CN103054610B - Photoacoustic imaging device free of limitation of ultrasonic transducer frequency bands and detection method of photoacoustic imaging device - Google Patents
Photoacoustic imaging device free of limitation of ultrasonic transducer frequency bands and detection method of photoacoustic imaging device Download PDFInfo
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Abstract
The invention discloses a photoacoustic imaging device free of limitation of ultrasonic transducer frequency bands and a detection method of the photoacoustic imaging device. The photoacoustic imaging device comprises a photoacoustic excitation assembly, a photoacoustic signal detection assembly, a photoacoustic signal collection/processing assembly and a sample platform, the photoacoustic excitation assembly, the photoacoustic signal detection assembly and the photoacoustic signal collection/processing assembly are sequentially connected, the photoacoustic excitation assembly and the photoacoustic signal collection/processing assembly are connected, and the photoacoustic signal detection assembly is connected with the sample platform. According to the photoacoustic imaging device, pulse lasers are used for radiating a biological sample to generate photoacoustic signals, continuous lasers with narrow line width are focused on the surface of the sample, vibration speeds of the surface of the sample are detected to achieve the purpose of detecting the photoacoustic signals, the defect of bandwidth limitation of the transducer is overcome, and the defects that high frequency photoacoustic signals are sharply attenuated in biological tissues and can not be detected are overcome; detection portions are not required to be subjected to any processing, requirements for imaging environment conditions are low, and large pushing functions on clinical performances of photoacoustic technology are achieved.
Description
Technical field
The invention belongs to photoacoustic imaging technology field, particularly a kind of opto-acoustic imaging devices without ultrasonic transducer frequency band limits and detection method thereof.
Background technology
When with photoirradiation certain absorber, absorbent body light energy and produce temperature rise, gradient of temperature causes the volume breathing of absorber, produces ultrasound wave, this phenomenon is called optoacoustic effect.Optoacoustic effect has received people's concern since 19th century were found always, and it has application in various degree in all fields.As a kind of novel imaging technique, photoacoustic imaging has obtained application in increasing field.This imaging technique is using short-pulse laser as driving source, and the ultrasonic signal exciting is thus as information carrier, by the signal collecting is carried out to image reconstruction, and then obtain the light absorption distributed intelligence of tissue, this technological incorporation the high-contrast of pure optical image technology and the high-resolution advantage of pure acoustics imaging.Photoacoustic imaging technology not only can effectively be portrayed mechanics of biological tissue, can also accurately realize harmless functional imaging, be the morphosis of postgraduate's fabric texture, physiology, pathological characters, metabolic functions etc. provide brand-new means, have broad application prospects at biomedical sector.
Traditional photoacoustic signal testing tool is all generally ultrasonic transducer, and photoacoustic signal has very wide frequency band, but conventional ultrasound transducer is subject to materials limitations, general frequency band is all narrower, and the narrower detector of the photoacoustic signal of wideband and frequency band has formed implacable contradiction.
Summary of the invention
Primary and foremost purpose of the present invention is that the shortcoming that overcomes prior art, with not enough, provides a kind of opto-acoustic imaging devices without ultrasonic transducer frequency band limits.
Another object of the present invention is to provide the detection method of using the above-mentioned opto-acoustic imaging devices without ultrasonic transducer frequency band limits.
Object of the present invention is achieved through the following technical solutions: a kind of opto-acoustic imaging devices without ultrasonic transducer frequency band limits, comprise photo-acoustic excitation assembly, photoacoustic signal detection components, photoacoustic signal collection/processing components and sample stage, described photo-acoustic excitation assembly, photoacoustic signal detection components and photoacoustic signal collection/processing components are connected successively, photo-acoustic excitation assembly is connected with photoacoustic signal collection/processing components, and photoacoustic signal detection components is connected with sample stage;
Described photo-acoustic excitation assembly comprises photoacoustic signal detection light source, beam splitter, dichroic mirror, photo-acoustic excitation light source and two-dimensional scan galvanometer, photoacoustic signal detection light source, beam splitter, dichroic mirror and two-dimensional scan galvanometer are connected successively, photo-acoustic excitation light source is connected with dichroic mirror, photoacoustic signal collection/processing components respectively, and two-dimensional scan galvanometer is connected with photoacoustic signal collection/processing components; Photo-acoustic excitation assembly is mainly used in excited sample and produces photoacoustic signal;
Described photoacoustic signal detection components (confocal scanning assembly) comprises flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C, condenser lens, photomultiplier tube A, photomultiplier tube B and piezoelectric ceramic actuator; Described flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C, condenser lens and photomultiplier tube A are connected successively, photomultiplier tube B is connected with piezoelectric ceramic actuator, polarization beam apparatus C respectively, and piezoelectric ceramic actuator is connected with Confocal Fabry-Perot Interferometer, photoacoustic signal collection/processing components respectively; Photomultiplier tube A, B are connected with photoacoustic signal collection/processing components respectively; Flat-field objective is connected with described sample stage; Polarization beam apparatus A is connected with two-dimensional scan galvanometer; Polarization beam apparatus B is connected with beam splitter;
Between described flat-field objective and polarization beam apparatus A, quarter wave plate is set; The Main Function of quarter wave plate is to make the yawing moment of light beam change pi/2, ensures that backward scattered flashlight, all by polarization beam apparatus A, polarization beam apparatus B and polarization beam apparatus C, finally all focuses on photomultiplier tube A;
The Main Function of photoacoustic signal detection components is the vibration velocity that detects the sample surfaces that is excited, what speed was corresponding is exactly photoacoustic signal, can cause the detection light frequency reflecting back through sample surfaces to change by the known surface vibration velocity of Doppler effect, and the detection of this frequency displacement rely on confocal fabry perot interferometer to realize; Be all-trans through polarization beam apparatus B from beam splitter light beam out, seeing through Confocal Fabry-Perot Interferometer is being all-trans to photomultiplier tube B through polarization beam apparatus C, optical signal is converted into the signal of telecommunication, after collecting data by capture card, analyze, then feed back to piezoelectric ceramic actuator and carry out stable operating point with the chamber length of controlling Confocal Fabry-Perot Interferometer; Another light beam process dichroic mirror and galvanometer and polarization beam apparatus A, quarter wave plate, flat-field objective are radiated at sample surfaces, and backward scattered light process flat-field objective, quarter wave plate, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C and condenser lens are until photomultiplier tube A;
Described photoacoustic signal collection/processing components is made up of coaxial cable, capture card and computer, and capture card is connected with computer, and computer is connected with piezoelectric ceramic actuator; Capture card is connected with described photomultiplier tube A, photomultiplier tube B respectively by coaxial cable;
Described computer is provided with acquisition controlling and signal processing system;
Acquisition controlling and signal processing system that described acquisition controlling and signal processing system preferably adopt Labview and Matlab to write voluntarily;
Described photo-acoustic excitation assembly, photoacoustic signal detection components and photoacoustic signal collection/processing components are electrically connected successively;
Described Confocal Fabry-Perot Interferometer, piezoelectric ceramic actuator, photomultiplier tube B and a closed servosystem of computer composition; Described closed servosystem refers to from beam splitter light beam out and is all-trans through polarization beam apparatus B, seeing through Confocal Fabry-Perot Interferometer is being all-trans to photomultiplier tube B through polarization beam apparatus C, optical signal is converted into the signal of telecommunication, computer is analyzed after collecting data by capture card, then feeds back to piezoelectric ceramic actuator and carrys out stable operating point with the chamber length of controlling Confocal Fabry-Perot Interferometer;
Described photo-acoustic detection light source is divided into two-beam by beam splitter;
Described photo-acoustic excitation light source and photo-acoustic detection light source are combined into light beam by dichroic mirror;
Described photo-acoustic excitation light source, photo-acoustic detection light source and the strict optics of dichroic mirror are coaxial;
Described flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C, condenser lens, photomultiplier tube A, photomultiplier tube B and the strict optics of piezoelectric ceramic actuator are coaxial;
The detection method of using the above-mentioned opto-acoustic imaging devices without ultrasonic transducer frequency band limits, comprises the following steps:
(1) photoacoustic signal detection components is placed in sample surfaces directly over;
(2) photo-acoustic excitation light and photoacoustic signal detect light and are combined into light beam by dichroic mirror, and are irradiated to sample surfaces through two-dimensional scan galvanometer, polarization beam apparatus A and flat-field objective successively, make photoacoustic signal detection light focus on the surface of sample;
(3) photo-acoustic excitation illumination is mapped on sample, after absorption of sample luminous energy, produces photoacoustic signal, and photoacoustic signal causes the vibration of sample surfaces; The vibration of sample surfaces causes that photoacoustic signal detects light and produces Doppler frequency shift, and the rear orientation light and the reflected light light intensity after confocal fabry perot interferometer that produce the sample surfaces of Doppler frequency shift can produce corresponding variation;
(4) rear orientation light of sample surfaces and reflected light are upper by being radiated at photomultiplier tube A after flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C and condenser lens successively, and the variation of the upper light intensity of photomultiplier tube A is photoacoustic signal; The drift angle separately that changes two-dimensional scan galvanometer X, Y-axis deflects photo-acoustic excitation light and photoacoustic signal detection light, and once, capture card just carries out a data acquisition to the every deflection of two-dimensional scan galvanometer;
(5) gathered after whole signals, reconstructed optoacoustic two dimensional image and the 3-D view of tissue sample by the method for maximum projection;
The pulse laser wavelength of described photo-acoustic excitation light source is 400～2500nm, and pulsewidth is 1～50ns, and repetition rate is 1Hz～50kHz;
The wavelength of described photoacoustic signal detection light source is 300～800nm, and live width is 1～20MHz;
Preferably, the pulse laser wavelength of described photo-acoustic excitation light source is 532nm, and pulsewidth is 10ns, and repetition rate is 20Hz;
Preferably, the wavelength of described photoacoustic signal detection light source is 632.8nm, and live width is 10MHz;
The method for building up of described 3-D view preferably carries out in the following ways: all photoacoustic signals are got same time yardstick and done longitudinal section projection, by the photoacoustic image obtaining after projection reconstruction of three-dimensional images on three-dimensional reconstruction software volview3.2, in three-dimensional reconstruction software, rotate whole 3-D view and obtain the 3-D view of visual angle;
The described opto-acoustic imaging devices without ultrasonic transducer frequency band limits can be applicable to biomedical sector, especially can be applicable to morphosis, physiology and the pathological characters of postgraduate's fabric texture;
Action principle of the present invention: the pulse laser that photo-acoustic excitation light source produces, focus on sample by flat-field objective, sample produces photoacoustic signal, and photoacoustic signal can cause the vibration on biological tissue surface; And photoacoustic signal detection light focuses on sample surfaces by flat-field objective equally, because the vibration of sample surfaces can cause rear orientation light and the catoptrical generation Doppler frequency shift of sample surfaces, rear orientation light and the reflected light light intensity after confocal fabry perot interferometer of sample surfaces that produces Doppler frequency shift can produce corresponding variation, and the change that detects light intensity by photomultiplier tube can reflect the size of produced photoacoustic signal; Then the drift angle separately that changes two-dimensional scan galvanometer X, Y-axis deflects photo-acoustic excitation light and photoacoustic signal detection light, and once, capture card just carries out a data acquisition to the every deflection of two-dimensional scan galvanometer.Gather after whole signals, reconstructed optoacoustic two dimensional image and the 3-D view of tissue sample by the method for maximum projection.
The present invention has following advantage and effect with respect to prior art:
(1) the present invention utilizes pulsed laser irradiation biological sample to produce photoacoustic signal, then use compared with the continuous laser of narrow linewidth and focus on biological tissue surface, because the vibration on biological sample surface can cause that photoacoustic signal detects light and produces Doppler frequency shift, and Doppler frequency shift can cause the rear orientation light of sample surfaces and catoptrical light intensity to produce corresponding change, the speed of the vibration by detecting the biological tissue surface causing due to photoacoustic signal reaches the object that detects photoacoustic signal, has broken away from the limit bandwidth defect of traditional transducer.
(2) the present invention can detect at photoacoustic signal source place, has so just prevented the sharp-decay of high frequency light acoustical signal in biological tissue and shortcoming that can not be detected.Contactless photoacoustic signal detection method of the present invention has been broken away from the restriction of traditional coupling opto-acoustic signal detection, has also broken away from the restriction of traditional photoacoustic signal detection position, can carry out photo-acoustic detection to any position.
(3) the present invention does not need to do any processing to detecting position, lower to imaging circumstances conditional request, has very large impetus for clinicalization that realizes photoacoustic technique.
Brief description of the drawings
Fig. 1 is the structural representation of the opto-acoustic imaging devices without ultrasonic transducer frequency band limits of embodiment 1.Wherein: 1-1 is photoacoustic signal detection light source, 1-2 is photo-acoustic excitation light source, 1-3 is beam splitter, 1-4 is dichroic mirror, 1-5 is two-dimensional scan galvanometer, 2 is sample stage, 3-1 is flat-field objective, and 3-2 is quarter wave plate, and 3-3 is polarization beam apparatus A, 3-4 is polarization beam apparatus B, 3-5 is Confocal Fabry-Perot Interferometer, and 3-6 is polarization beam apparatus C, and 3-7 is photomultiplier tube B, 3-8 is piezoelectric ceramic actuator, and 3-9 is that condenser lens, 3-10 are that photomultiplier tube A, 4 is the computer with photoacoustic signal collection/processing system.
Fig. 2 is the schematic diagram that light intensity frequency displacement changes.
Fig. 3 is the optoacoustic two dimensional image of the mouse back blood vessel of embodiment 2.
Detailed description of the invention
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 to this.
Embodiment 1
As shown in Figure 1, a kind of opto-acoustic imaging devices without ultrasonic transducer frequency band limits, comprise photo-acoustic excitation assembly, photoacoustic signal detection components, photoacoustic signal collection/processing components 4 and sample stage 2, described photo-acoustic excitation assembly, photoacoustic signal detection components and photoacoustic signal collection/processing components are connected successively, photo-acoustic excitation assembly is connected with photoacoustic signal collection/processing components, and photoacoustic signal detection components is connected with sample stage 2;
Described photo-acoustic excitation assembly comprises photoacoustic signal detection light source 1-1, beam splitter 1-3, dichroic mirror 1-4, photo-acoustic excitation light source 1-2 and two-dimensional scan galvanometer 1-5, photoacoustic signal detection light source 1-1, beam splitter 1-3, dichroic mirror 1-4 and two-dimensional scan galvanometer 1-5 are connected successively, photo-acoustic excitation light source 1-2 is connected with dichroic mirror 1-4, photoacoustic signal collection/processing components 4 respectively, and two-dimensional scan galvanometer 1-5 is connected with photoacoustic signal collection/processing components 4;
Described photoacoustic signal detection components (confocal scanning assembly) comprises flat-field objective 3-1, polarization beam apparatus A3-3, polarization beam apparatus B3-4, Confocal Fabry-Perot Interferometer 3-5, polarization beam apparatus C3-6, condenser lens 3-9, photomultiplier transit A pipe 3-10, photomultiplier tube B3-7 and piezoelectric ceramic actuator 3-8; Described flat-field objective 3-1, polarization beam apparatus A3-3, polarization beam apparatus B3-4, Confocal Fabry-Perot Interferometer 3-5, polarization beam apparatus C3-6, condenser lens 3-9 and photomultiplier tube A3-10 are connected successively, photomultiplier tube B3-7 is connected with piezoelectric ceramic actuator 3-8, polarization beam apparatus C3-6 respectively, and piezoelectric ceramic actuator 3-8 is connected with Confocal Fabry-Perot Interferometer 3-5, photoacoustic signal collection/processing components 4 respectively; Photomultiplier tube A3-10 is connected with photoacoustic signal collection/processing components 4; Flat-field objective 3-1 is connected with sample stage 2; Polarization beam apparatus B3-4 is connected with beam splitter 1-3; Polarization beam apparatus A3-3 is connected with two-dimensional scan galvanometer 1-5;
Between flat-field objective 3-1 and polarization beam apparatus A3-3, quarter wave plate 3-2 is set;
Described photoacoustic signal collection/processing components is made up of coaxial cable, capture card and computer, and capture card is connected with computer, and computer is connected with piezoelectric ceramic actuator; Capture card is connected with described photomultiplier tube A, photomultiplier tube B respectively by coaxial cable;
Described computer is provided with acquisition controlling and signal processing system;
Acquisition controlling and signal processing system that described acquisition controlling and signal processing system adopt Labview and Matlab to write voluntarily;
Described photo-acoustic excitation assembly, photoacoustic signal detection components and photoacoustic signal collection/processing components are electrically connected successively;
Described Confocal Fabry-Perot Interferometer, piezoelectric ceramic actuator, photomultiplier tube and a closed servosystem of computer composition; Described closed servosystem refers to from beam splitter light beam out and is all-trans through polarization beam apparatus B, seeing through Confocal Fabry-Perot Interferometer is being all-trans to photomultiplier tube B through polarization beam apparatus C, optical signal is converted into the signal of telecommunication, computer is analyzed after collecting data by capture card, then feeds back to piezoelectric ceramic actuator and carrys out stable operating point with the chamber length of controlling Confocal Fabry-Perot Interferometer;
Described photo-acoustic detection light source is divided into two-beam by beam splitter;
Described photo-acoustic excitation light source and photo-acoustic detection light source are combined into light beam by dichroic mirror;
Described photo-acoustic excitation light source, photo-acoustic detection light source and the strict optics of dichroic mirror are coaxial;
Described flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C, condenser lens, photodiode, photomultiplier tube and the strict optics of piezoelectric ceramic actuator are coaxial;
The pulse laser that photo-acoustic excitation light source 1-2 produces, focuses on sample by flat-field objective 3-1, and sample produces photoacoustic signal, and photoacoustic signal can cause the vibration on biological tissue surface; And photoacoustic signal detection light focuses on sample surfaces by usual object lens equally, because the vibration of sample surfaces can cause rear orientation light and the catoptrical generation Doppler frequency shift of sample surfaces, the rear orientation light and the reflected light light intensity after confocal fabry perot interferometer that produce the sample surfaces of Doppler frequency shift can produce corresponding variation, detect the change of light intensity by photomultiplier tube, be the photoacoustic signal of biological tissue; Then the drift angle separately that changes two-dimensional scan galvanometer X, Y-axis deflects photo-acoustic excitation light and photoacoustic signal detection light, and once, capture card just carries out a data acquisition to the every deflection of two-dimensional scan galvanometer.Gather after whole signals, reconstructed optoacoustic two dimensional image and the 3-D view of tissue sample by the method for maximum projection.
Embodiment 2
The detection method of using the opto-acoustic imaging devices without ultrasonic transducer frequency band limits of embodiment 1, comprises the following steps:
(1) toward the 2% pentobarbital sodium solution of two weeks large Kunming white mice injection 0.5mL, after mouse anesthesia, employment is removed the hair of mouse back with depilatory cream, then mice is placed on sample stage and is fixed;
(2) photoacoustic signal detection components be placed in mice surface directly over; Regulate sample stage height to make to detect light to focus on the surface of mouse back;
(3) photo-acoustic excitation light and photoacoustic signal detect light and are combined into light beam by dichroic mirror, are irradiated to successively the surface of mouse back through two-dimensional scan galvanometer, polarization beam apparatus A and flat-field objective, make photoacoustic signal detection light focus on the surface of mouse back;
(4) photo-acoustic excitation illumination is mapped on the surface of mouse back, after the Surface absorption luminous energy of mouse back, produces photoacoustic signal, and photoacoustic signal causes the surperficial vibration of mouse back; The surperficial vibration of mouse back causes that photoacoustic signal detects light and produces Doppler frequency shift, and Doppler frequency shift causes the surperficial rear orientation light of mouse back and catoptrical light intensity to produce change;
(5) the surperficial rear orientation light of mouse back and reflected light are successively by being radiated on photodiode after flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C and condenser lens, and on photodiode, the variation of light intensity is photoacoustic signal; The drift angle separately that changes two-dimensional scan galvanometer X, Y-axis deflects photo-acoustic excitation light and photoacoustic signal detection light, and once, capture card just carries out a data acquisition to the every deflection of two-dimensional scan galvanometer;
(6) gathered after whole signals, gone out the optoacoustic two dimensional image of mouse back tissue by maximum backprojection reconstruction, be illustrated in figure 3 the blood-vessel image of mouse back;
The pulse laser wavelength of described photo-acoustic excitation light source is 532nm, and pulsewidth is 10ns, and repetition rate is 20Hz;
The wavelength of described photoacoustic signal detection light source is 632.8nm, and live width is 10MHz.
Above-described embodiment is preferably embodiment of the present invention; but embodiments of the present invention are not restricted to the described embodiments; other any do not deviate from change, the modification done under spirit of the present invention and principle, substitutes, combination, simplify; all should be equivalent substitute mode, within being included in protection scope of the present invention.
Claims (8)
1. the opto-acoustic imaging devices without ultrasonic transducer frequency band limits, it is characterized in that comprising photo-acoustic excitation assembly, photoacoustic signal detection components, photoacoustic signal collection/processing components and sample stage, described photo-acoustic excitation assembly, photoacoustic signal detection components and photoacoustic signal collection/processing components are connected successively, photo-acoustic excitation assembly is connected with photoacoustic signal collection/processing components, and photoacoustic signal detection components is connected with sample stage;
Described photo-acoustic excitation assembly comprises photoacoustic signal detection light source, beam splitter, dichroic mirror, photo-acoustic excitation light source and two-dimensional scan galvanometer, photoacoustic signal detection light source, beam splitter, dichroic mirror and two-dimensional scan galvanometer are connected successively, photo-acoustic excitation light source is connected with dichroic mirror, photoacoustic signal collection/processing components respectively, and two-dimensional scan galvanometer is connected with photoacoustic signal collection/processing components;
Described photoacoustic signal detection components comprises flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C, condenser lens, photomultiplier tube A, photomultiplier tube B and piezoelectric ceramic actuator; Described flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C, condenser lens and photomultiplier tube A are connected successively, photomultiplier tube B is connected with piezoelectric ceramic actuator, polarization beam apparatus C respectively, and piezoelectric ceramic actuator is connected with Confocal Fabry-Perot Interferometer, photoacoustic signal collection/processing components respectively; Photomultiplier tube A, B are connected with photoacoustic signal collection/processing components respectively; Flat-field objective is connected with described sample stage; Polarization beam apparatus A is connected with two-dimensional scan galvanometer; Polarization beam apparatus B is connected with beam splitter.
2. the opto-acoustic imaging devices without ultrasonic transducer frequency band limits according to claim 1, is characterized in that: between described flat-field objective and polarization beam apparatus A, quarter wave plate is set.
3. the opto-acoustic imaging devices without ultrasonic transducer frequency band limits according to claim 1, it is characterized in that: described photoacoustic signal collection/processing components is made up of coaxial cable, capture card and computer, capture card is connected with computer, and computer is connected with piezoelectric ceramic actuator; Capture card is connected with described photomultiplier tube A, photomultiplier tube B respectively by coaxial cable.
4. the opto-acoustic imaging devices without ultrasonic transducer frequency band limits according to claim 1, is characterized in that: described photo-acoustic excitation assembly, photoacoustic signal detection components and photoacoustic signal collection/processing components are electrically connected successively.
5. the opto-acoustic imaging devices without ultrasonic transducer frequency band limits according to claim 1, is characterized in that: described Confocal Fabry-Perot Interferometer, piezoelectric ceramic actuator, photomultiplier tube B and a closed servosystem of computer composition; Described photo-acoustic excitation light source, photo-acoustic detection light source and the strict optics of dichroic mirror are coaxial.
6. the opto-acoustic imaging devices without ultrasonic transducer frequency band limits according to claim 1, is characterized in that: described flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C, condenser lens, photomultiplier tube A, photomultiplier tube B and the strict optics of piezoelectric ceramic actuator are coaxial.
7. the detection method of the opto-acoustic imaging devices without ultrasonic transducer frequency band limits described in utilization claim 1～6 any one, is characterized in that comprising the following steps:
(1) photoacoustic signal detection components is placed in sample surfaces directly over;
(2) photo-acoustic excitation light and photoacoustic signal detect light and are combined into light beam by dichroic mirror, and are irradiated to sample surfaces through two-dimensional scan galvanometer, polarization beam apparatus A and flat-field objective successively, make photoacoustic signal detection light focus on the surface of sample;
(3) photo-acoustic excitation illumination is mapped on sample, after absorption of sample luminous energy, produces photoacoustic signal, and photoacoustic signal causes the vibration of sample surfaces; The vibration of sample surfaces causes that photoacoustic signal detects light and produces Doppler frequency shift, and the rear orientation light and the reflected light light intensity after confocal fabry perot interferometer that produce the sample surfaces of Doppler frequency shift can change;
(4) rear orientation light of sample surfaces and reflected light are upper by being radiated at photomultiplier tube A after flat-field objective, polarization beam apparatus A, polarization beam apparatus B, Confocal Fabry-Perot Interferometer, polarization beam apparatus C and condenser lens successively, and the variation of the upper light intensity of photomultiplier tube A is photoacoustic signal; The drift angle separately that changes two-dimensional scan galvanometer X, Y-axis deflects photo-acoustic excitation light and photoacoustic signal detection light, and once, capture card just carries out a data acquisition to the every deflection of two-dimensional scan galvanometer;
(5) gathered after whole signals, reconstructed optoacoustic two dimensional image and the 3-D view of tissue sample by the method for maximum projection.
8. the detection method of the opto-acoustic imaging devices without ultrasonic transducer frequency band limits according to claim 7, is characterized in that:
The pulse laser wavelength of described photo-acoustic excitation light source is 400～2500nm, and pulsewidth is 1～50ns, and repetition rate is 1Hz～50kHz;
The wavelength of described photoacoustic signal detection light source is 300～800nm, and live width is 1～20MHz.
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| CN104323762B (en) * | 2014-12-01 | 2017-09-22 | 广州佰奥廷电子科技有限公司 | A kind of nevus flammeus blood vessel quantification detection means based on opto-acoustic microscopic imaging |
| CN104490365B (en) * | 2015-01-12 | 2017-01-11 | 南京大学 | Method for rebuilding broad-band photo-acoustic image by using narrow-band sensor |
| JP6553210B2 (en) * | 2015-01-15 | 2019-07-31 | ハーリング、ロドニー | Diffuse acoustic confocal imaging device |
| CN106618496A (en) * | 2016-12-09 | 2017-05-10 | 华南师范大学 | All-optical photoacoustic Doppler transverse flow speed measuring method and device |
| CN106769878B (en) * | 2016-12-12 | 2023-10-03 | 福建工程学院 | Photoacoustic spectrum-based traditional Chinese medicine decoction component detection method and device |
| CN108051369B (en) * | 2017-11-30 | 2021-02-12 | 华南师范大学 | Non-contact all-optical photoacoustic imaging device and method thereof |
| CN115791632B (en) * | 2022-12-09 | 2024-06-14 | 东北大学秦皇岛分校 | Intravascular ultrasound imaging device and intravascular ultrasound imaging method |
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