Oral bioimaging device based on quantum entanglement phase

Abstract

The invention belongs to the technical field of quantum and biological imaging, and particularly relates to an oral cavity biological imaging device based on a quantum entanglement phase. According to the invention, energy-time entangled photon pairs are generated by using a continuous laser pumping nonlinear waveguide, and signal photons are separated from idler frequency photons through an optical filter; a to-be-measured oral biological sample is placed in the unbalanced interferometer, two interference curves of different phases are obtained by measuring Franson interference between signal photons and idler frequency photons when the biological sample exists or not, and the entanglement phase difference of the two interference curves is calculated. The position of the sample to be detected is changed through the two-dimensional scanning platform, Franson interference is executed, and entanglement phase differences of different positions are obtained. And combining the phase differences to obtain a quantum phase image of the sample. According to the invention, high-precision imaging of a microstructure can be realized; according to the invention, each component can be from a mature photoelectric device, the device has the advantages of miniaturization, integration, practicability and the like, and a new way is opened up for quantum precision measurement and life science development.

Description

Technical Field

[0001] The invention belongs to the technical field of quantum and biological imaging, and in particular relates to an oral biological imaging device based on quantum entanglement phase. Background Art

[0002] Measurement is a basic means of observing natural phenomena, including length, direction, macro / micro world observation, etc. As a typical measurement device for exploring microstructures, optical microscopes are of great significance in fields such as biology, medicine, and materials science. It can observe tiny structures that are invisible to the naked eye and reveal a whole new microscopic world. However, with the progress of research on the microscopic world, especially when exploring the complexity of cellular and molecular systems, such as oral tissue pathological sections, periodontal ligament cells, etc., traditional optical microscopy has encountered many challenges, such as resolution limitations caused by the 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 because they are colorless or have low contrast, and high-intensity light irradiation may even cause photodamage and photobleaching of biological samples. Therefore, using low-intensity light irradiation to achieve high-quality imaging of transparent samples while maintaining high spatial resolution and high signal-to-noise ratio is still a major challenge in optical microscopy research.

[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, computing, 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 computing, and improve the accuracy of quantum metrology. Therefore, introducing quantum entanglement properties into optical microscopy is a promising way to improve imaging performance. Numerous quantum imaging schemes have been developed based on quantum entanglement / correlation, including quantum ghost imaging, quantum interference imaging, and non-detection photon imaging. However, these schemes mainly involve the temporal correlation characteristics of entangled photon pairs, but not the phase information of entangled photon pairs. Summary of the invention

[0004] In view of the above problems, in order to further improve the performance of transparent oral biological sample imaging, the present invention proposes an oral biological imaging device based on quantum entanglement phase. The present invention is mainly used to solve the problems of existing optical imaging systems in terms of accuracy, signal-to-noise ratio, and in vivo imaging capabilities when imaging transparent biological samples such as oral tissue pathological sections and periodontal ligament cells.

[0005] The present invention uses energy-time entangled photon pairs as light sources, places the oral sample to be tested in one arm of the signal photon interferometer, measures the Franson interference of the energy-time entangled photon pairs with and without the sample to be tested, and statistically records the phase changes in the interference curve. The position of the sample to be tested is changed to measure the phase change values ​​at different locations of the sample, and all phase values ​​are placed in the corresponding locations of the object to construct an image.

[0006] The technical solution adopted by the present invention is:

[0007] An oral bio-imaging device based on quantum entanglement phase, comprising 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;

[0008] Among them, 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 and a second optical filter 7 are 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 are 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 are connected in sequence; an input of the first optical collimator 8 is connected to an output of the first optical filter 6, an input of the second optical collimator 9 is connected to an output of the second optical filter 7, an output of the first single-photon detector 27 and an output of the second single-photon detector 28 are both connected to an input of a coincidence measurement unit 29; a three-dimensional scanning platform 22 is arranged at the second unbalanced interferometer 15 and both have observation ports that match each other; the three-dimensional scanning platform 22 and the coincidence measurement unit 29 are both connected to a 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 is measured when there is no sample to be measured, specifically by continuously changing the phase of the first unbalanced interferometer 10 to obtain the coincidence count values ​​at different phases, and finally the interference curve when there is no sample is obtained by fitting the coincidence count values;

[0011] Then measure the Franson interference curve of the signal photon and the idler photon when there is a sample to be tested. Specifically, place the sample to be tested on the three-dimensional scanning platform 22 and set the position of the sample to be tested. The Franson interference curve of the sample to be tested at the initial position is obtained by adopting the same operation as when there is no sample to be tested. Then, the three-dimensional scanning platform 22 is controlled by the computer 30 to change the position of the sample to be tested. Franson interference is performed when the sample to be tested is at different positions in turn, so as to obtain the entangled phase difference of each measuring point; finally, these entangled phase differences are placed in corresponding positions, so as to realize imaging of the sample to be tested.

[0012] Furthermore, the first unbalanced interferometer 10 includes a first optical beam splitter 13, a first optical reflector 11, a second optical reflector 12 and a second optical beam splitter 14 which are connected in sequence, and the first optical beam splitter 13 and the second optical beam splitter 14 are also connected so that the first unbalanced interferometer 10 forms a ring shape, wherein the first optical beam splitter 13 is connected to the first optical collimator 8, and the second optical beam splitter 14 is connected to the third optical collimator 23; the method for continuously changing the phase of the first unbalanced interferometer 10 is to install the first optical reflector 11 on a piezoelectric ceramic, and continuously change the phase of the first unbalanced interferometer 10 through the piezoelectric ceramic.

[0013] Furthermore, the second unbalanced interferometer 15 includes a third beam splitter 16, a fourth beam splitter 17, a third light reflector 18, a first lens 19, a second lens 20, and a fourth reflector 21, wherein the third beam splitter 16 is respectively connected to the second light collimator 9, the fourth beam splitter 17, and the third light reflector 18, the fourth beam splitter 17 is respectively connected to the fourth light collimator 24 and the fourth reflector 21, the third light reflector 18 is connected to the first lens 19, and the fourth reflector 21 is connected to the second lens 20; the positions of the first lens 19 and the second lens 20 are relatively 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 to further focus the signal photons so as to act on the sample to be measured, and the second lens 20 is used to collect the transmitted signal photons after acting on the sample to be measured.

[0014] Furthermore, the three-dimensional scanning platform 22 has a placement rack for placing the sample to be tested, and the displacement of the sample to be tested is automatically controlled under the control of the computer 30, or manually controlled by the displacement structure. The sample to be tested is a transparent biological tissue slice or a transparent cell.

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

[0016] Furthermore, the continuously 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 light with a wavelength of 1520-1540 nm.

[0017] Furthermore, 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] Furthermore, the nonlinear optical medium 5 is a straight waveguide structure or a waveguide-coupled micro-ring resonant cavity structure;

[0019] Alternatively, the nonlinear optical medium 5 is one of a periodically poled lithium niobate waveguide, a periodically poled potassium titanyl phosphate waveguide, and a periodically poled barium metaborate 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 Fabry-Perot cavities or waveguide-coupled micro-ring resonant cavity structures.

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

[0023] Beneficial effects of the present invention:

[0024] The invention provides an oral bio-imaging device based on quantum entangled phase, in which a biological sample to be tested is placed in an unbalanced interferometer, and the phase change of the entangled photon pair is measured when there is a sample or not, so as to obtain an image of the sample to be tested. Specifically, a quantum entangled photon pair is generated by pumping a nonlinear waveguide with a pump laser, and the signal photon and the idler photon are separated and output selectively by an optical filter; the Franson interference of the signal photon and the idler photon with or without the biological sample is measured by an unbalanced interferometer, a single photon detector and a time-to-digital converter, and the three-dimensional entangled phase with or without the biological sample is obtained by comparing the two interference curves, and the phase change is obtained by subtracting the two; the linear movement of the two-dimensional scanning platform is controlled by a computer to change the position of the oral biological sample to be tested, and the above-mentioned Franson interference is repeated to obtain the entangled phase change values ​​of the sample at different positions; finally, these change values ​​are combined with the points corresponding to the S path of the two-dimensional scanning platform to obtain the final oral bio-image based on entangled phase. The oral biological imaging device and method based on entangled phase proposed in the present invention utilizes an all-fiber integrated device to prepare an entangled light source, thereby increasing the robustness of the imaging device and effectively reducing the volume of the imaging device, with the advantages of miniaturization and integration. The present invention utilizes quantum entangled phase as an imaging carrier, which has high sensitivity and can achieve higher-precision imaging compared to the prior art. At the same time, each component of the present invention can be derived from mature optoelectronic devices, which is conducive to system assembly, preparation and practical development, and is an important basis for promoting the practical application of quantum entangled phase microscopy imaging. BRIEF DESCRIPTION OF THE DRAWINGS

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

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

[0027] Description of reference numerals:

[0028] 1. Continuously tunable pump laser source, 2. Optical amplifier, 3. Adjustable 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 reflector, 12. Second optical reflector, 13. First optical beam splitter, 14. Second optical beam splitter, 15. Second unbalanced interferometer, 16. Third optical beam splitter, 17. Fourth optical beam splitter, 18. Third optical reflector, 19. First lens, 20. Second lens, 21. Fourth reflector, 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 DESCRIPTION

[0029] The technical solution of the present invention is described below with detailed drawings and embodiments.

[0030] Example

[0031] like Figure 1 As shown, the device of this example includes 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;

[0032] Among them, 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 and a second optical filter 7 are 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 are 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 are connected in sequence; an input of the first optical collimator 8 is connected to an output of the first optical filter 6, an input of the second optical collimator 9 is connected to an output of the second optical filter 7, an output of the first single-photon detector 27 and an output of the second single-photon detector 28 are both connected to an input of a coincidence measurement unit 29; a three-dimensional scanning platform 22 is arranged at the second unbalanced interferometer 15 and both have mutually matching observation ports; and the three-dimensional scanning platform 22 and the coincidence measurement unit 29 are both connected to a computer 30.

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

[0034] The optical amplifier 2 and the adjustable optical attenuator 3 are used to adjust the intensity of the continuous pump laser. In this embodiment, the optical amplifier 2 amplifies the intensity of the continuous pump laser. The adjustable optical attenuator 3 adjusts 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 polarization adjustment of the continuous pump laser. By changing the working state of the polarization controller 4, it is made consistent with the input polarization of the nonlinear optical medium 5, so that the output count rate of the photon pairs generated by the nonlinear medium 5 reaches the maximum; the polarization controller 4 used in this example is a fiber polarization controller with a wavelength range of 1260nm-1625nm and an insertion loss of 0.1dB.

[0036] In the nonlinear optical medium 5, under the conditions of satisfying the energy conservation and momentum conservation, the second harmonic generation process and the spontaneous parametric down conversion process occur, and a large-bandwidth declarative quantum light source is generated. The idler photons are filtered out by the first optical filter 6, and the signal photons are filtered out by the second optical filter 7. There is energy-time entanglement between the signal photons and the idler photons. In this embodiment, the nonlinear optical medium 5 adopts a periodically polarized lithium niobate waveguide (PPLN). In the PPLN waveguide, a continuous pump laser with a central wavelength of 1540nm first generates a pulsed pump laser with a central wavelength of 770nm 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 100GHz and a central wavelength of 1549nm. The reflection end of the first optical filter 6 is connected to the input end of the second optical filter 7, and the signal photons with a bandwidth of 100GHz and a central wavelength of 1532nm are selected from its transmission end.

[0037] Fiber collimating lenses 8 and 9 focus and collimate the light transmitted in the optical fiber and couple it into the free space. Fiber collimating lenses 23 and 24 focus the free space light and couple it into the optical fiber. The focal length of the fiber collimating lens is 20 mm.

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

[0039] The third beam splitter 16, the fourth beam splitter 17, the third light reflector 18, the first lens 19, the second lens 20, and the fourth reflector 21 are used to construct a second unbalanced interferometer 15 for signal photons, which is still a Mach-Zehnder interferometer. In this example, 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, on top of which an oral cell sample is placed, and the electrically controlled two-dimensional scanning platform 22 is controlled by a computer 30 to ensure that it can perform an S-shaped linear scan in a hundred nanometer step in the XY plane. This allows researchers to more accurately observe the microstructure of the biological sample being tested, thereby obtaining more properties and characteristics.

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

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

[0043] The coincidence measurement unit 29 is used to record the coincidence counts of incident photons in two independent channels of the single-photon detector, and transmit the data to the computer to obtain the coincidence measurement technology between them. In this example, the ID900 time-to-digital converter is used, and the counting rate of each channel reaches 100Mcps with a resolution of 100ps.

[0044] In completing Figure 1After the quantum entangled phase-based biological imaging device shown in the figure, the Franson interference curve of the signal photon and the idler photon is first measured when the two-dimensional scanning platform does not contain a biological sample. In this embodiment, the light reflector 11 is installed on the piezoelectric ceramic, and the phase of the unbalanced interferometer 10 is continuously changed by the piezoelectric ceramic, so as to obtain the coincidence count values ​​under different phases. Finally, the interference curve without the sample is obtained by fitting the coincidence count values, as shown in FIG. Figure 2 (a) is shown as a solid line; then the oral biological sample to be tested is placed on the two-dimensional scanning platform, and the above operation is repeated to obtain the interference curve when there is a sample, as shown in Figure 2 (a) The dotted line shows the phase difference between the two curves. 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 tested is changed according to the S-shaped scanning route by the two-dimensional scanning platform (such as Figure 2 (b)), thereby focusing the signal photons at different positions of the sample to be tested, performing Franson interference at each position, and obtaining the entangled phase difference of each measurement point; finally, these entangled phase differences are placed in the corresponding positions to achieve imaging of the sample to be tested.

[0045] The present invention relates to an oral biological imaging device and method based on entangled phase, which belongs to the intersection of quantum information and life science. The present invention realizes quantum imaging of biological samples by measuring the change in the entangled phase of entangled photons caused by the biological sample to be tested. The present invention expands the method of quantum imaging, can further improve the accuracy of quantum imaging, can be applied to the field of life science, and also has the advantages of compactness and scalability, which is conducive to the practical and commercial development of quantum information technology.

Claims

1. An oral bio-imaging device based on quantum entangled phase, characterized in that: The invention 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 The single photon detectors (28) are connected in sequence; the input of the first light collimator (8) is connected to the output of the first light filter (6), the input of the second light collimator (9) is connected to the output of the second light filter (7), and the output of the first single photon detector (27) and the output of 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 the two have mutually matching observation ports; the three-dimensional scanning platform (22) and the coincidence measurement unit (29) are both connected to a computer (30); The imaging method of the imaging device is: First, the Franson interference curve of the signal photon and the idler photon is measured when there is no sample to be measured, specifically by continuously changing the phase of the first unbalanced interferometer (10) to obtain coincidence count values ​​at different phases, and finally the interference curve when there is no sample is obtained by fitting the coincidence count values; Then, the Franson interference curve of the signal photon and the idler photon is measured when there is a sample to be tested. Specifically, the sample to be tested is placed on a three-dimensional scanning platform (22) and the position of the sample to be tested is set. The Franson interference curve of the sample to be tested at the initial position is obtained by performing the same operation as when there is no sample to be tested. Then, the three-dimensional scanning platform (22) is controlled by a computer (30) to change the position of the sample to be tested. Franson interference is performed in sequence when the sample to be tested is at different positions, thereby obtaining the entangled phase difference of each measurement point. Finally, these entangled phase differences are placed in corresponding positions, thereby realizing imaging of the sample to be tested.

2. The oral bio-imaging device based on quantum entanglement phase according to claim 1, characterized in that: The first unbalanced interferometer (10) comprises a first optical beam splitter (13), a first optical reflector (11), a second optical reflector (12) and a second optical beam splitter (14) which are connected in sequence, wherein the first optical beam splitter (13) and the second optical beam splitter (14) are also connected so that the first unbalanced interferometer (10) forms a ring shape, wherein the first optical beam splitter (13) is connected to a first optical collimator (8), and the second optical beam splitter (14) is connected to a third optical collimator (23); the method for continuously changing the phase of the first unbalanced interferometer (10) is to install the first optical reflector (11) on a piezoelectric ceramic, and continuously change the phase of the first unbalanced interferometer (10) through the piezoelectric ceramic.

3. The oral bio-imaging device based on quantum entangled phase according to claim 1, characterized in that: The second unbalanced interferometer (15) comprises a third beam splitter (16), a fourth beam splitter (17), a third light reflector (18), a first lens (19), a second lens (20), and a fourth reflector (21), wherein the third beam splitter (16) is connected to the second light collimator (9), the fourth beam splitter (17), and the third light reflector (18) respectively, the fourth beam splitter (17) is connected to the fourth light collimator (24) and the fourth reflector (21) respectively, the third light reflector (18) is connected to the first lens (19), and the fourth reflector (21) is connected to the second lens (20); the first lens (19) and the second lens (20) are arranged relative to each other 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 to further focus the signal photons so as to act on the sample to be measured, and the second lens (20) is used to collect the transmitted signal photons after acting on the sample to be measured.

4. The oral bio-imaging device based on quantum entangled phase according to claim 1, characterized in that: The three-dimensional scanning platform (22) has a placement rack for placing samples to be tested. The displacement of the samples to be tested is controlled automatically under the control of a computer (30) or manually by a displacement structure. The samples to be tested are transparent biological tissue slices or transparent cells.

5. The oral bio-imaging device based on quantum entangled phase according to claim 1, characterized in that: The continuously tunable pump laser source (1) is used to provide continuous and stable pump light for the preparation of a quantum entangled light source; the nonlinear optical medium (5) is used to generate quantum entangled photon pairs according to the pump light; the first optical collimator (8) and the second optical collimator (9) are used to achieve coupling and focusing of optical fiber light transmission to free space, and the third optical collimator (23) and the fourth optical collimator (24) are used to achieve focusing of free space light and coupling it into the optical fiber.

6. The oral bio-imaging device based on quantum entangled phase according to claim 1, characterized in that: The continuously 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 light with a wavelength of 1520-1540 nm.

7. The oral bio-imaging device based on quantum entangled phase according to claim 1, characterized in that: 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 an optical fiber polarization controller.

8. The oral bio-imaging device based on quantum entangled phase according to claim 1, characterized in that: The nonlinear optical medium (5) is a straight waveguide structure or a waveguide-coupled micro-ring resonant cavity structure; Alternatively, the nonlinear optical medium (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 oral bio-imaging device based on quantum entangled phase according to claim 1, characterized in that: 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; Alternatively, the first optical filter (6) and the second optical filter (7) are Fabry-Perot cavities or waveguide-coupled micro-ring resonant cavity structures.

10. The oral bio-imaging device based on quantum entangled phase according to claim 1, characterized in that: The coincidence measurement unit (29) is a time-to-digital converter or a field programmable logic gate array.

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