CN113670854A - Differential interference contrast microscopic endoscopic imaging system and endoscopic imaging method - Google Patents
Differential interference contrast microscopic endoscopic imaging system and endoscopic imaging method Download PDFInfo
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Abstract
The invention discloses a differential interference contrast microscopic endoscopic imaging system and an endoscopic imaging method. The invention is characterized in that the contrast of the observed object is enhanced, the technology utilizes a differential interference prism to generate ordinary light (o light) and extraordinary light (e light), because the optical path difference of the two beams of coherent light is changed after passing through the object and the two beams of coherent light interfere on an image surface, the tiny change of the surface height of the sample is expressed by strong light intensity change on an interference background, a relief feeling is formed, and the microscopic outline of the surface of the sample can be reflected vividly. The differential interference microscopy can realize the nanoscale phase resolution on the surface of the sample, observe the microstructure on the surface of the sample and help doctors to judge the focus characteristics through the surface fluctuation characteristics of the observed sample to make diagnosis.
Description
Technical Field
The invention relates to the technical field of optical microscopic endoscopic imaging, in particular to a differential interference contrast microscopic endoscopic imaging system and an endoscopic imaging method.
Background
The endoscope is an integrated endoscopic imaging instrument which integrates various technologies such as optics, precision machinery, electronic circuits, software, algorithms and the like. An endoscope generally comprises a lens body, an illumination system, an operation insertion part, a host system and the like. Endoscopes can be classified into medical endoscopes and industrial endoscopes according to different use scenes. The medical endoscope enters the human body through a natural pore passage or a percutaneous puncture channel of the human body to observe the pathological changes of relevant parts and assist doctors in making pathological changes or taking focus biopsy for pathological diagnosis. Meanwhile, part of the endoscope can be integrated with a micro surgical robot to timely treat pathological tissues or implant artificial products with treatment effects. The endoscope in industry is mainly used for detecting the interiors of pipelines, instruments and equipment which cannot be reached by human eyes, and mainly for detecting whether cracks, white spots, sand holes, air holes, slag inclusions and the like exist on the surface of a welding line of the pipeline. In comparison, due to the special use environment of the human body, the medical endoscope has higher requirements on the imaging performance, stability and safety of the system.
However, in the prior art, a differential interference microscopy technology and an endoscope technology are not combined for accurate diagnosis, and the prior imaging technology is difficult to provide a profile image with richer sample surface detail information, so that lesion tissue diagnosis is not accurate, and industrial detection ultra-fine surface profile cannot be accurately observed.
Therefore, by combining the differential interference microscopy technology with the traditional optical and electronic endoscope technology, an endoscope with the differential interference contrast microscopy capability is developed, which is expected to provide doctors with more abundant profile images of sample surface detail information and provide doctors with more accurate information for diagnosing pathological tissues of patients. In the field of industrial endoscopes, such a device can also be used for precise industrial detection, and provides possibility for ultra-fine surface contour observation.
Disclosure of Invention
The invention aims to provide a differential interference contrast microscopic endoscopic imaging system and an endoscopic imaging method, which solve the problems that in the prior art, a more abundant profile image of sample surface detail information is difficult to provide, lesion tissue diagnosis is not accurate, and industrial detection ultra-fine surface profile cannot be accurately observed.
The invention provides a differential interference contrast microscopic endoscopic imaging system, which comprises:
an illumination light source for generating excitation light;
a light guide fiber for guiding the excitation light;
the illumination light path module is used for modulating and shaping the excitation light transmitted by the optical fiber and irradiating the surface of the observed sample, wherein the illumination light path module comprises a collimation polarization module, a first differential interference prism and an illumination objective lens which are sequentially arranged from top to bottom;
the imaging receiving module is used for analyzing and imaging the scattered light returned from the surface of the observed sample, and comprises an imaging objective lens, a second differential interference prism, a second 1/4 wave plate, a polarization analyzer, a cylindrical mirror and an imaging detector which are sequentially arranged from bottom to top;
and the cable is used for conducting the electric signal of the imaging receiving module and is connected with an external control module.
Further, when the optical fiber is a polymer fiber or a quartz optical fiber, the collimating and polarizing module comprises a lens assembly, a polarizer and a first 1/4 wave plate which are sequentially arranged from top to bottom; when the optical fiber is a polarization maintaining optical fiber, the collimation polarization module comprises a lens component and a first 1/4 wave plate which are sequentially arranged from top to bottom.
Further, the interference surface of the first differential interference prism coincides with the back focal surface of the illumination objective lens, and the interference surface of the second differential interference prism coincides with the interference surface of the imaging objective lens.
Further, the crystal axis direction of the polarizer or the light source polarization direction of the polarization maintaining fiber is perpendicular to the crystal axis direction of the analyzer, the crystal axis direction of the first 1/4 wave plate is located at 45 ° clockwise from the crystal axis direction of the polarizer, the crystal axis direction of the first differential interference prism, the crystal axis direction of the second differential interference prism and the crystal axis direction of the second 1/4 wave plate are both located at 45 ° counterclockwise from the crystal axis direction of the polarizer.
Further, the illumination light path module and the imaging receiving module are positioned on the same side of the observed sample and integrated in the endoscope probe.
Further, the illumination light source is selected from one of an LED (light emitting diode) light source, an LD (laser diode) light source or a polarized light source; the imaging detector is selected from a COMS (complementary metal oxide semiconductor) detector or a CCD (charge coupled device) detector; the first and second differential interference prisms are selected from Wollaston prisms or Nomarski prisms.
The invention also provides a differential interference contrast microscopy endoscopic imaging method, which comprises the following steps:
s1: providing an illumination source, coupling light from the illumination source into an optical fiber;
s2: through the connection of the optical fiber and the illumination optical path module, the excitation light conducted by the optical fiber is divided into two ordinary rays (o light) and extraordinary rays (e light) which can interfere with each other through the illumination optical path module and irradiates the surface of the observed sample, and the surface of the observed sample forms a returned scattered light beam of the illumination optical path;
s3: carrying out polarization analysis and focusing imaging on the scattered light beam of the illumination light path returned by the surface of the observed sample through an imaging receiving module;
s4: and the electric signal formed by the imaging receiving module is connected with an external control module through a cable.
Further, the step S2 includes the following sub-steps:
s21: the exciting light transmitted by the optical fiber is modulated and shaped by the collimation polarization module to form a circularly polarized light beam of an illumination light path;
s22: the circular polarized light beam of the illumination optical path is divided into two ordinary rays (o rays) and extraordinary rays (e rays) which can interfere with each other through a first differential interference prism;
s23: the ordinary light (o light) and the extraordinary light (e light) are irradiated to the surface of the observed sample through the illumination objective lens, and the surface of the observed sample forms a returned illumination optical path scattered light beam.
Further, the step S21 includes the following sub-steps:
if the optical fiber is a polymer fiber or a quartz optical fiber, the transmitted excitation light is collimated by the lens component to form a parallel light beam of an illumination light path; the parallel light beams of the illumination light path form illumination light path polarized light beams through a polarizer; the illumination light path polarized light beam passes through a first 1/4 wave plate to form an illumination light path circularly polarized light beam;
if the optical fiber is a polarization maintaining optical fiber, the transmitted excitation light is a linearly polarized light beam, and the linearly polarized light beam is collimated by the lens component to form a polarized light beam of an illumination light path; the illumination light path polarized light beam passes through a first 1/4 wave plate to form an illumination light path circularly polarized light beam.
Further, the step S3 includes the following sub-steps:
s31: the scattered light beam of the illumination light path returned by the surface of the observed sample is received by the imaging objective lens, and the scattered light beam of the illumination light path is collimated into an imaging receiving parallel light beam;
s32: the imaging receiving parallel light beam is recombined into an imaging receiving circular polarized light beam by a second differential interference prism;
s33: the imaging receiving circularly polarized light beam passes through a second 1/4 wave plate to form an imaging receiving linearly polarized light beam;
s34: the imaging receiving linear polarized light beam only retains the imaging receiving linear polarized light beam carrying the object characteristic information through the analyzer, and is focused and imaged on the imaging detector through the cylindrical lens.
The invention has the beneficial effects that: in the invention, the differential interference microscopy is a polarized light interference technology, which is characterized in that the contrast of an observed object is enhanced, the technology utilizes a differential interference prism to generate ordinary light (o light) and extraordinary light (e light), because the two beams of coherent light change the optical path difference after passing through the object and interfere on an image surface, the tiny change of the surface height of a sample is expressed by strong light intensity change on an interference background, a relief feeling is formed, and the microscopic outline of the surface of the sample can be visually reflected. The differential interference microscopy can realize the nanoscale phase resolution on the surface of the sample, observe the microstructure on the surface of the sample and help doctors to judge the focus characteristics through the surface fluctuation characteristics of the observed sample to make diagnosis.
Drawings
FIG. 1 is a schematic view of the overall structure of the present invention;
FIG. 2 is a schematic structural diagram of an imaging receiving module according to the present invention;
fig. 3 is a schematic structural diagram of an illumination light path module according to embodiment 1 of the present invention;
FIG. 4 is a schematic structural view of example 1 of the present invention in the crystal axis direction;
fig. 5 is a schematic structural diagram of an illumination light path module in embodiment 2 of the present invention;
FIG. 6 is a schematic structural view in the crystal axis direction in example 2 of the present invention;
FIG. 7 shows cells obtained by differential interference method in example 1 of the present invention;
FIG. 8 shows a cell photographed by a general imaging method.
Description of the reference numerals
101-illumination light source, 102-optical fiber, 103-illumination light path module, 104-observed sample, 105-imaging receiving module, 106-cable, 201-lens assembly, 202-polarizer, 203-first 1/4 wave plate, 204-first differential interference prism, 205-illumination objective lens, 206-imaging objective lens, 207-second differential interference prism, 208-second 1/4 wave plate, 209-analyzer, 210-cylindrical lens, 211-imaging detector and 20-collimation polarization module.
Detailed Description
The following description of at least one exemplary embodiment is merely illustrative in nature and is in no way intended to limit the invention, its application, or uses. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
Referring to fig. 1-6, a differential interference contrast microscopy endoscopic imaging system includes:
an illumination light source 101 for generating excitation light;
an optical fiber 102 for conducting excitation light;
an illumination light path module 103, configured to shape and illuminate the excitation light transmitted by the optical fiber 102 on the surface of the observed sample 104, where the illumination light path module 103 includes a collimation polarization module 20, a first differential interference prism 204, and an illumination objective 205, which are sequentially arranged from top to bottom;
the imaging receiving module 105 is configured to perform analytic imaging on the scattered light returned from the surface of the observed sample 104, and the imaging receiving module 105 includes an imaging objective 206, a second differential interference prism 207, a second 1/4 wave plate 208, an analyzer 209, a tube lens 210, and an imaging detector 211, which are sequentially arranged from bottom to top;
and a cable 106 for conducting the electrical signal of the imaging receiving module 105 to be connected with an external control module.
Further, when the optical fiber 102 is a polymer fiber or a quartz optical fiber, the collimating and polarizing module 20 includes, from top to bottom, a lens assembly 201, a polarizer 202, and a first 1/4 wave plate 203; when the optical fiber 102 is a polarization maintaining fiber, the collimating and polarizing module 20 includes a lens assembly 201 and a first 1/4 wave plate 203, which are sequentially arranged from top to bottom.
Further, the interference surface of the first differential interference prism 204 coincides with the back focal surface of the illumination objective 205, and the interference surface of the second differential interference prism 207 coincides with the interference surface of the imaging objective 206.
Further, the crystal axis direction of the polarizer 202 or the light source polarization direction of the polarization maintaining fiber is perpendicular to the crystal axis direction of the analyzer 209, the crystal axis direction of the first 1/4 wave plate 203 is located at 45 ° clockwise from the crystal axis direction of the polarizer 202, the crystal axis direction of the first differential interference prism 204, the crystal axis direction of the second differential interference prism 207, and the crystal axis direction of the second 1/4 wave plate 208 are both located at 45 ° counterclockwise from the crystal axis direction of the polarizer 202.
Further, the illumination light path module 103 and the imaging receiving module 105 are located on the same side of the observed sample 104 and integrated in the endoscope probe.
Further, the illumination light source 101 is selected from one of an LED (light emitting diode) light source, an LD (laser diode) light source, or a polarized light source; the imaging detector 211 is selected from a cmos (complementary metal oxide semiconductor) detector or a CCD (charge coupled device) detector; the first and second differential interference prisms 204, 207 are selected from Wollaston prisms or nomastki prisms.
The invention also provides a differential interference contrast microscopy endoscopic imaging method, which comprises the following steps:
s1: providing an illumination light source 101, coupling light from the illumination light source 101 into an optical fiber 102;
s2: through the connection of the optical fiber 102 and the illumination optical path module 103, the excitation light conducted by the optical fiber 102 is split into two ordinary rays (o light) and extraordinary rays (e light) which can interfere with each other by the illumination optical path module 103 and is irradiated to the surface of the observed sample 104, and the surface of the observed sample 104 forms a returned scattered light beam of the illumination optical path;
s21: the excitation light conducted by the optical fiber 102 is modulated and shaped by the collimating and polarizing module 20 to form a circularly polarized light beam of an illumination light path;
if the optical fiber 102 is a polymer fiber or a quartz optical fiber, the transmitted excitation light is collimated by the lens assembly 201 to form a parallel light beam of an illumination light path; the parallel light beams of the illumination light path form an illumination light path polarized light beam through a polarizer 202; the illumination light path polarized light beam passes through a first 1/4 wave plate 203 to form an illumination light path circularly polarized light beam;
if the optical fiber 102 is a polarization maintaining fiber, the transmitted excitation light is a linearly polarized light beam, and the linearly polarized light beam is collimated by the lens assembly 201 to form a polarized light beam of an illumination light path; the illumination light path polarized light beam passes through a first 1/4 wave plate 203 to form an illumination light path circularly polarized light beam;
s22: the circular polarized light beam of the illumination optical path is divided into two ordinary rays (o rays) and extraordinary rays (e rays) which can interfere with each other through a first differential interference prism 204;
s23: the ordinary light (o light) and the extraordinary light (e light) are irradiated to the surface of the observed sample 104 through the illumination objective lens 205, and the surface of the observed sample 104 forms a returned scattered light beam of the illumination optical path;
s3: the scattered light beam of the illumination light path returned by the surface of the observed sample 104 is subjected to polarization resolution and focused imaging through an imaging receiving module 105;
s31: the illumination light path scattered light beam returned from the surface of the observed sample 104 is received by the imaging objective lens 206 and is collimated into an imaging received parallel light beam;
s32: the imaging reception parallel light beam is recombined into an imaging reception circular polarized light beam by a second differential interference prism 207;
s33: the imaged received circularly polarized light beam passes through a second 1/4 waveplate 208 to form an imaged received linearly polarized light beam;
s34: the imaging receiving linear polarized light beam only retains the imaging receiving linear polarized light beam carrying the object characteristic information through the analyzer 209 and is focused on the imaging detector 211 through the tube lens 210.
S4: the electrical signal generated by the image receiving module 105 is connected to an external control module via a cable 106.
Example 1, see fig. 1-4:
the illumination light source 101 is selected from an LD (laser diode) light source, the optical fiber 102 is selected from a quartz optical fiber, the observed sample 104 is selected from human tissue, the imaging detector 211 is selected from a COMS (complementary metal oxide semiconductor) detector, and the first differential interference prism 204 and the second differential interference prism 207 are selected from Wollaston prisms.
The illumination light path module 103 comprises a lens assembly 201, a polarizer 202, a first 1/4 wave plate 203, a first differential interference prism 204 and an illumination objective lens 205 which are sequentially arranged from top to bottom, and the imaging receiving module 105 comprises an imaging objective lens 206, a second differential interference prism 207, a second 1/4 wave plate 208, an analyzer 209, a barrel mirror 210 and an imaging detector 211 which are sequentially arranged from bottom to top.
Among them, it is to be noted that:
the interference surfaces of the first and second differential interference prisms 204 and 207 are coincident with the back focal surface of the illumination objective 205 and the interference surface of the imaging objective 206;
and the second point O represents the intersection point of the illumination or imaging optical path and the paper surface, and represents the positional relationship on the paper surface, the crystal axis direction of the polarizer 202 is perpendicular to the crystal axis direction of the analyzer 209, the crystal axis direction of the first 1/4 wave plate 203 is positioned at 45 ° clockwise from the crystal axis direction of the polarizer 202, the crystal axis direction of the first differential interference prism 204, the crystal axis direction of the second differential interference prism 207 and the crystal axis direction of the second 1/4 wave plate 208 are both positioned at 45 ° counterclockwise from the crystal axis direction of the polarizer 202.
The implementation process comprises the following steps: light emitted by the illumination light source 101 enters the optical fiber 102 through coupling, and is connected with the illumination light path module 103 through the optical fiber 102, the excitation light conducted by the optical fiber 102 is collimated by the lens assembly 201 to form an illumination light path parallel light beam, the illumination light path parallel light beam forms illumination light path linearly polarized light through the polarizer 202, the illumination light path polarized light forms illumination light path circularly polarized light beam through the first 1/4 wave plate 203, the illumination light path circularly polarized light is divided into two ordinary light (o light) and extraordinary light (e light) which can interfere with each other through the first differential interference prism 204, although the polarizer 202, the first 1/4 slide 203 and the first differential interference prism 204 change the polarization characteristics of the light beam, however, the light beams are also parallel, and therefore, the ordinary rays (o light) and the extraordinary rays (e light) are irradiated to the surface of the observed sample 104 through the illumination objective lens 205;
the surface of the observed sample 104 forms returned scattered light of the illumination light path, so that the two beams of ordinary light (o light) and extraordinary light (e light) carry the characteristic information of the observed sample 104, the scattered light of the illumination light path is received by the imaging objective 206, and the scattered light of the illumination light path is collimated into an imaging receiving parallel light beam, the imaging receiving parallel light beam is recombined into an imaging receiving circularly polarized light beam by the second differential interference prism 207, the imaging receiving circularly polarized light beam forms an imaging receiving linearly polarized light beam through the second 1/4 wave plate 208, the imaging receiving linearly polarized light beam retains only the imaging receiving linearly polarized light carrying the characteristic information of the object through the analyzer 209 and is focused and imaged on the imaging detector 211 through the barrel mirror 210, and the electric signal of the imaging detector 211 is connected with an external control module through the cable (106).
Example 1 cells imaged by differential interference method are shown in fig. 7.
Example 2, see fig. 1-2, fig. 5-6:
the illumination light source 101 is selected from a polarized light source, the observed sample 104 is selected from human tissue, the imaging detector 211 is selected from a CCD (charge coupled device) detector, the first differential interference prism 204 and the second differential interference prism 207 are selected from Nomarski (Nomarski) prisms, the optical fiber 102 is selected from a polarization-maintaining optical fiber, and the polarizer 202 is omitted because the light emitted by the optical fiber 102 is originally polarized light.
The illumination light path module 103 comprises a lens assembly 201, a first 1/4 wave plate 203, a first differential interference prism 204 and an illumination objective lens 205 which are sequentially arranged from top to bottom, and the imaging receiving module 105 comprises an imaging objective lens 206, a second differential interference prism 207, a second 1/4 wave plate 208, an analyzer 209, a tube mirror 210 and an imaging detector 211 which are sequentially arranged from bottom to top.
Among them, it is to be noted that:
the interference surfaces of the first and second differential interference prisms 204 and 207 are coincident with the back focal surface of the illumination objective 205 and the interference surface of the imaging objective 206;
second, point O indicates the intersection of the illumination or imaging optical path and the paper surface, and indicates the positional relationship on the paper surface, the light source polarization direction of the polarization maintaining fiber is perpendicular to the crystal axis direction of the analyzer 209, the crystal axis direction of the first 1/4 wave plate 203 is located at 45 ° clockwise with respect to the crystal axis direction of the light source polarization direction of the polarization maintaining fiber, the crystal axis direction of the first differential interference prism 204, the crystal axis direction of the second differential interference prism 207, and the crystal axis direction of the second 1/4 wave plate 208 are both located at 45 ° counterclockwise with respect to the crystal axis direction of the light source polarization direction of the polarization maintaining fiber.
The implementation process comprises the following steps: light emitted by the illumination light source 101 enters the optical fiber 102 through coupling, and through connection between the optical fiber 102 and the illumination light path module 103, the excitation light conducted by the optical fiber 102 is collimated by the lens assembly 201 to form a parallel illumination light path polarized light beam, which forms an illumination light path circularly polarized light beam through the first 1/4 wave plate 203, the illumination light path circularly polarized light beam is split into two ordinary light (o light) and extraordinary light (e light) which can interfere with each other by the first differential interference prism 204, and although the polarization characteristics of the light beam are changed by the first 1/4 glass plate 203 and the first differential interference prism 204, the light beams are parallel, so the ordinary light (o light) and the extraordinary light (e light) are irradiated to the surface of the observed sample 104 through the illumination objective lens 205;
the surface of the observed sample 104 forms returned scattered light of the illumination light path, so that the two beams of ordinary light (o light) and extraordinary light (e light) carry the characteristic information of the observed sample 104, the scattered light of the illumination light path is received by the imaging objective 206, and the scattered light of the illumination light path is collimated into an imaging receiving parallel light beam, the imaging receiving parallel light beam is recombined into an imaging receiving circularly polarized light beam by the second differential interference prism 207, the imaging receiving circularly polarized light beam forms an imaging receiving linearly polarized light beam through the second 1/4 wave plate 208, the imaging receiving linearly polarized light beam retains only the imaging receiving linearly polarized light carrying the characteristic information of the object through the analyzer 209 and is focused and imaged on the imaging detector 211 through the barrel mirror 210, and the electric signal of the imaging detector 211 is connected with an external control module through the cable (106).
Comparative example 1
The human tissue in example 1 photographed by the general imaging method is as shown in fig. 8.
As can be seen from comparing example 1 with comparative example 1, the distinctive feature of the differential interference technique is to enhance the contrast of the observed object, convert the height and height features of the sample into intensity information, and form a relief feeling. The sample shot by the traditional endoscope is two-dimensional, the height characteristic information of the sample is not available, and the special focus usually has irregular height fluctuation characteristics, while the image shot by the traditional observation method does not contain the information, and the doctor can easily ignore the characteristics. The introduction of differential interference technology into the endoscope helps the doctor judge the characteristics of the focus by the surface relief characteristics of the observed sample to make a diagnosis.
The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention, and various modifications and changes may be made by those skilled in the art. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Claims (10)
1. A differential interference contrast microscopy endoscopic imaging system, comprising:
an illumination light source (101) for generating excitation light;
an optical fiber (102) for conducting excitation light;
an illumination light path module (103) for modulating and shaping the excitation light transmitted by the optical fiber (102) and illuminating the surface of the observed sample (104), wherein the illumination light path module (103) comprises a collimation polarization module (20), a first differential interference prism (204) and an illumination objective lens (205) which are sequentially arranged from top to bottom;
the imaging receiving module (105) is used for analyzing and imaging the scattered light returned by the surface of the observed sample (104), and the imaging receiving module (105) comprises an imaging objective lens (206), a second differential interference prism (207), a second 1/4 wave plate (208), an analyzer (209), a barrel mirror (210) and an imaging detector (211) which are sequentially arranged from bottom to top;
and the cable (106) is used for conducting the electric signals of the imaging receiving module (105) and is connected with an external control module.
2. The differential interference contrast microscopy endoscopic imaging system according to claim 1, wherein when the optical fiber (102) is a polymer fiber or a quartz optical fiber, the collimating and polarizing module (20) comprises a lens assembly (201), a polarizer (202) and a first 1/4 wave plate (203) arranged in sequence from top to bottom; when the optical fiber (102) is a polarization maintaining fiber, the collimating and polarizing module (20) comprises a lens assembly (201) and a first 1/4 wave plate (203) which are sequentially arranged from top to bottom.
3. The differential interference contrast microscopy endoscopic imaging system according to claim 2, wherein the interference surface of the first differential interference prism (204) coincides with the back focal surface of the illumination objective (205) and the interference surface of the second differential interference prism (207) coincides with the interference surface of the imaging objective (206).
4. The differential interference contrast microscopy endoscopic imaging system according to claim 2, wherein the crystal axis direction of the polarizer (202) or the light source polarization direction of the polarization maintaining fiber is perpendicular to the crystal axis direction of the analyzer (209), the crystal axis direction of the first 1/4 wave plate (203) is 45 ° clockwise from the crystal axis direction of the polarizer (202), the crystal axis direction of the first differential interference prism (204), the crystal axis direction of the second differential interference prism (207) and the crystal axis direction of the second 1/4 wave plate (208) are 45 ° counterclockwise from the crystal axis direction of the polarizer (202).
5. The differential interference contrast microscopy endoscopic imaging system according to claim 1, wherein said illumination light path module (103) and said image receiving module (105) are located on the same side of said observed sample (104) and integrated into an endoscopic probe.
6. The differential interference contrast microscopy endoscopic imaging system according to claim 1, wherein said illumination source (101) is selected from one of an LED light source, an LD light source, or a polarized light source; the imaging detector (211) is selected from a COMS detector or a CCD detector; the first differential interference prism (204) and the second differential interference prism (207) are selected from wollaston prisms or nomas prisms.
7. A differential interference contrast microscopy endoscopic imaging method is characterized by comprising the following steps:
s1: providing an illumination light source (101) for generating excitation light, coupling said excitation light from said illumination light source (101) into an optical fiber (102);
s2: through the connection of the optical fiber (102) and an illumination optical path module (103), the excitation light conducted by the optical fiber (102) is divided into two ordinary light and extraordinary light which can interfere with each other through the illumination optical path module (103) and is irradiated to the surface of an observed sample (104), and the surface of the observed sample (104) forms a returned illumination optical path scattered light beam;
s3: polarization resolving and focusing imaging is carried out on the illumination light path scattered light beam returned by the surface of the observed sample (104) through an imaging receiving module (105);
s4: the electric signal formed by the imaging receiving module (105) is connected with an external control module through a cable (106).
8. The differential interference contrast microscopy endoscopic imaging method according to claim 7, wherein said step S2 comprises the following sub-steps:
s21: the excitation light conducted by the optical fiber (102) is modulated and shaped by a collimation polarization module (20) to form a circularly polarized light beam of an illumination light path;
s22: the circular polarized light beam of the illumination optical path is divided into two ordinary lights and extraordinary lights which can interfere with each other through a first differential interference prism (204);
s23: the ordinary ray and the extraordinary ray are irradiated to the surface of the observed sample (104) through the illumination objective lens (205), and the surface of the observed sample (104) forms a returned illumination optical path scattered light beam.
9. The differential interference contrast microscopy endoscopic imaging method according to claim 8, wherein said step S21 comprises the following sub-steps:
if the optical fiber (102) is a polymer fiber or a quartz optical fiber, the transmitted excitation light is collimated by the lens component (201) to form a parallel light beam of an illumination light path; the parallel light beams of the illumination light path form an illumination light path polarized light beam through a polarizer (202); the illumination light path polarized light beam passes through a first 1/4 wave plate (203) to form an illumination light path circularly polarized light beam;
if the optical fiber (102) is a polarization maintaining optical fiber, the transmitted excitation light is a linearly polarized light beam, and the linearly polarized light beam is collimated by the lens component (201) to form a polarized light beam of an illumination light path; the illumination light path polarized beam passes through a first 1/4 wave plate (203) to form an illumination light path circularly polarized beam.
10. The differential interference contrast microscopy endoscopic imaging method according to claim 9, wherein said step S3 comprises the following sub-steps:
s31: the scattered light beam of the illumination light path returned by the surface of the observed sample (104) is received by an imaging objective lens (206), and the scattered light beam of the illumination light path is collimated into an imaging receiving parallel light beam;
s32: the imaging reception parallel light beam is recombined into an imaging reception circular polarized light beam by a second differential interference prism (207);
s33: the imaging receive circularly polarized light beam passes through a second 1/4 waveplate (208) to form an imaging receive linearly polarized light beam;
s34: the imaging receiving linear polarized light beam only retains the imaging receiving linear polarized light beam carrying the object characteristic information through an analyzer (209), and is focused and imaged on an imaging detector (211) through a tube lens (210).
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