elastogram device, it is characterised in that：The sampling of the oscillograph
Rate is 2.5GHz, and the acquisition control and signal processing system of the computer installation utilize Labview and Matlab programmings
It forms.
9. optoacoustic according to claim 5 or 6 quantifies elastogram device, it is characterised in that：What the laser was sent out
Pulse laser wavelength is 400~2500nm, and pulse width is 1~50ns, and repetition rate is 1Hz~5KHz.
10. optoacoustic according to claim 5 or 6 quantifies elastogram device, it is characterised in that：Coupling in the coupling slot
Conjunction liquid is water, monitors water temperature, the temperature of water temperature and tissue sample is made to be consistent.
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| CN102175776A (en) * | 2011-01-14 | 2011-09-07 | 华南师范大学 | Photoacoustic elastic imaging method and device |
| CN102297898A (en) * | 2011-05-17 | 2011-12-28 | 南京理工大学 | Laser ultrasonic measuring method for third order elastic constant of metal |
| CN102879335A (en) * | 2012-09-26 | 2013-01-16 | 华南师范大学 | Portable noninvasive real-time photoacoustic viscoelastic detector |
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| CN102175776A (en) * | 2011-01-14 | 2011-09-07 | 华南师范大学 | Photoacoustic elastic imaging method and device |
| CN102297898A (en) * | 2011-05-17 | 2011-12-28 | 南京理工大学 | Laser ultrasonic measuring method for third order elastic constant of metal |
| CN102879335A (en) * | 2012-09-26 | 2013-01-16 | 华南师范大学 | Portable noninvasive real-time photoacoustic viscoelastic detector |
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