An oral biological imaging device based on quantum entanglement phase

Abstract

The present application belongs to the technical field of quantum and biological imaging, and particularly relates to an oral biological imaging device based on quantum entanglement phase. The present application utilizes continuous laser pumping nonlinear waveguide to generate energy-time entangled photon pairs, separates signal photons from idler photons through an optical filter; places the oral biological sample to be measured in a non-balanced interferometer, measures the Franson interference between signal photons and idler photons with or without biological samples, obtains two different phase interference curves, and calculates the entanglement phase difference. The position of the sample to be measured is changed through a two-dimensional scanning platform, the Franson interference is performed, and the entanglement phase difference at different positions is obtained. The phase differences are combined to obtain the quantum phase image of the sample. The present application can realize high-precision imaging of microstructures; all components of the present application can come from mature optoelectronic devices, and have the advantages of miniaturization, integration, practicality and the like, and open up a new way for the development of quantum precision measurement and life science.

Description

TECHNICAL FIELD

[0001] The application belongs to the technical field of quantum and biological imaging, and particularly relates to an oral biological imaging device based on quantum entanglement phase. BACKGROUND

[0002] Measurement is a basic means of observing natural phenomena, including length, direction, macro / micro world observation, etc. Optical microscopy, as a typical measurement device for exploring microstructure, has important significance in the fields of biology, medicine and material science. It can observe microstructures that cannot be seen by the naked eye and reveal a new micro world. However, with the progress of research on the micro world, especially in exploring the complexity of cell and molecular systems, such as oral histopathological sections, periodontal membrane cells, etc., traditional optical microscopy technology has encountered many challenges, such as resolution limit caused by diffraction limit, image quality degradation caused by light scattering and absorption, etc. In addition, many pathological sections or cells need to be stained or fluorescently labeled due to their colorless or low contrast, and high-intensity light irradiation can even cause photo-damage and photo-bleaching of biological samples. Therefore, it is still a great challenge for optical microscopy research to achieve high-quality imaging of transparent samples using low-intensity light irradiation while maintaining high spatial resolution and high signal-to-noise ratio.

[0003] Quantum information science (QIS) combines the principles of quantum physics and information science, and has great potential for progress in the fields of communication, computation and precision measurement. Quantum entanglement, as a unique and important resource in QIS, can ensure the security of quantum communication, enhance the parallel processing capability of quantum computation, and improve the accuracy of quantum metrology. Therefore, introducing quantum entanglement characteristics into optical microscopy technology is a promising way to improve imaging performance. Based on quantum entanglement / correlation, a number of quantum imaging schemes have been developed, including quantum ghost imaging, quantum interference imaging and non-probing photon imaging, etc. However, these schemes mainly involve the temporal correlation characteristics of entangled photon pairs, and do not involve the phase information of entangled photon pairs. SUMMARY

[0004] In view of the above problems, in order to further improve the performance of transparent oral biological sample imaging, the present application provides an oral biological imaging device based on quantum entanglement phase. The present application is mainly used to solve the problems of existing optical imaging systems in terms of precision, signal-to-noise ratio, and insufficient ability of live imaging for transparent biological samples such as oral histopathological sections, periodontal membrane cells, etc.

[0005] The present application takes energy-time entangled photon pairs as light sources, places the oral sample to be measured in the signal photon one arm interferometer, respectively measures the Franson interference of the energy-time entangled photon pairs with and without the sample to be measured, and records the phase change of the statistical interference curve.

[0006] The technical scheme adopted by the present application is:

[0007] An oral cavity biological imaging device based on quantum entangled phase, comprising a continuous tunable pump laser source 1, an optical amplifier 2, an adjustable optical attenuator 3, a first polarization controller 4, a nonlinear waveguide 5, a first optical filter 6, a second optical filter 7, a first optical collimator 8, a second optical collimator 9, a first unbalanced interferometer 10, a second unbalanced interferometer 15, a three-dimensional scanning platform 22, a third optical collimator 23, a fourth optical collimator 24, a second polarization controller 25, a third polarization controller 26, a first single-photon detector 27, a second single-photon detector 28, a coincidence measurement unit 29, and a computer 30.

[0008] The continuous tunable pump laser source 1, the optical amplifier 2, the adjustable optical attenuator 3, the first polarization controller 4, the nonlinear waveguide 5, the first optical filter 6, and the second optical filter 7 are connected in sequence; the first optical collimator 8, the first unbalanced interferometer 10, the third optical collimator 23, the second polarization controller 25, and the first single-photon detector 27 are connected in sequence; the second optical collimator 9, the second unbalanced interferometer 15, the fourth optical collimator 24, the third polarization controller 26, and the second single-photon detector 28 are connected in sequence; the input of the first optical collimator 8 is connected to the output of the first optical filter 6, the input of the second optical collimator 9 is connected to the output of the second optical filter 7, and the outputs of the first single-photon detector 27 and the second single-photon detector 28 are both connected to the input of the coincidence measurement unit 29; the three-dimensional scanning platform 22 is arranged at the second unbalanced interferometer 15 and both have matching observation ports; the three-dimensional scanning platform 22 and the coincidence measurement unit 29 are both connected to the computer 30.

[0009] The imaging method of the imaging device is:

[0010] First, the Franson interference curve of the signal photon and the idler photon without the sample to be measured is measured, specifically by continuously changing the phase of the first unbalanced interferometer 10 to obtain the coincidence count value at different phases, and finally fitting the coincidence count value to obtain the interference curve without the sample;

[0011] The Franson interference curve of the signal photons and the idler photons when the sample to be measured is measured is obtained by placing the sample to be measured on the three-dimensional scanning platform 22 and setting the position of the sample to be measured, and then the Franson interference curve of the sample to be measured at the initial position is obtained by using the same operation without the sample to be measured. Then, the three-dimensional scanning platform 22 is controlled by the computer 30 to change the position of the sample to be measured, and the Franson interference is performed in turn when the sample to be measured is at different positions, so as to obtain the entanglement phase difference of each measurement point. Finally, the entanglement phase differences are placed in the corresponding positions, so as to realize the imaging of the sample to be measured.

[0012] Further, the first non-equilibrium interferometer 10 comprises a first optical beam splitter 13, a first optical mirror 11, a second optical mirror 12 and a second optical beam splitter 14 connected in sequence, and the first optical beam splitter 13 and the second optical beam splitter 14 are also connected to form a ring-shaped first non-equilibrium interferometer 10, wherein the first optical beam splitter 13 is connected with the first optical collimator 8, and the second optical beam splitter 14 is connected with the third optical collimator 23; and the method for continuously changing the phase of the first non-equilibrium interferometer 10 is to install the first optical mirror 11 on a piezoelectric ceramic, and continuously change the phase of the first non-equilibrium interferometer 10 through the piezoelectric ceramic.

[0013] Further, the second non-equilibrium interferometer 15 comprises a third optical beam splitter 16, a fourth optical beam splitter 17, a third optical mirror 18, a first lens 19, a second lens 20 and a fourth mirror 21, wherein the third optical beam splitter 16 is connected with the second optical collimator 9, the fourth optical beam splitter 17 and the third optical mirror 18 respectively, the fourth optical beam splitter 17 is connected with the fourth optical collimator 24 and the fourth mirror 21 respectively, the third optical mirror 18 is connected with the first lens 19, and the fourth mirror 21 is connected with the second lens 20; the first lens 19 and the second lens 20 are oppositely arranged and have a spacing, the sample to be measured is placed in the spacing by the three-dimensional scanning platform 22 for observation, and the first lens 19 is used for further focusing of the signal photons to act on the sample to be measured, and the second lens 20 is used for collecting the transmitted signal photons after acting on the sample to be measured.

[0014] Further, the three-dimensional scanning platform 22 has a placing rack for placing the sample to be measured, and the control mode of the displacement of the sample to be measured is automatic control under the control of the computer 30, or manual control by a displacement structure, and the sample to be measured is a transparent biological tissue slice or a transparent cell.

[0015] Further, the continuous tunable pump laser source 1 is used to provide continuous and stable pump light for the preparation of quantum entangled light source; the nonlinear waveguide 5 is used to generate quantum entangled photon pairs according to the pump light; the first light collimator 8 and the second light collimator 9 are used to realize the coupling and focusing collimation of optical fiber to free space, and the third light collimator 23 and the fourth light collimator 24 are used to realize the focusing and coupling of free space light into optical fiber.

[0016] Further, the continuous tunable pump laser source 1 is one of a solid laser, a gas laser, a semiconductor laser or a dye laser, and is used to generate continuous laser with a wavelength of 1520-1540 nm.

[0017] Further, the first polarization controller 4, the second polarization controller 25 and the third polarization controller 26 are one of a flat plate polarization controller, a cubic polarization controller or a fiber polarization controller.

[0018] Further, the nonlinear waveguide 5 is a straight waveguide structure or a waveguide coupled micro-ring resonant cavity structure.

[0019] Alternatively, the nonlinear waveguide 5 is one of a periodically poled lithium niobate waveguide, a periodically poled potassium titanyl phosphate waveguide and a periodically poled barium borate waveguide.

[0020] Further, the first optical filter 6 and the second optical filter 7 are one of an arrayed waveguide grating, a dense wavelength division multiplexer or an adjustable bandpass filter.

[0021] Alternatively, the first optical filter 6 and the second optical filter 7 are a Fabry-Perot cavity or a waveguide coupled micro-ring resonant cavity structure.

[0022] Further, the coincidence measurement unit 29 is a time-to-digital converter or a field programmable gate array.

[0023] The beneficial effects of the present application are as follows:

[0024] The application provides an oral cavity biological imaging device based on quantum entanglement phase, which places a biological sample to be measured in a non-equilibrium interferometer, measures the phase change of an entangled photon pair when the sample is present or not, and thus obtains an image of the sample to be measured. Specifically, quantum entangled photons are generated by pumping a nonlinear waveguide with a pump laser, signal photons and idler photons are separated by an optical filter and selected for output; the Franson interference of the signal photons and the idler photons when the biological sample is present or not is measured by a non-equilibrium interferometer, a single-photon detector and a time-to-digital converter; the three-dimensional entanglement phase when the biological sample is present or not is obtained by comparing two interference curves, and the phase change is obtained by subtracting the two; the position of the oral cavity biological sample to be measured is changed by linearly moving a two-dimensional scanning platform controlled by a computer, and the above Franson interference is repeated to obtain the entanglement phase change value at different positions of the sample; finally, the change values are combined with the points corresponding to the S path of the two-dimensional scanning platform to obtain the final oral cavity biological image based on the entanglement phase. The oral cavity biological imaging device and method based on the entanglement phase proposed by the application use all-fiber integrated devices to prepare an entangled light source, increase the robustness of the imaging device, effectively reduce the volume of the imaging device, and have the advantages of miniaturization and integration; the application uses quantum entanglement phase as an imaging carrier, has high sensitivity, and can realize higher precision imaging compared with the prior art; meanwhile, the components of the application can all come from mature optoelectronic devices, which is conducive to the system assembly, preparation and practical development, and is an important basis for promoting the practicality of quantum entanglement phase-based microscopic imaging. BRIEF DESCRIPTION OF DRAWINGS

[0025] Figure 1 It is a structural schematic diagram of the application.

[0026] Figure 2 It is a linear scanning schematic diagram in the embodiment and a Franson interference curve schematic diagram measured when a biological sample is present or not at one point.

[0027] BRIEF DESCRIPTION OF DRAWINGS:

[0028] 1. Continuously tunable pumped laser source; 2. Optical amplifier; 3. Tunable optical attenuator; 4. First polarization controller; 5. Nonlinear waveguide; 6. First optical filter; 7. Second optical filter; 8. First optical collimator; 9. Second optical collimator; 10. First unbalanced interferometer; 11. First optical mirror; 12. Second optical mirror; 13. First optical beamsplitter; 14. Second optical beamsplitter; 15. Second unbalanced interferometer; 16. Third optical beamsplitter; 17. Fourth optical beamsplitter; 18. Third optical mirror; 19. First lens; 20. Second lens; 21. Fourth mirror; 22. Two-dimensional scanning platform; 23. Third optical collimator; 24. Fourth optical collimator; 25. Second polarization controller; 26. Third polarization controller; 27. First single-photon detector; 28. Second single-photon detector; 29. ​​Coincidence measurement unit; 30. Computer. Detailed Implementation

[0029] The technical solution of the present invention is described in detail below with reference to the accompanying drawings and embodiments.

[0030] Example

[0031] like Figure 1 As shown, the device in this example includes a continuously tunable pumped laser source 1, an optical amplifier 2, a tunable optical attenuator 3, a first polarization controller 4, a nonlinear waveguide 5, a first optical filter 6, a second optical filter 7, a first optical collimator 8, a second optical collimator 9, a first unbalanced interferometer 10, a second unbalanced interferometer 15, a three-dimensional scanning platform 22, a third optical collimator 23, a fourth optical collimator 24, a second polarization controller 25, a third polarization controller 26, a first single-photon detector 27, a second single-photon detector 28, a coincidence measurement unit 29, and a computer 30.

[0032] The system comprises a continuously tunable pump laser source 1, an optical amplifier 2, a tunable optical attenuator 3, a first polarization controller 4, a nonlinear waveguide 5, a first optical filter 6, and a second optical filter 7 connected in sequence; a first optical collimator 8, a first unbalanced interferometer 10, a third optical collimator 23, a second polarization controller 25, and a first single-photon detector 27 connected in sequence; a second optical collimator 9, a second unbalanced interferometer 15, a fourth optical collimator 24, a third polarization controller 26, and a second single-photon detector 28 connected in sequence; the input of the first optical collimator 8 is connected to the output of the first optical filter 6, the input of the second optical collimator 9 is connected to the output of the second optical filter 7, and the outputs of the first single-photon detector 27 and the second single-photon detector 28 are both connected to the input of the coincidence measurement unit 29; a three-dimensional scanning platform 22 is located at the second unbalanced interferometer 15, and both have mutually matched observation ports; both the three-dimensional scanning platform 22 and the coincidence measurement unit 29 are connected to the computer 30.

[0033] In this example, the continuous tunable pump laser source 1 is a Toptica DLC CTL continuous laser, which is used to output continuous narrow linewidth continuous pump laser, the center wavelength is 1540 nm, the linewidth is about 10 kHz, and the power is about 1 mW;

[0034] The optical amplifier 2 and the adjustable optical attenuator 3 are used to realize the adjustment of the intensity of the continuous pump laser; in this embodiment, the optical amplifier 2 realizes the amplification of the intensity of the continuous pump laser; the adjustable optical attenuator 3 realizes the regulation of the intensity of the continuous pump laser input into the optical amplifier 2, and the average optical power is 3 mW; the optical amplifier 2 adopts an erbium-doped fiber amplifier, and the adjustable optical attenuator 3 is a mechanical fiber optical attenuator.

[0035] The first polarization controller 4 realizes the polarization adjustment of the continuous pump laser, and by changing the working state of the polarization controller 4, the input polarization of the nonlinear waveguide 5 is kept consistent, so that the output count rate of the photon pair generated by the nonlinear medium 5 reaches the maximum; the polarization controller 4 used in this example is a fiber polarization controller, and the wavelength range is 1260 nm-1625 nm, and the insertion loss is 0.1 dB.

[0036] In the nonlinear waveguide 5, under the condition of satisfying the energy conservation and momentum conservation, the second harmonic generation process and the spontaneous parametric down-conversion process occur, a broadband heralded quantum light source is generated, the idler photons are filtered out through the first optical filter 6, and the signal photons are filtered out through the second optical filter 7, and there is energy-time entanglement between the signal photons and the idler photons. In this embodiment, the nonlinear waveguide 5 adopts a periodical polarization lithium niobate waveguide (PPLN), in the PPLN waveguide, the continuous pump laser with a center wavelength of 1540 nm first generates pulsed pump laser with a center wavelength of 770 nm through the second harmonic generation process, and then generates broadband entangled photon pairs through the spontaneous parametric down-conversion process, the transmission end of the first optical filter 6 selects idler photons with a bandwidth of 100 GHz and a center wavelength of 1549 nm, and the reflection end of the first optical filter 6 is connected to the input end of the second optical filter 7, and the transmission end thereof selects signal photons with a bandwidth of 100 GHz and a center wavelength of 1532 nm.

[0037] The fiber collimating lenses 8 and 9 realize the focusing and collimation of the light transmitted in the optical fiber and couple it into the free space, and the fiber collimating lenses 23 and 24 realize the focusing and coupling of the free space light into the optical fiber, and the focal length of the fiber collimating lenses is 20 mm.

[0038] The first light mirror 11, the second light mirror 12, the first light beam splitter 13 and the second light beam splitter 14 are used to build the first unbalanced interferometer 10 for the idler photons, which is a Mach-Zehnder interferometer. In this embodiment, the first light mirror 11 is controlled by a piezoelectric ceramic controller to precisely control the phase of the interferometer. The light splitting ratio of the beam splitters 13 and 14 is 50:50.

[0039] The third light beam splitter 16, the fourth light beam splitter 17, the third light mirror 18, the first lens 19, the second lens 20 and the fourth mirror 21 are used to build the second unbalanced interferometer 15 for the signal photons, which is also a Mach-Zehnder interferometer. In this embodiment, the light splitting ratio of the beam splitters 16 and 17 is 50:50, and the focal length of the lenses 19 and 20 is 15 mm.

[0040] The two-dimensional scanning platform 22 is an electrically controlled scanning platform. The oral cell sample is placed on the top of the scanning platform. The electrically controlled two-dimensional scanning platform 22 is controlled by the computer 30 to ensure that it can perform S-shaped linear scanning in the X-Y plane with a step of hundreds of nanometers. This allows researchers to more accurately observe the microstructure of the biological sample under test and obtain more properties and characteristics.

[0041] The second polarization controller 25 and the third polarization controller 26 are used to adjust the polarization of the idler photons and the signal photons to ensure that the polarization direction entering the single-photon detector is consistent. The polarization controllers 25 and 26 are fiber polarization controllers with a wavelength range of 1260 nm-1625 nm and an insertion loss of 0.1 dB.

[0042] The first single-photon detector 27 and the second single-photon detector 28 are used to detect the idler photons and the signal photons, respectively, to convert the single-photon optical signal into an electrical pulse signal. The single-photon detectors include photomultiplier tube single-photon detectors, avalanche diode single-photon detectors, superconducting nanowire single-photon detectors, etc. In this embodiment, a superconducting nanowire single-photon detector is used. The detection efficiency of the C-band optical photons can reach 80%, the dark count is less than 50 Hz, and the time jitter is less than 20 ps.

[0043] The coincidence measurement unit 29 is used to record the coincidence count of the incident photons of the two independent channels of the single-photon detectors and transmit the data to the computer. The coincidence measurement technology between them is obtained by the computer. In this embodiment, an ID900 time-to-digital converter is used. The count rate of each channel reaches 100 Mcps, and the resolution is 100 ps.

[0044] After the above steps are completed, the computer 30 is used to analyze the data of the two channels of the single-photon detectors to obtain the correlation between the two channels. Figure 1The shown quantum entanglement phase-based biological imaging device first measures the Franson interference curve of the signal photon and the idler photon when the two-dimensional scanning platform does not contain a biological sample, in this embodiment, the optical mirror 11 is installed on the piezoelectric ceramic, the phase of the unbalanced interferometer 10 is continuously changed through the piezoelectric ceramic, and then the coincidence count values under different phases are obtained, finally the interference curve without a sample is obtained by fitting the coincidence count values, as shown in Figure 2 (a) solid line; then the biological sample to be measured is placed on the two-dimensional scanning platform, the above operation is repeated, and the interference curve with the sample is obtained, as shown in Figure 2 (a) dotted line. The phase difference between the two curves is caused by the biological sample, so the phase can reflect the characteristic properties of the cell; then the position of the biological sample to be measured is changed by the two-dimensional scanning platform according to the S-shaped scanning route (as shown in Figure 2 (b)), so as to focus the signal photon on different positions of the sample to be measured, and perform Franson interference at each position to obtain the entanglement phase difference of each measurement point; finally, the entanglement phase differences are placed in the corresponding positions, so as to realize the imaging of the sample to be measured.

[0045] The present application relates to a kind of based on entanglement phase oral biological imaging device and method, belong to the cross field of quantum information and life science.The present application realizes the quantum imaging of biological sample by measuring the change of entangled photon pair entanglement phase of biological sample to be measured.The present application expands the method of quantum imaging, can further improve the accuracy of quantum imaging, can be applied to life science field, in addition, also have compact and scalable advantages, is conducive to the development of quantum information technology to practical and commercialization.

Claims

1. An oral bioimaging device based on quantum entanglement phase, characterized in that, The imaging device comprises a continuously tunable pump laser source (1), an optical amplifier (2), an adjustable optical attenuator (3), a first polarization controller (4), a nonlinear waveguide (5), a first optical filter (6), a second optical filter (7), a first optical collimator (8), a second optical collimator (9), a first unbalanced interferometer (10), a second unbalanced interferometer (15), a three-dimensional scanning platform (22), a third optical collimator (23), a fourth optical collimator (24), a second polarization controller (25), a third polarization controller (26), a first single-photon detector (27), a second single-photon detector (28), a coincidence measurement unit (29), and a computer (30). The continuously tunable pump laser source (1), the optical amplifier (2), the adjustable optical attenuator (3), the first polarization controller (4), the nonlinear waveguide (5), the first optical filter (6), and the second optical filter (7) are connected in sequence; the first optical collimator (8), the first unbalanced interferometer (10), the third optical collimator (23), the second polarization controller (25), and the first single-photon detector (27) are connected in sequence; the second optical collimator (9), the second unbalanced interferometer (15), the fourth optical collimator (24), the third polarization controller (26), and the second single-photon detector (28) are connected in sequence; the input of the first optical collimator (8) is connected to the output of the first optical filter (6), the input of the second optical collimator (9) is connected to the output of the second optical filter (7), and the outputs of the first single-photon detector (27) and the second single-photon detector (28) are both connected to the input of the coincidence measurement unit (29); the three-dimensional scanning platform (22) is arranged at the second unbalanced interferometer (15) and both have matching observation ports; the three-dimensional scanning platform (22) and the coincidence measurement unit (29) are both connected to the computer (30). The imaging method of the imaging device is as follows: First, the Franson interference curve of the signal photons and the idler photons without the sample is measured, specifically, the phase of the first unbalanced interferometer (10) is continuously changed to obtain the coincidence count value at different phases, and finally the interference curve without the sample is fitted by the coincidence count value; Then, the Franson interference curve of the signal photons and the idler photons with the sample is measured, specifically, the sample is placed on the three-dimensional scanning platform (22) and the position of the sample is set, the Franson interference curve at the initial position of the sample is obtained by using the same operation without the sample, then the three-dimensional scanning platform (22) is controlled by the computer (30) to change the position of the sample, and the Franson interference is performed at different positions of the sample to obtain the entanglement phase difference of each measurement point; finally, the entanglement phase differences are placed in the corresponding positions to realize the imaging of the sample.

2. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The first non-equilibrium interferometer (10) comprises a first optical beam splitter (13), a first optical mirror (11), a second optical mirror (12) and a second optical beam splitter (14) connected in sequence, and the first optical beam splitter (13) and the second optical beam splitter (14) are also connected so that the first non-equilibrium interferometer (10) forms a ring, wherein the first optical beam splitter (13) is connected with the first optical collimator (8), and the second optical beam splitter (14) is connected with the third optical collimator (23); and the method for continuously changing the phase of the first non-equilibrium interferometer (10) is that the first optical mirror (11) is installed on a piezoelectric ceramic, and the phase of the first non-equilibrium interferometer (10) is continuously changed through the piezoelectric ceramic.

3. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The second non-equilibrium interferometer (15) comprises a third optical beam splitter (16), a fourth optical beam splitter (17), a third optical mirror (18), a first lens (19), a second lens (20) and a fourth mirror (21), wherein the third optical beam splitter (16) is connected with the second optical collimator (9), the fourth optical beam splitter (17) and the third optical mirror (18) respectively, the fourth optical beam splitter (17) is connected with the fourth optical collimator (24) and the fourth mirror (21) respectively, the third optical mirror (18) is connected with the first lens (19), and the fourth mirror (21) is connected with the second lens (20); the first lens (19) and the second lens (20) are oppositely arranged and have a spacing, the sample to be measured is placed in the spacing by the three-dimensional scanning platform (22) for observation, and the first lens (19) is used for further focusing of the signal photons so as to act on the sample to be measured, and the second lens (20) is used for collecting the transmitted signal photons after acting on the sample to be measured.

4. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The three-dimensional scanning platform (22) has a placing rack for placing the sample to be measured, and the control mode of the displacement of the sample to be measured is automatic control under the control of a computer (30) or manual control by a displacement structure, and the sample to be measured is a transparent biological tissue section or a transparent cell.

5. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The continuous tunable pump laser source (1) is used for providing continuous and stable pump light for preparation of a quantum entangled light source; the nonlinear waveguide (5) is used for generating a pair of quantum entangled photons according to the pump light; the first optical collimator (8) and the second optical collimator (9) are used for realizing coupling and focusing collimation of optical fiber light to free space; and the third optical collimator (23) and the fourth optical collimator (24) are used for realizing focusing and coupling of free space light into an optical fiber.

6. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The continuous tunable pump laser source (1) is one of a solid-state laser, a gas laser, a semiconductor laser or a dye laser, and is used for generating continuous laser with a wavelength of 1520-1540 nm.

7. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The first polarization controller (4), the second polarization controller (25) and the third polarization controller (26) are one of a flat plate polarization controller, a cubic polarization controller or a fiber polarization controller.

8. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The nonlinear waveguide (5) is a straight waveguide structure or a waveguide-coupled micro-ring resonant cavity structure. Or, the nonlinear waveguide (5) is one of a periodically poled lithium niobate waveguide, a periodically poled potassium titanyl phosphate waveguide, and a periodically poled barium metaborate waveguide.

9. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The first optical filter (6) and the second optical filter (7) are one of an arrayed waveguide grating, a dense wavelength division multiplexer, or an adjustable bandpass filter. Or, the first optical filter (6) and the second optical filter (7) are a Fabry-Perot cavity or a waveguide-coupled micro-ring resonant cavity structure.

10. The quantum entanglement phase based oral bioimaging device according to claim 1, wherein, The coincidence measurement unit (29) is a time-to-digital converter or a field programmable gate array.

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