CN105572049A - Opto-acoustic quantitative elasticity imaging method and device - Google Patents
Opto-acoustic quantitative elasticity imaging method and device Download PDFInfo
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- CN105572049A CN105572049A CN201510944323.0A CN201510944323A CN105572049A CN 105572049 A CN105572049 A CN 105572049A CN 201510944323 A CN201510944323 A CN 201510944323A CN 105572049 A CN105572049 A CN 105572049A
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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 an opto-acoustic quantitative elasticity imaging method and device. The method comprises the following steps: a laser device emits pulse laser which is focused by a focusing lens and irradiates a tissue sample so as to excite an opto-acoustic signal, and the opto-acoustic signal is received by an ultrasonic detector through a coupling solution in a coupling trough; the opto-acoustic received by the ultrasonic detector is collected by an oscilloscope after being amplified by an amplifier, and signal information is stored into a computer; the computer controls a stepping motor to move the tissue sample point by point, so that an X-Y two-dimensional planar scanning region is formed on the corresponding tissue sample; after the oscilloscope collects all the signals, the computer calculates a quantitative elastic modulus of the tissue sample of each point; and a quantitative elastic two-dimensional image of the tissue sample is reconstructed according to the calculated quantitative elastic modulus. The device comprises an opto-acoustic exciting source, a signal collection/transmission/reconstruction assembly, the coupling trough, the stepping motor and an X-Y two-dimensional scanning platform. The opto-acoustic quantitative elasticity imaging method and device can realize non-destructive and high-resolution elastic and quantitative tissue measurement and imaging.
Description
Technical field
The present invention relates to a kind of elastograph imaging method and device, the quantitative elastograph imaging method of especially a kind of optoacoustic and device, belong to technical field of biomedical detection.
Background technology
The pathological change of tissue, often with the change of its engineering properties particularly elastic modulus, therefore can realize the lesion detection of tissue by the physical parameter analyzing tissue.At present, received widely by doctor and iconography researcher by the method for the elasticity prediction tissue disease detecting tissue, the detection method of the harmless cirrhosis of method realization detected as utilized Ultrasonic elasticity 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.Static ultrasound elastomeric check method adopts static or quasi-static tissue excitation method, the power extrusion tissue of known dimensions is artificially utilized to be that tissue produces deformation, ultrasonic imaging is utilized to obtain the displacement size in organizing, equal (power/displacement size) according to elastic modulus, quantitative elastic modulus can be obtained.The shortcoming of the method is, is pure elastic body by organization modeling, ignores the fact that tissue has viscoelastic property, inevitably causes measurement result inaccurate.Simultaneously be applied to the impact that the distribution in the tissue of structural power is subject to tissue sample shape and motivator in the method, cause measurement result and actual value deviation larger.The nonlinear effect excitation shearing wave that ultrasonic shear wave elastogram utilizes focus supersonic to cause at focus place, obtains the elastic modulus of tissue by measuring shearing wave velocity of propagation in the tissue.The method is mainly used in the elastomeric check of histoorgan as large in mammary gland and thyroid gland etc., have that launching efficiency is lower detects the shortcoming such as inaccurate to small lesion district, and focal zone energy is too high causes temperature to raise causing the change of damage or search coverage physiological property inevitable to biological tissue.Simultaneously.Current elasticity quantitatively detects and mainly can be able to realize at large organ with imaging, and the elastogram for vascular diseases also rests on imaging strain figure and cannot realize the degree of quantitative elastogram.The optoacoustic quantitative measurment of tissue elasticity modulus in this paper and formation method can realize quantitative elasticity measurement and the imaging in harmless small lesion district, to compare have incomparable superiority with existing elasticity measurement with imaging technique.
At present, utilize photoacoustic method to detect tissue elasticity to have been reported in China, as invention disclosed patent on September 7th, 2011: photoacoustic elastic imaging method and device, applicant: South China Normal University, the applying date: on January 14th, 2011, application number: 201110008213.5, the continuous light source which employs intensity modulated excites generation photoacoustic signal, by measuring phase differential between this signal and modulation signal and point by point scanning can reconstruct the elasticity distribution image of test set tissue samples.But in the above-mentioned methods, can not realize the quantitative measurment of tissue elasticity modulus, namely can not obtain the absolute value of elastic modulus, can only relative value be provided, reduce the accuracy of the method measurement result in actual applications.
Summary of the invention
The object of the invention is the defect in order to solve above-mentioned prior art, providing the quantitative elastograph imaging method of a kind of optoacoustic, the method can realize can't harm, high-resolution tissue elasticity quantitative measurment and imaging.
Another object of the present invention is to provide a kind of quantitative elastogram device of optoacoustic realizing said method.
Object of the present invention can reach by taking following technical scheme:
The quantitative elastograph imaging method of optoacoustic, said method comprising the steps of:
1) tissue sample is placed on X-Y two-dimensional scan platform, and is immersed in the coupling liquid of coupling slot; Condenser lens is arranged on directly over tissue sample, and the height adjusting condenser lens makes the focus not offset groups tissue samples surface of condenser lens; Ultrasonic detector is aimed at tissue sample, and makes the lower end of ultrasonic detector enter in the coupling liquid of coupling slot;
2) laser instrument sends pulse laser, and this pulse laser is focused on by condenser lens, and impinge upon on tissue sample, inspire photoacoustic signal, photoacoustic signal is received by ultrasonic detector after the coupling liquid of coupling slot;
3) photoacoustic signal of ultrasonic detector reception is after amplifier amplifies, gathered by oscillograph, the signal message of collection is stored in computing machine by oscillograph, computer-controlled stepper motor pointwise moving tissue sample, corresponding tissue sample forms X-Y two dimensional surface scanning area, stepper motor often moves once, and oscillograph just carries out a signals collecting;
4), after oscillograph gathers full signal, the signal of each point is carried out an integration to the time by computing machine, obtains the function of time of tissue sample surface vibration displacement; Obtain tissue sample surface vibration displacement from above freezing rise to its maximal value time required time, utilize the quantitative elastic modulus of the tissue sample of this Time Calculation each point; According to the quantitative elastic modulus calculated, reconstruct the quantitative elasticity two dimensional image of tissue sample.
As a kind of preferred version, step 1) in, described in the lower end of ultrasonic detector is entered in the coupling liquid of coupling slot be specially: make the lower end of ultrasonic detector enter the coupling liquid degree of depth 5-8mm place of coupling slot.
As a kind of preferred version, step 3) in, described computer-controlled stepper motor pointwise moving tissue sample refers to: computing machine utilizes Labview programmed control stepper motor pointwise moving tissue sample; Step 4) in, the signal of each point is carried out an integration to the time and refers to by described computing machine: computing machine utilizes Matlab program that the signal of each point is carried out an integration to the time.
As a kind of preferred version, step 4) in, the quantitative elastic modulus of tissue sample of described calculating each point, adopts following formula:
Wherein, ρ is biological tissue's density, and R is laser facula radius, t
maxfor tissue sample surface vibration displacement from above freezing rise to its maximal value time required time.
Another object of the present invention can reach by taking following technical scheme:
The quantitative elastogram device of optoacoustic, described device comprises photo-acoustic excitation source, signals collecting/transmission/reconstruction assembly, coupling slot, stepper motor and X-Y two-dimensional scan platform, and described photo-acoustic excitation source comprises laser instrument and condenser lens; Described signals collecting/transmission/reconstruction assembly comprises ultrasonic detector, amplifier, oscillograph and computing machine, and described ultrasonic detector, amplifier, oscillograph are connected successively with computing machine, and described computing machine is provided with to gather and controls and signal processing system; Described stepper motor is connected with computing machine, and described X-Y two-dimensional scan platform is placed in coupling slot, is full of coupling liquid in described coupling slot;
During test, tissue sample is placed on X-Y two-dimensional scan platform, and is immersed in the coupling liquid of coupling slot; Described condenser lens is arranged on directly over tissue sample, and the focus of condenser lens not offset groups tissue samples surface, the pulse laser that described laser instrument sends is focused on by condenser lens, impinges upon on tissue sample; Tissue sample aimed at by described ultrasonic detector, and the lower end of ultrasonic detector enters in the coupling liquid of coupling slot, the photoacoustic signal that tissue receiving sample is inspired; Described computer-controlled stepper motor pointwise moving tissue sample.
As a kind of preferred version, described device also comprises instrument and fixes/fixing device assembly, described instrument fixes/fixing device assembly for fixing/support X-Y two-dimensional scan platform, condenser lens and ultrasonic detector.
As a kind of preferred version, described ultrasonic detector is nautical receiving set, and its response frequency is 200KHz-15MHz, and diameter is 1mm; The piezoelectricity converting member of ultrasonic detector to be a thickness the be gold electrode PVDF membrane of 28 μm, when receiving photoacoustic signal, this gold electrode PVDF membrane aims at tissue sample.
As a kind of preferred version, described oscillographic sampling rate is 2.5GHz, and the collection control that described computing machine is installed and signal processing system utilize Labview and Matlab programming to form.
As a kind of preferred version, the pulse laser wavelength that described laser instrument sends is 400 ~ 2500nm, and pulse width is 1 ~ 50ns, and repetition frequency is 1Hz ~ 5KHz.
As a kind of preferred version, the coupling liquid in described coupling slot is water, and monitoring water temperature, makes the temperature of water temperature and tissue sample be consistent.
The present invention has following beneficial effect relative to prior art:
1, the signal of oscillograph collection is carried out an integration to the time by the present invention, obtain the function of time of tissue sample surface vibration displacement, obtain tissue sample surface vibration displacement from above freezing rise to its maximal value time required time, this Time Calculation is utilized to organize quantitative elastic modulus, compared with the method measured with existing relative resilient, without the need to normal structure as a reference, there is higher accuracy.
2, the present invention utilizes laser instrument to send pulse laser, and this pulse laser is focused on by condenser lens, impinges upon on tissue sample, inspire photoacoustic signal, thus carry out tissue elasticity detection, compared with traditional Ultrasonic elasticity detection method, there is tissue specificity and high resolution capacity.
3, the ultrasonic detector that the present invention adopts is nautical receiving set, and its response frequency is 200KHz-15MHz, and diameter is 1mm, has detection sensitivity advantage that is high, that limit without bandwidth, thus ensure that the ability of highly sensitive detection.
4, the method for the quantitative elastomeric check of optoacoustic of the present invention possesses the ability detected fast, and the apparatus structure realizing the method is simple, easy to use, can be widely used in the elastogram of tissue, be convenient to industrialization.
Accompanying drawing explanation
Fig. 1 is the structural representation of the quantitative elastogram device of optoacoustic of the embodiment of the present invention 1.
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 elastic modulus curve map at Fig. 3 and Fig. 4 dotted line place.
Wherein, 1-coupling slot, 2-stepper motor, 3-laser instrument, 4-condenser lens, 5-ultrasonic detector, 6-amplifier, 7-oscillograph, 8-computing machine, 9-tissue sample.
Embodiment
Below in conjunction with embodiment and accompanying drawing, the present invention is described in further detail, but embodiments of the present invention are not limited thereto.
Embodiment 1:
As shown in Figure 1, the quantitative elastogram device of optoacoustic of the present embodiment comprises photo-acoustic excitation source, signals collecting/transmission/reconstruction assembly, coupling slot 1, stepper motor 2, X-Y two-dimensional scan platform and instrument and fixes/fixing device assembly (not shown), and described photo-acoustic excitation source comprises laser instrument 3 and condenser lens 4; Described signals collecting/transmission/reconstruction assembly comprises ultrasonic detector 5, amplifier 6, oscillograph 7 and computing machine 8, and described ultrasonic detector 5, amplifier 6, oscillograph 7 are connected successively with computing machine 8; The sampling rate of described oscillograph 7 is 2.5GHz; Described computing machine 8 is provided with to gather and controls and signal processing system, and this system utilizes Labview and Matlab programming to form; Described stepper motor 2 is connected with computing machine 8, and described X-Y two-dimensional scan platform is placed in coupling slot 1, is full of coupling liquid in described coupling slot 1;
Described ultrasonic detector 5 is nautical receiving set, and its response frequency is 200KHz-15MHz, and diameter is 1mm; The piezoelectricity converting member of ultrasonic detector to be a thickness the be gold electrode PVDF membrane of 28 μm.
Described instrument fixes/fixing device assembly for fixing/support X-Y two-dimensional scan platform, condenser lens 4 and ultrasonic detector 5.
Realize the quantitative elastograph imaging method of optoacoustic of the present embodiment, the following principle of main employing:
Tissue is irradiated with a laser generation shearing wave, and its equation is:
Wherein, u
zfor the displacement in z direction and excitation line direction, after to be shearing wave displacement be also tissue is energized, produce displacement during photoacoustic signal.
for shear-wave velocity, μ is modulus of shearing, and v=μ/ρ is dynamic shearing coefficient of viscosity, F
zfor photic thermoelastic radiant force.At focal position of laser,
m=β
0α I
0, β
0for thermal expansivity, α is the absorption coefficient of tissue, I
0for laser intensity.R is position independent variable, and R is laser facula radius, and φ (t) is laser intensity variation relation in time, and pulse width is t
0.
According to the solution of ordinary differential equation, and carry out Hankel transform and obtain:
Equation is above write as the form of Green function:
This shear displacemant is the displacement of biological tissue surface when producing photoacoustic signal simultaneously.
Because meet between photoacoustic signal and displacement:
Consider in laser spot place temperature variation to be change slowly the time, by carrying out situational variables to above formula:
Photoacoustic spectrum changes to its maximal value institute elapsed-time standards from zero and meets t
max=R/c
t, modulus of shearing μ meets μ=ρ (R/t
max)
2; Wherein, ρ is biological tissue's density, can be taken as 1100kg/m
3, by utilizing elastic modulus and modulus of shearing relation E=2 μ (1+ η), wherein, η is biological tissue's Poisson ratio, because biological tissue is incompressible, is taken as 0.499, thus obtains the quantitative elastic modulus size of tissue:
Therefore, the quantitative elastograph imaging method of the optoacoustic of the present embodiment comprises the following steps:
1) tissue sample 9 is placed on X-Y two-dimensional scan platform, and is immersed in the coupling liquid of coupling slot 1; Condenser lens 4 is arranged on directly over tissue sample 9, and the height adjusting condenser lens 4 makes focus not offset groups tissue samples 9 surface of condenser lens 4; Ultrasonic detector 5 is aimed at tissue sample 9, namely gold electrode PVDF membrane aims at tissue sample 9, and the coupling liquid degree of depth making the lower end of ultrasonic detector 5 enter coupling slot 1 is about in 5-8mm place, and coupling liquid is water, monitoring water temperature, makes the temperature of water temperature and tissue sample 9 be consistent;
2) laser instrument 3 sends pulse laser, the pulse laser wavelength sent is 400 ~ 2500nm, pulse width is 1 ~ 50ns, repetition frequency is 1Hz ~ 5KHz, this pulse laser is focused on by condenser lens 4, impinge upon on tissue sample 9, inspire photoacoustic signal, photoacoustic signal is received by ultrasonic detector 5 after the coupling liquid of coupling slot 1;
3) photoacoustic signal of ultrasonic detector 5 reception is after amplifier 6 amplifies, gathered by oscillograph 7, the signal message of collection is stored in computing machine 8 by oscillograph 7, computing machine 8 utilizes Labview programmed control stepper motor 2 pointwise moving tissue sample 9, corresponding tissue sample 9 forms X-Y two dimensional surface scanning area, stepper motor 2 often moves once, and oscillograph 7 just carries out a signals collecting;
4), after oscillograph 7 gathers full signal, computing machine 8 utilizes Matlab program that the signal of each point is carried out an integration to the time, obtains the function of time of tissue sample surface vibration displacement; Obtain tissue sample surface vibration displacement from above freezing rise to its maximal value time required time, as shown in Figure 2, give the variation relation of four kinds of displacements along with the time, different elastic modulus in figure, the time that displacement arrives needed for maximal value is not identical; By above-mentioned formula (6), utilize the quantitative elastic modulus of the tissue sample of this Time Calculation each point; According to the quantitative elastic modulus calculated, reconstruct the quantitative elasticity two dimensional image of tissue sample.
Embodiment 2:
The present embodiment is the experiment utilizing Agar samples to carry out, and mainly comprises the following steps:
1) be that the ink adding 10% in the agar of 20g/L makees squarely sample in concentration, in the middle of its, make the agar that concentration is 15g/L and square circular sample made by the ink adding 3%, this results in the Agar samples a in Fig. 3; Be that the ink adding 10% in the agar of 30g/L makees squarely sample in concentration, in the middle of its, make the agar that concentration is 25g/L and square circular sample made by the ink adding 3%, this results in the Agar samples b in Fig. 4;
2) start laser instrument, output pulse laser wavelength is 532nm, and pulsewidth is 10ns, and repetition frequency is 15Hz; This pulse laser is radiated at after being focused on by condenser lens on Agar samples a and b, and Agar samples a and b is inspired photoacoustic signal, and photoacoustic signal is received by ultrasonic detector after the coupling liquid in coupling slot;
3) photoacoustic signal of ultrasonic detector reception is after amplifier amplifies, and be transferred to oscillograph and carry out data acquisition, data are transmitted and are stored in computing machine by oscillograph again, and what computer-controlled stepper motor was corresponding forms scanning area on sample;
4) after gathering full signal, to the first normalization of the data gathered, then photoacoustic image and optoacoustic elastic image is rebuild with maximum value projection method and elasticity sciagraphy, Fig. 5 and Fig. 6 is the photoacoustic image of Agar samples a and b respectively, can find out, the background agar photoacoustic imaging of display does not almost have contrast, and the photoacoustic imaging of middle border circular areas does not almost have contrast yet; Fig. 7 and Fig. 8 is the optoacoustic elastic image of Agar samples a and b respectively, can find out, the optoacoustic elastic image of display then shows large contrast, which illustrates the necessity of optoacoustic elastogram; The elasticity number of what a and b in Fig. 9 showed respectively is Fig. 3 and Fig. 4 dotted line place Agar samples, can find out the significant change of elasticity number.
In sum, the present invention proposes the quantitative elastic modulus measuring method of a kind of tissue newly, compared with the method measured with existing relative resilient, without the need to normal structure as a reference, there is higher accuracy; Utilize laser focusing to carry out tissue elasticity detection, compared with traditional Ultrasonic elasticity detection method, there is tissue specificity and high resolution capacity; The ultrasonic detector adopted is nautical receiving set, has detection sensitivity advantage that is high, that limit without bandwidth, thus ensure that the ability of highly sensitive detection.
The above; be only patent preferred embodiment of the present invention; but the protection domain of patent of the present invention is not limited thereto; anyly be familiar with those skilled in the art in the scope disclosed in patent of the present invention; be equal to according to the technical scheme of patent of the present invention and inventive concept thereof and replace or change, all belonged to the protection domain of patent of the present invention.
Claims (10)
1. the quantitative elastograph imaging method of optoacoustic, is characterized in that: said method comprising the steps of:
1) tissue sample is placed on X-Y two-dimensional scan platform, and is immersed in the coupling liquid of coupling slot; Condenser lens is arranged on directly over tissue sample, and the height adjusting condenser lens makes the focus not offset groups tissue samples surface of condenser lens; Ultrasonic detector is aimed at tissue sample, and makes the lower end of ultrasonic detector enter in the coupling liquid of coupling slot;
2) laser instrument sends pulse laser, and this pulse laser is focused on by condenser lens, and impinge upon on tissue sample, inspire photoacoustic signal, photoacoustic signal is received by ultrasonic detector after the coupling liquid of coupling slot;
3) photoacoustic signal of ultrasonic detector reception is after amplifier amplifies, gathered by oscillograph, the signal message of collection is stored in computing machine by oscillograph, computer-controlled stepper motor pointwise moving tissue sample, corresponding tissue sample forms X-Y two dimensional surface scanning area, stepper motor often moves once, and oscillograph just carries out a signals collecting;
4), after oscillograph gathers full signal, the signal of each point is carried out an integration to the time by computing machine, obtains the function of time of tissue sample surface vibration displacement; Obtain tissue sample surface vibration displacement from above freezing rise to its maximal value time required time, utilize the quantitative elastic modulus of the tissue sample of this Time Calculation each point; According to the quantitative elastic modulus calculated, reconstruct the quantitative elasticity two dimensional image of tissue sample.
2. the quantitative elastograph imaging method of optoacoustic according to claim 1, it is characterized in that: step 1) in, described in the lower end of ultrasonic detector is entered in the coupling liquid of coupling slot be specially: make the lower end of ultrasonic detector enter the coupling liquid degree of depth 5-8mm place of coupling slot.
3. the quantitative elastograph imaging method of optoacoustic according to claim 1, it is characterized in that: step 3) in, described computer-controlled stepper motor pointwise moving tissue sample refers to: computing machine utilizes Labview programmed control stepper motor pointwise moving tissue sample; Step 4) in, the signal of each point is carried out an integration to the time and refers to by described computing machine: computing machine utilizes Matlab program that the signal of each point is carried out an integration to the time.
4. the quantitative elastograph imaging method of optoacoustic according to claim 1, is characterized in that: step 4) in, the quantitative elastic modulus of tissue sample of described calculating each point, adopts following formula:
Wherein, ρ is biological tissue's density, and R is laser facula radius, t
maxfor tissue sample surface vibration displacement from above freezing rise to its maximal value time required time.
5. the quantitative elastogram device of optoacoustic, is characterized in that: described device comprises photo-acoustic excitation source, signals collecting/transmission/reconstruction assembly, coupling slot, stepper motor and X-Y two-dimensional scan platform, and described photo-acoustic excitation source comprises laser instrument and condenser lens; Described signals collecting/transmission/reconstruction assembly comprises ultrasonic detector, amplifier, oscillograph and computing machine, and described ultrasonic detector, amplifier, oscillograph are connected successively with computing machine, and described computing machine is provided with to gather and controls and signal processing system; Described stepper motor is connected with computing machine, and described X-Y two-dimensional scan platform is placed in coupling slot, is full of coupling liquid in described coupling slot;
During test, tissue sample is placed on X-Y two-dimensional scan platform, and is immersed in the coupling liquid of coupling slot; Described condenser lens is arranged on directly over tissue sample, and the focus of condenser lens not offset groups tissue samples surface, the pulse laser that described laser instrument sends is focused on by condenser lens, impinges upon on tissue sample; Tissue sample aimed at by described ultrasonic detector, and the lower end of ultrasonic detector enters in the coupling liquid of coupling slot, the photoacoustic signal that tissue receiving sample is inspired; Described computer-controlled stepper motor pointwise moving tissue sample.
6. the quantitative elastogram device of optoacoustic according to claim 5, it is characterized in that: described device also comprises instrument and fixes/fixing device assembly, described instrument fixes/fixing device assembly for fixing/support X-Y two-dimensional scan platform, condenser lens and ultrasonic detector.
7. the quantitative elastogram device of the optoacoustic according to claim 5 or 6, is characterized in that: described ultrasonic detector is nautical receiving set, and its response frequency is 200KHz-15MHz, and diameter is 1mm; The piezoelectricity converting member of ultrasonic detector to be a thickness the be gold electrode PVDF membrane of 28 μm, when receiving photoacoustic signal, this gold electrode PVDF membrane aims at tissue sample.
8. the quantitative elastogram device of the optoacoustic according to claim 5 or 6, is characterized in that: described oscillographic sampling rate is 2.5GHz, and the collection control that described computing machine is installed and signal processing system utilize Labview and Matlab programming to form.
9. the quantitative elastogram device of the optoacoustic according to claim 5 or 6, is characterized in that: the pulse laser wavelength that described laser instrument sends is 400 ~ 2500nm, and pulse width is 1 ~ 50ns, and repetition frequency is 1Hz ~ 5KHz.
10. the quantitative elastogram device of the optoacoustic according to claim 5 or 6, is characterized in that: the coupling liquid in described coupling slot is water, and monitoring water temperature, makes the temperature of water temperature and tissue sample be consistent.
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Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
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Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1382983A (en) * | 2002-03-21 | 2002-12-04 | 江苏大学 | Nondestructive quantitative measuring method and device for photoacaustic performance of membrane-base coupling structure in micro optical-mechanical-electric system |
| JP2004351153A (en) * | 2003-05-30 | 2004-12-16 | Olympus Corp | Optical imaging apparatus |
| 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 |
-
2015
- 2015-12-16 CN CN201510944323.0A patent/CN105572049B/en active Active
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1382983A (en) * | 2002-03-21 | 2002-12-04 | 江苏大学 | Nondestructive quantitative measuring method and device for photoacaustic performance of membrane-base coupling structure in micro optical-mechanical-electric system |
| JP2004351153A (en) * | 2003-05-30 | 2004-12-16 | Olympus Corp | Optical imaging apparatus |
| CN102175776A (en) * | 2011-01-14 | 2011-09-07 | 华南师范大学 | Photoacoustic elastic imaging method and device |
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