CN216926576U - Photoacoustic microfluidic detection system - Google Patents
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- CN216926576U CN216926576U CN202123053553.8U CN202123053553U CN216926576U CN 216926576 U CN216926576 U CN 216926576U CN 202123053553 U CN202123053553 U CN 202123053553U CN 216926576 U CN216926576 U CN 216926576U
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Abstract
The utility model provides a photoacoustic microfluidic detection system, and belongs to the technical field of photoacoustic detection. The detection system comprises a laser excitation module, a laser detection module, a micro-fluidic chip and a signal processing module, wherein the micro-fluidic chip comprises a substrate, a micro-channel arranged on the substrate, a liquid inlet and a liquid outlet which are communicated with the micro-channel, and a prism arranged above the micro-channel, the laser excitation module is used for exciting a target sample in the micro-channel below the prism to emit ultrasonic waves, the laser detection module comprises a polarization beam splitter and a balance light detector, and the balance light detector is used for converting the change of the intensity difference of S polarized light and P polarized light into a voltage signal; the input end of the signal processing module is connected with the output end of the balanced light detector and used for receiving and processing the voltage signal of the balanced light detector to obtain the photoacoustic signal of the target sample. The utility model has simple detection mode and low cost.
Description
Technical Field
The utility model relates to a photoacoustic detection technology, in particular to a photoacoustic microfluidic detection system.
Background
Microfluidics is a rapidly evolving tool that enables researchers to exercise unprecedented control over microscale environments. Microfluidic technology is being used in numerous fields, including biology, materials science, medicine, chemistry, and physics. Working within microchannels, researchers can manipulate the various components of the system in which they are interested with high resolution. Small size and small volume systems have many other key advantages, including portability, low cost, rapid prototyping, easier automation, and the ability to use limited sample sizes and reagents. Consequently, microfluidic research has grown enormously over the last 20 years, resulting in a large number of microfluidic applications.
Microfluidics refers primarily to a new technology for active or passive manipulation of one or more fluids in a microscale space, which can reduce the basic functions of chemical, biological, etc. laboratories to a few square centimeters on a chip, and is therefore also referred to as lab-on-a-chip. The technology also shows great potential in the fields of drug discovery, tissue engineering, nanotechnology and the like, so that thousands of drugs, genes or chemical samples can be rapidly analyzed and processed on a lab-on-a-chip platform.
In this case, it is necessary to develop a high-speed detection scheme for dynamic detection of a target sample in a microfluidic channel. Researchers have proposed many methods such as surface enhanced raman scattering spectroscopy, electrical impedance sensing, laser induced fluorescence, etc. Among these techniques, laser-induced fluorescence is the most widely used technique due to its high sensitivity and specificity. However, in view of the mechanism of fluorescence, a photoelectric sensor such as a photomultiplier tube or an avalanche photodiode must be used for measurement, and this detection method often requires a certain measurement time and sacrifices the time resolution. In addition, labeling the sample with fluorescence inevitably contaminates the target analyte to some extent, affecting detection and collection of the target analyte.
Therefore, many research groups desire new detection tools with high sensitivity and high speed to provide more physical and chemical information for target samples in microfluidic channels. The photoacoustic detection is a novel detection technology based on the photoacoustic effect, has the advantages of no mark, high sensitivity, good contrast, high imaging speed and the like, and is gradually applied to the field of microfluidics. There is some room for improvement in this technology due to the effect of the ultrasound transducer as a photoacoustic probe.
The current photoacoustic detection system applied to microfluidics uses an ultrasonic transducer for detection. The ultrasonic transducer is made of piezoelectric materials, and due to the limitation of the piezoelectric materials, the ultrasonic transducer is narrow in bandwidth, single in frequency band, insufficient in small-size sensitivity and high in cost. So far, no highly integrated photoacoustic detection system can perform wide-bandwidth photoacoustic detection on microfluidics on the basis of simple structure and low cost.
SUMMERY OF THE UTILITY MODEL
In order to solve the problems in the prior art, the utility model provides a photoacoustic microfluidic detection system.
11. The utility model comprises a laser excitation module, a laser detection module, a micro-fluidic chip and a signal processing module, wherein,
the micro-fluidic chip comprises a substrate, a micro-channel arranged on the substrate, a liquid inlet and a liquid outlet which are communicated with the micro-channel, and a prism arranged above the micro-channel,
the laser excitation module is used for exciting a target sample in the micro-channel below the prism to emit ultrasonic waves,
the laser detection module comprises a polarization beam splitter and a balance light detector, the laser detection module receives photoacoustic signals generated after a target sample is excited, light beams are divided into S polarized light and P polarized light through the polarization beam splitter and then are respectively output to the balance light detector, and the balance light detector is used for converting the change of the intensity difference of the S polarized light and the P polarized light into voltage signals;
the input end of the signal processing module is connected with the output end of the balanced light detector and used for receiving and processing the voltage signal of the balanced light detector to obtain the photoacoustic signal of the target sample.
The utility model is further improved, and the laser excitation module comprises a first laser light source which is pulse laser.
The utility model is further improved, 3. the laser excitation module also comprises a first light path and a photoelectric probe which are arranged at the output end of the first laser light source, the first light path outputs two paths of light beams, one path of light beams is received by the photoelectric probe, the other path of light beams is used for exciting a sample to emit ultrasonic waves,
the signal processing module is also connected with the photoelectric probe and takes the photoelectric signal received by the photoelectric probe as trigger.
The utility model is further improved, the first light path comprises a beam expander, a light filter, a first beam splitter, a first reflector and an objective lens, pulse laser emitted by the first laser source is collimated and amplified by the beam expander, then is filtered by the light filter, and is split by the first beam splitter, one beam of light enters the photoelectric probe, the other beam of light enters the objective lens after being reflected by the first reflector, and is focused on a target sample in the microfluidic chip, so that the sample is excited to emit ultrasonic waves.
The utility model is further improved, the signal processing module comprises a filter, an amplifier and an oscilloscope, the input end of the filter is connected with the output end of the laser detection module balanced light detector, the output end of the filter is connected with the input end of the amplifier, the output end of the amplifier is connected with the input end of the oscilloscope, and the oscilloscope outputs the photoacoustic signal of the target sample.
The utility model is further improved, the laser detection module comprises a second laser light source, a second light path arranged on the incident side of the prism and used for processing the second laser light source, and a third light path arranged on the reflection side of the prism and containing the third light path, the output end of the third light path is connected with the input end of the polarization beam splitter, and the second laser light source is a continuous laser light source.
12. The utility model is further improved, the second light path comprises a polarizer, an 1/4 wave plate, a first lens and a second reflector, the continuous laser emitted by the second laser source is changed into linearly polarized light by the polarizer, the linearly polarized light is changed into circularly polarized light by the 1/4 wave plate, the circularly polarized light is focused by the first lens to be used as detection light, the detection light is incident into the prism from the side surface of the prism by taking the angle close to the total reflection angle as the incident angle after passing through the second reflector, and is focused on the lower bottom surface of the prism,
the third light path comprises a third reflector and a second lens, and reflected light emitted by the lenses is reflected by the third reflector, focused by the second lens and enters the polarization beam splitter.
13. The utility model is further improved, the second light path comprises a polarizer, 1/4 wave plates, an optical fiber, a first optical fiber collimating mirror and a second optical fiber collimating mirror which are arranged at two ends of the optical fiber, and a first focusing lens which is arranged at the rear end of the second optical fiber collimating mirror, continuous laser emitted by the second laser source is changed into linearly polarized light through the polarizer, the linearly polarized light is changed into circularly polarized light through the 1/4 wave plate, the circularly polarized light passes through the first optical fiber collimating mirror, is collected by the optical fiber, and is transmitted to the second optical fiber collimating mirror through the optical fiber, the light emitted by the second optical fiber collimating mirror is focused at the middle part of the detection window through the first focusing lens,
the third light path comprises a second focusing lens, an optical fiber, a third optical fiber collimating lens and a fourth optical fiber collimating lens which are arranged at two ends of the optical fiber, and further comprises a second lens and a polarization beam splitter, reflected light passes through the third optical fiber collimating lens after passing through the second focusing lens, is collected by the optical fiber and is transmitted to the fourth optical fiber collimating lens, is focused by the second lens, and is divided into two beams by the polarization beam splitter according to S polarized light and P polarized light in reflected light, and the two beams are received by two probes of the high-bandwidth balance light detector respectively.
The utility model is further improved, the prism, the second fiber collimator, the first focusing lens, the second focusing lens and the third fiber collimator are integrally arranged into a combined lens, the prism is an isosceles prism with a base angle slightly smaller than a total reflection angle, the second fiber collimator, the first focusing lens, the second focusing lens and the third fiber collimator are symmetrically embedded at two sides of the prism, lens surfaces of the second fiber collimator and the third fiber collimator are arranged in parallel with the side surface of the prism, and the first focusing lens converges light beams at the middle of the bottom surface of the prism.
The utility model is further improved, the microfluidic chip comprises a glass slide substrate, a substrate arranged above the glass slide substrate and a prism arranged in the detection area of the substrate, and the micro-channel is arranged on the substrate below the prism.
Compared with the prior art, the utility model has the beneficial effects that: in the detection process, the target sample does not need to be subjected to fluorescence labeling, the detection mode is simple, and the complex problem that the sample in the microfluidic chip needs to be labeled in the prior art is solved. Meanwhile, the photoacoustic probe of the photoacoustic microfluidic system has the advantages of wider detection bandwidth, simpler structure, smaller volume and lower cost, is more suitable for being combined with microfluidic technology, and has wider application prospect in microfluidic application.
Drawings
FIG. 1 is a schematic structural diagram of an embodiment of a probing system according to the present invention;
FIG. 2 is a schematic diagram of the operation of the microfluidic chip according to the present invention;
FIG. 3 is a schematic structural diagram of another embodiment of a detection system according to the present invention;
FIG. 4 is a schematic view of a combined lens structure according to the present invention;
FIG. 5 is a schematic diagram of a first sample being detected according to the present invention;
FIG. 6 is a diagram illustrating a photoacoustic signal from a first sample;
FIG. 7 is a schematic diagram of a second sample being probed according to the utility model;
fig. 8 is a diagram illustrating a photoacoustic signal of a second sample.
Detailed Description
The present invention will be described in further detail with reference to the accompanying drawings and examples.
The photoacoustic microfluidic detection system comprises a laser excitation module, a laser detection module, a microfluidic chip and a signal processing module.
Microfluidic detection system example 1:
as shown in fig. 1 and fig. 2, the laser excitation module includes a pulse excitation light source 1, a beam expander 2, a filter 3, a beam splitter 4, a reflector M, an objective 6, and a photoelectric probe. A pulse laser is emitted from a pulse excitation light source 1, is collimated and amplified by a beam expander 2, is filtered by a light filter 3, is split by a beam splitter 4, and one beam of light enters a photoelectric probe 5 to serve as a trigger signal of a subsequent signal processing module. The other beam of light 500 is reflected by the mirror M into the objective 6, focused on the sample in the microfluidic chip microchannel 400, and excites the sample to emit ultrasonic waves.
The laser detection module comprises a continuous laser light source 7, a polarizer 8, an 1/4 wave plate 9, a lens L, a reflector M, a polarization beam splitter 11 and a balance light detector 12. The continuous laser source emits a continuous laser beam, which is converted into linearly polarized light by the polarizer 8 and converted into circularly polarized light by the 1/4 wave plate 9. The circularly polarized light is focused as probe light 600 by the first lens L. The detection light 600 enters the prism 10 from the side surface of the prism 10 at a certain angle after passing through the reflector M, is focused on the lower bottom surface of the prism 10, and is totally internally reflected at the focal point, forming a detection window at the focal point. When ultrasonic waves exist in the water on the lower surface of the prism 10, the refractive index of the water around the detection window is changed, and the energy of the P polarized light and the S polarized light in the modulated reflected light is subjected to nonlinear change with different responses. In the range where the incident angle is close to the total reflection angle, the P-polarized light and the S-polarized light are most sensitive to the change of the refractive index of water, and the signal difference between the two is also the largest. The angle of incidence is then reduced to just that total reflection does not occur by fine tuning the mirrors of the entrance prism, with this angle close to the angle of total reflection being taken as the angle of incidence. The reflected light 700 reflected from the detection window passes through the prism 10, is reflected by the mirror M, is focused by the second lens L, and then is split into two beams by the polarization beam splitter 11, wherein the two beams are respectively received by the two probes of the high-bandwidth balanced light detector 12.
The microfluidic chip is formed by packaging a lower layer of glass slide substrate 100, an upper layer of PDMS plate 200 and a prism 10 of a detection area. In which the prism 10 is embedded in a PDMS (Polydimethylsiloxane), a polymer organic silicon compound, plate. Wherein, the lower surface of the PDMS plate 200 is engraved with a liquid inlet, a micro flow channel 400 and a liquid outlet.
The microfluidic chip of the embodiment comprises the following manufacturing steps:
1. selecting adhesive tapes with different thicknesses according to requirements, and then cutting the adhesive tapes by using laser to form a structure with a microchannel;
2. attaching the adhesive tape with the micro-channel structure in a smooth utensil with a proper size;
3. PDMS and curing agent were mixed at 10: 1, stirring for 3 minutes, placing the mixture in a vacuum drying oven for vacuumizing, and taking out the treated PDMS after bubbles generated by vacuumizing disappear;
4. the treated PDMS was poured into the above-mentioned dish, and then a prism was placed in the center of the dish against the surface of the tape. Note that the prism base at this time is parallel or perpendicular to the pipe, and the processed PDMS also has no prism base;
5. placing the dish in a drying box, heating at 50 ℃ for 12 hours, cutting off and peeling the PDMS plate from the dish;
6. and (4) punching an inlet hole, and after the outlet hole is punched, carrying out oxygen plasma treatment on the PDMS plate and the glass slide, and then irreversibly bonding the PDMS plate and the glass slide to obtain the PDMS microfluidic chip.
The signal processing module of this example includes a filter, an amplifier, and an oscilloscope. The detected change of the intensity difference of the P polarized light and the S polarized light is converted into a voltage signal by a balance light detector in the laser detection module, an interference signal is filtered by a filter, the signal is amplified by an amplifier, and finally the signal is acquired by a high-bandwidth oscilloscope. The oscilloscope takes the photoelectric signal received by the photoelectric probe in the excitation module as trigger, and the displayed signal is the photoacoustic signal.
Microfluidic detection system example 2:
the laser excitation module comprises a pulse excitation light source 1, a beam expander 2, a filter 3, a beam splitter 4, a reflector M, an objective 6 and a photoelectric probe. A pulse laser is emitted from a pulse excitation light source 1, is collimated and amplified by a beam expander 2, is filtered by a light filter 3, is split by a beam splitter 4, and one beam of light enters a photoelectric probe 5 to serve as a trigger signal of a subsequent signal processing module. The other beam of light 500 is reflected by the mirror M into the objective 6, focused on the sample in the microfluidic chip microchannel 400, and excites the sample to emit ultrasonic waves.
The laser detection module comprises a continuous laser light source 7, a polarizer 8, an 1/4 wave plate 9, an optical fiber 14, fiber collimating mirrors 13, 15, 16 and 17, a lens L, a polarization beam splitter 11 and a balance light detector 12. The continuous laser light source 7 emits a continuous laser beam, which is converted into linearly polarized light by the polarizer 8 and converted into circularly polarized light by the 1/4 wave plate 9. The circularly polarized light passes through the fiber collimator 13 and is collected by the fiber 13.
When the ultrasonic waves in the water pass to the interface between the prism 10 and the water, the ultrasonic waves cause the refractive index of the water around the interface to change periodically. If a light beam is reflected at the interface, the energy of the P-polarized light and the S-polarized light in the reflected light will undergo nonlinear changes with different responses to the refractive index change of water. When the angle of the incident angle is slightly smaller than the total reflection angle, the P-polarized light and the S-polarized light in the reflected light are most sensitive to the change of the refractive index of water, and the signals of the P-polarized light and the S-polarized light are most different. Based on this principle, this example designs an isosceles prism with a base angle slightly smaller than the total reflection angle, and as shown in fig. 4, a combination lens of fiber collimating lenses 15, 16 and focusing lenses 18, 19 is embedded on both sides of the prism 10, and the lens surface is completely parallel to the sides of the prism 10. When the circularly polarized light in the optical fiber 14 is connected to the combined lens on the side of the prism, the circularly polarized light is firstly collimated by the fiber collimating mirror 15 and then focused by the focusing lens 18, and enters the interface between the bottom of the prism 10 and the water at an incident angle slightly smaller than the total reflection angle. The reflected light passes through the combined lens of the focusing lens 19 and the fiber collimator 16 and is collected again by the optical fiber 14. The optical fiber 14 freely transmits the reflected light to the outside of the prism, and then the reflected light is collimated by the optical fiber collimating mirror 17 and slightly focused by the lens L, and the S polarized light and the P polarized light in the reflected light are separated into two beams by the polarization beam splitter 11 and respectively received by the two probes of the high-bandwidth balanced light detector 12.
The microfluidic chip is formed by packaging a lower glass slide substrate, an upper PDMS plate and a prism of a detection area. Wherein the prism is embedded in the PDMS plate. Wherein, the lower surface of PDMS board is carved with liquid inlet, microchannel, liquid outlet. The manufacturing steps of the microfluidic chip are as follows:
1. selecting adhesive tapes with different thicknesses according to requirements, and then cutting the adhesive tapes by using laser to form a structure with a microchannel;
2. attaching the adhesive tape with the micro-channel structure in a smooth utensil with a proper size;
3. PDMS and curing agent were mixed at 10: 1, stirring for 3 minutes, placing the mixture in a vacuum drying oven for vacuumizing, and taking out the treated PDMS after bubbles generated by vacuumizing disappear;
4. the treated PDMS was poured into the above-mentioned dish, and then a prism was placed in the center of the dish against the surface of the tape. Note that the bottom edge of the prism is parallel or perpendicular to the pipe at this time, and the PDMS after treatment simultaneously sinks past the bottom edge of the prism;
5. placing the dish in a drying box, heating at 50 ℃ for 12 hours, cutting off and peeling the PDMS plate from the dish;
6. and (3) punching an inlet hole, after the outlet hole is punched, carrying out oxygen plasma treatment on the PDMS plate and the glass slide, and then bonding the PDMS plate and the glass slide irreversibly to obtain the PDMS microfluidic chip.
The signal processing module comprises a filter, an amplifier and an oscilloscope. The detected change of the intensity difference of the P polarized light and the S polarized light is converted into a voltage signal by a balance light detector in the laser detection module, an interference signal is filtered by a filter, the signal is amplified by an amplifier, and finally the signal is acquired by a high-bandwidth oscilloscope. The oscilloscope takes the photoelectric signal received by the photoelectric probe in the excitation module as trigger, and the displayed signal is the photoacoustic signal.
Embodiment mode 1:
as shown in fig. 5, in the present embodiment, a 532nm pulse laser is used as the pulse excitation light source 1, a HeNa laser is used as the continuous laser light source 7, a polarizer 8 is used as the polarizer, and a black tape is used as the sample. The black adhesive tape is pasted in the pipeline on the lower bottom surface of the prism in the micro-fluidic chip. The thickness of the channel in the microfluidic chip is about 500 microns. The photoacoustic signal of the black tape in the 500 micron tube displayed in the oscilloscope of the signal processing module is shown in fig. 6.
Embodiment mode 2:
as shown in fig. 7, in the present embodiment, a 532nm pulsed laser is used as the pulsed excitation light source 1, a HeNa laser is used as the continuous laser light source 7, a polarizer 8 is used as the polarizer, and black PS (polystyrene) beads with a particle size of 50 μm are used as the sample. The thickness of the channel in the microfluidic chip is about 800 microns. The oscilloscope of the signal processing module showed photoacoustic signals of black PS beads in the 800 micron pipe as shown in fig. 8.
Through the above embodiments, the present invention has the following innovation points:
1. ultrasonic transducers based on piezoelectric materials typically respond only strongly at their resonant frequency, with a consequent reduction in the response in frequency bands far from the resonant frequency. In photoacoustic detection, light absorbers with different sizes can generate photoacoustic signals with different frequencies and wide bandwidths. Therefore, the use of a bandwidth limited ultrasound probe is often not suitable for samples of different sizes. The full-optical-based photoacoustic detection probe provided by the utility model has wide frequency bandwidth and can detect photoacoustic signals of optical absorbers with different sizes.
2. The sensitivity of conventional piezoelectric transducers decreases as the size of the transducer decreases. This is because the mechanism of action of piezoelectric materials is the internal electrical polarity change of the material in response to external pressure. As the size becomes smaller, the influence of the electrical thermal noise of the material itself on the signal becomes larger. Therefore, the size of the ultrasonic transducer made of piezoelectric material cannot be too small, which makes the photoacoustic microfluidic system based on the ultrasonic transducer difficult to be miniaturized. The photoacoustic microfluidic system based on all-optical detection provided by the utility model breaks through the traditional size limitation, and on the premise of high sensitivity, the whole system is highly integrated, and the size of the system only depends on the size of a prism.
3. In a conventional photoacoustic microfluidic system, a photoacoustic signal emitted by a sample is attenuated by PDMS before reaching an ultrasonic transducer, so that the detected signal is weak. Particularly, the attenuation of the high-frequency photoacoustic signal is more obvious. In the photoacoustic microfluidic system based on all-optical detection provided by the utility model, photoacoustic signals emitted by the sample directly pass through the aqueous medium and are received by the photoacoustic probe. The photoacoustic microfluidic system has higher sensitivity.
In summary, in the photoacoustic microfluidic system provided by the present invention, the laser excitation module emits laser to excite the sample in the flow channel of the microfluidic chip, the detection module receives the photoacoustic signal generated after the target sample is excited, the photoacoustic signal is firstly converted into an intensity difference signal of polarized light and then converted into an electrical signal, and the signal processing module receives and processes the electrical signal to obtain the photoacoustic signal of the target sample. In the detection process, the target sample does not need to be subjected to fluorescence labeling, the detection mode is simple, and the complex problem that the sample in the microfluidic chip needs to be labeled in the prior art is solved. Meanwhile, different from the existing photoacoustic microfluidic system adopting an ultrasonic transducer as a photoacoustic probe, the photoacoustic probe of the photoacoustic microfluidic system provided by the utility model has the advantages of wider detection bandwidth, simpler structure, smaller volume and lower cost, is more suitable for being combined with a microfluidic technology, and has wider application prospect in microfluidic application.
The above-described embodiments are intended to be illustrative, and not restrictive, of the utility model, and all changes that come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein.
Claims (10)
1. A photoacoustic microfluidic detection system, comprising: comprises a laser excitation module, a laser detection module, a micro-fluidic chip and a signal processing module, wherein,
the micro-fluidic chip comprises a substrate, a micro-channel arranged on the substrate, a liquid inlet and a liquid outlet which are communicated with the micro-channel, and a prism arranged above the micro-channel,
the laser excitation module is used for exciting a target sample in the micro-channel below the prism to emit ultrasonic waves,
the laser detection module comprises a polarization beam splitter and a balance light detector, the laser detection module receives photoacoustic signals generated after a target sample is excited, light beams are divided into S polarized light and P polarized light through the polarization beam splitter and then are respectively output to the balance light detector, and the balance light detector is used for converting the change of the intensity difference of the S polarized light and the P polarized light into voltage signals;
the input end of the signal processing module is connected with the output end of the balanced light detector and used for receiving and processing the voltage signal of the balanced light detector to obtain the photoacoustic signal of the target sample.
2. The photoacoustic microfluidic detection system of claim 1, wherein: the laser excitation module comprises a first laser light source, and the first laser light source is pulse laser.
3. The photoacoustic microfluidic detection system of claim 2, wherein: the laser excitation module also comprises a first light path and a photoelectric probe which are arranged at the output end of the first laser light source, the first light path outputs two paths of light beams, one path of light beams is received by the photoelectric probe, the other path of light beams is used for exciting a sample to emit ultrasonic waves,
the signal processing module is also connected with the photoelectric probe and takes the photoelectric signal received by the photoelectric probe as trigger.
4. The photoacoustic microfluidic detection system of claim 3, wherein: the first light path comprises a beam expander, a light filter, a first beam splitter, a first reflector and an objective lens, wherein pulse laser emitted by the first laser light source is collimated and amplified by the beam expander, then is filtered by the light filter, and is split by the first beam splitter, one beam of light enters the photoelectric probe, the other beam of light enters the objective lens after being reflected by the first reflector, and is focused on a target sample in the microfluidic chip, so that the sample is excited to emit ultrasonic waves.
5. The photoacoustic microfluidic detection system of claim 4, wherein: the signal processing module comprises a filter, an amplifier and an oscilloscope, wherein the input end of the filter is connected with the output end of the laser detection module balanced light detector, the output end of the filter is connected with the input end of the amplifier, the output end of the amplifier is connected with the input end of the oscilloscope, and the oscilloscope outputs photoacoustic signals of a target sample.
6. The photoacoustic microfluidic detection system of any one of claims 1 to 5, wherein: the laser detection module comprises a second laser light source, a second light path and a third light path, the second light path is arranged on the incident side of the prism and used for processing the second laser light source, the third light path is arranged on the reflection side of the prism, the output end of the third light path is connected with the input end of the polarization beam splitter, and the second laser light source is a continuous laser light source.
7. The photoacoustic microfluidic detection system of claim 6, wherein: the second light path comprises a polarizer, an 1/4 wave plate, a first lens and a second reflector, continuous laser emitted by the second laser source is changed into linearly polarized light through the polarizer and is changed into circularly polarized light through the 1/4 wave plate, the circularly polarized light is focused through the first lens to be used as detection light, the detection light is incident into the prism from the side surface of the prism at an angle close to a total reflection angle as an incident angle after passing through the second reflector and is focused on the lower bottom surface of the prism,
the third light path comprises a third reflector and a second lens, and reflected light emitted by the lenses is reflected by the third reflector, focused by the second lens and enters the polarization beam splitter.
8. The photoacoustic microfluidic detection system of claim 6, wherein: the second light path comprises a polarizer, an 1/4 wave plate, an optical fiber, a first optical fiber collimating mirror and a second optical fiber collimating mirror which are arranged at two ends of the optical fiber, and a first focusing lens which is arranged at the rear end of the second optical fiber collimating mirror, continuous laser emitted by the second laser source is changed into linearly polarized light through the polarizer and is converted into circularly polarized light through the 1/4 wave plate, the circularly polarized light is collected by the optical fiber through the first optical fiber collimating mirror and is then transmitted to the second optical fiber collimating mirror through the optical fiber, the light emitted by the second optical fiber collimating mirror is focused at the middle part of the detection window through the first focusing lens,
the third light path comprises a second focusing lens, an optical fiber, a third optical fiber collimating lens and a fourth optical fiber collimating lens which are arranged at two ends of the optical fiber, and further comprises a second lens and a polarization beam splitter, reflected light passes through the third optical fiber collimating lens after passing through the second focusing lens, is collected by the optical fiber and is transmitted to the fourth optical fiber collimating lens, is focused by the second lens, and is divided into two beams by the polarization beam splitter according to S polarized light and P polarized light in reflected light, and the two beams are received by two probes of the high-bandwidth balance light detector respectively.
9. The photoacoustic microfluidic detection system of claim 8, wherein: the prism, the second optical fiber collimating lens, the first focusing lens, the second focusing lens and the third optical fiber collimating lens are integrally arranged to be a combined lens, the prism is an isosceles prism with a base angle slightly smaller than a total reflection angle, the second optical fiber collimating lens, the first focusing lens, the second focusing lens and the third optical fiber collimating lens are symmetrically distributed and embedded in two sides of the prism, lens surfaces of the second optical fiber collimating lens and the third optical fiber collimating lens are arranged in parallel with the side surface of the prism, and the first focusing lens converges light beams in the middle of the bottom surface of the prism.
10. The photoacoustic microfluidic detection system of any one of claims 1 to 5, wherein: the micro-fluidic chip comprises a glass slide substrate, a substrate arranged above the glass slide substrate and a prism arranged in a detection area of the substrate, and the micro-channel is arranged on the substrate below the prism.
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| CN114112923A (en) * | 2021-12-07 | 2022-03-01 | 深圳大学 | Photoacoustic microfluidic detection system and detection method |
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