CN110824688A - Rapid reconstruction method for biological cell subsurface morphology based on phase imaging - Google Patents
Rapid reconstruction method for biological cell subsurface morphology based on phase imaging Download PDFInfo
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Abstract
The invention provides a phase imaging-based quick reconstruction method for the sub-surface morphology of biological cells, which comprises the steps of extracting a phase image of a cell sample and reconstructing the appearance of the cell sample; the invention obtains a phase diagram of a sample to be measured based on a mirror image inverted microscope, determines the boundaries of different parts of the sample by applying a phase gradient algorithm, and extracts boundary points to reconstruct the surface of the sample. Finally, based on optical experiments, surface morphology maps of the polystyrene microspheres and the erythrocytes are obtained by the method. The invention has wide practical value and application prospect in the aspects of live cell phase microscopic imaging and real-time identification, has the obvious advantages of no wound and no mark, and has important significance in the fields of biological cell phase microscopic imaging, form reconstruction and the like.
Description
Technical Field
The invention belongs to the field of phase microscopic imaging, and particularly relates to a method for quickly reconstructing a sub-surface morphology of a biological cell based on phase imaging.
Background
Cells are the physical, structural and functional units of life. Each cell contains the necessary organelles necessary for the survival of the cell. A living cell is a complex structure containing numerous organelles of different refractive indices. Therefore, knowledge of the refractive index is crucial for monitoring the properties of living cells. When light passes through such a transparent phase object, a phase shift closely related to the refractive index profile can be induced. In view of this phenomenon, quantitative phase microscopy QPM is applied to obtain morphological and structural information of cells. As a full-field, non-invasive microscope, QPM enables non-contact, non-invasive and fast high resolution imaging and is portable, requiring little maintenance. The method provides a powerful tool for the three-dimensional static and dynamic appearance observation, cell dynamics behavior characteristics and other researches of the phase object. However, the phase image cannot be used to directly show the shape and structure of cells, especially for nucleated cells, because the refractive index information and physical thickness information of the sample are coupled in the phase image.
Therefore, shape reconstruction is really important. There are many methods for reconstructing cell morphology, such as dual wavelength technique, entropy tomographic reconstruction method, and the like. Using these methods, refractive index information of the sample can be obtained and three-dimensional morphological features of the biological cells reconstructed. However, these tasks take a lot of time and the cost of the laboratory equipment is high.
Disclosure of Invention
Aiming at the technical problems, the invention provides a method for quickly reconstructing the sub-surface morphology of a biological cell based on phase imaging. The method comprises the steps of obtaining a phase diagram of a sample to be detected based on a mirror image inverted microscope, determining the boundaries of different parts of the sample by applying a phase gradient algorithm, and extracting boundary points to reconstruct the surface of the sample. The invention has wide practical value and application prospect in the aspects of live cell phase microscopic imaging and real-time identification, has the obvious advantages of no wound and no mark, and has important significance in the fields of biological cell phase microscopic imaging, form reconstruction and the like.
The technical scheme adopted by the invention for solving the technical problems is as follows: a phase imaging-based method for rapidly reconstructing the sub-surface morphology of biological cells comprises the following steps:
step S1, cell sample phase image extraction: obtaining a phase image of the cell sample by a microscope imaging system;
step S2, reconstructing the shape of the cell sample:
step S2.1, recording a phase map of the sample, the phase map of the sample being expressed as:
wherein the content of the first and second substances,representing the total phase shift value of light passing through the transparent sample, h (x, y) representing the axial physical thickness of light passing through the sample, nc(x, y, z) represents the average refractive index of the sample, nmThe refractive index of the environmental liquid where the sample is located is represented, and lambda is the wavelength of light;
step S2.2, recording a phase gradient curve of the sample:
xnn is positive integer formula three
X represents an axial gradient curve along the X direction, and n represents the division of the phase map into n phase gradient curves according to the number of pixels of the acquired phase map, i.e., n × n;
s2.3, judging the jumping point, and determining the boundary information of the sample:
judging the number of jump points on each phase gradient curve according to the formula IV,
Py(x，y)-Py(x，y-1)＞0andPy(x，y)-Py(x, y-1) > 0 formula four
Py(x, Y) represents a phase gradient value in the Y direction at the coordinate point (x, Y), Py(x, y-1) represents the phase gradient value of the previous point of (x, y), Py(x, y +1) represents a phase gradient value at a point subsequent to (x, y), and a phase gradient value P at the coordinate point (x, y)y(x, y) is larger than the phase gradient values of two adjacent points, and is the peak value of the nearby phase gradient, the point is called a jump point, and the boundary information of the sample is determined through the jump point;
s2.4, three-dimensional shape reconstruction:
obtaining a formula five according to the physical thickness of the formula two inversion sample, calculating the physical thickness of the sample, obtaining the three-dimensional shape of the sample according to the boundary information and the physical thickness of the sample,
wherein h represents the physical thickness of the sample,
representing the total phase shift value, n, of light passing through the transparent samplec(x，y，z）-nmRepresenting the difference between the average refractive index of the sample and the refractive index of the ambient liquid in which the sample is located.
In the above scheme, the microscope imaging system includes a light source, a frosted lens, a color filter, a first reflector, a first objective, an electric loading platform, a second reflector, a 4f imaging system, a beam splitter prism, a first CCD, a second CCD and imaging software;
the frosted lens, the color filter and the first reflector are distributed side by side along the output direction of the light source;
the first objective lens, the electric objective platform and the second objective lens are sequentially arranged along the direction of reflected light;
the second reflecting mirror, the 4f imaging system and the beam splitter prism are sequentially distributed along the parallel light speed, the light path is converged on the beam splitter prism and is respectively projected on the first CCD and the second CCD, and the first CCD and the second CCD are respectively connected with imaging software.
Further, the step S1 of obtaining the phase image of the cell sample by the microscope imaging system specifically includes:
s1.1, enabling light beams emitted by a light source with the wavelength of lambda to enter a mirror image inverted microscope system, and forming parallel light to enter a first reflector after the light beams pass through a frosted lens and a color filter;
s1.2, after passing through a first reflector, parallel light passes through a first objective and a sample placed on an electric loading platform, and then passes through a second objective and is converged to a second reflector to form parallel light beams;
and S1.3, the parallel light beam passes through a 4f imaging system, is divided into two beams of light through a beam splitter prism, is received by a first CCD and a second CCD of two information collectors respectively, and is finally transmitted to imaging software to form a phase image.
In the above scheme, the microscope imaging system is a BioPhase mirror inverted microscope imaging system.
Further, the BioPhase mirror inverted microscope imaging system is an olympus GX51 mirror inverted microscope system.
In the above scheme, the imaging software is BioPhase imaging software.
Compared with the prior art, the invention has the beneficial effects that: the phase microscopic imaging method based on the image inversion microscopic imaging system realizes phase microscopic imaging, has the advantages of no damage and no mark, can quickly acquire phase information of a sample, and has high reliability and stability, repeated experiment and low cost. The invention provides a trip point and a judgment method, the judgment condition of the trip point is very sensitive to the refractive index conversion, the boundary information of a sample can be accurately reflected, the trip point is a simple operation method, the surface of the sample can be rapidly obtained, and the trip point is particularly suitable for dynamically detecting the morphological characteristics of biological cells in real time.
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The above and/or additional aspects and advantages of the present invention will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings of which:
FIG. 1 is a schematic diagram of the optical path of one embodiment of the present invention.
FIG. 2 is a phase diagram of FIG. 2(a) and a phase gradient diagram of FIG. 2(b) of a polystyrene microsphere with a diameter of 4 μm according to an embodiment of the present invention, in which points A1 and A2 respectively represent transition points,
FIG. 3 is a three-dimensional reconstruction diagram of a polystyrene microsphere with a diameter of 4 μm according to an embodiment of the present invention, wherein the distance between two points is the reconstructed thickness of the polystyrene microsphere.
FIG. 4 is a phase diagram of human erythrocytes in FIG. 4(a) and a phase gradient diagram in FIG. 4(B) according to another embodiment of the present invention, in which points B1 and B2 respectively represent transition points.
Fig. 5 is a three-dimensional reconstruction diagram of a phase diagram of human red blood cells along an illumination direction according to another embodiment of the present invention, wherein the distance between two points is the thickness of the reconstructed human red blood cells.
Table 1 shows the reconstruction results of polystyrene microspheres with a diameter of 4 microns, wherein the reconstruction thickness of the polystyrene microspheres is 3.98 microns, the true thickness is 4 microns, the error is 0.5%, and the whole reconstruction process takes 0.0484 s.
In the figure, 1: a light source; 2: a frosted lens; 3: a color filter; 4: a first reflector; 5: a first objective lens; 6: a second objective lens; 7: an electric loading platform; 8: a second reflector; 9: 4f an imaging system; 10: a beam splitter prism; 11: a first CCD; 12: a second CCD; 13: imaging software.
Detailed Description
Reference will now be made in detail to embodiments of the present invention, examples of which are illustrated in the accompanying drawings, wherein like or similar reference numerals refer to the same or similar elements or elements having the same or similar function throughout. The embodiments described below with reference to the drawings are illustrative and intended to be illustrative of the invention and are not to be construed as limiting the invention.
A phase imaging-based method for rapidly reconstructing the sub-surface morphology of biological cells comprises the following steps:
step S1, cell sample phase image extraction: obtaining a cell sample phase image through a microscope imaging system, wherein the microscope imaging system comprises a light source 1, a frosted lens 2, a color filter 3, a first reflector 4, a first objective lens 5, an electric loading platform 6, a second reflector 7, a second reflector 8, a 4f imaging system 9, a beam splitter prism 10, a first CCD11, a second CCD12 and imaging software 13; the frosted lens 2, the color filter 3 and the first reflector 4 are distributed side by side along the output direction of the light source 1; the first objective lens 5, the electric objective platform 6 and the second objective lens 7 are sequentially arranged along the direction of reflected light; the second reflecting mirror 8, the 4f imaging system 9 and the beam splitter prism 10 are sequentially distributed along the parallel light speed, the light path is converged on the beam splitter prism 10 and is respectively projected on the first CCD11 and the second CCD12, and the first CCD11 and the second CCD12 are respectively connected with the imaging software 13.
The step S1 of obtaining the phase image of the cell sample by the microscope imaging system specifically includes:
s1.1, enabling a light beam emitted by a light source 1 with the wavelength of lambda to enter an Olympus GX51 mirror inversion microscope system, and forming parallel light to enter a first reflecting mirror 4 after passing through a ground lens 2 and a color filter 3;
s1.2, after passing through a first reflector 4, parallel light passes through a first objective 5 and a sample placed on an electric loading platform 6, passes through a second objective 7 and then is converged to a second reflector 8 to form parallel light beams;
s1.3, the parallel light beam passes through a 4f imaging system 9, is divided into two beams by a beam splitter prism 10, is recorded by a first CCD11 and a second CCD12 of two information collectors respectively, and is finally transmitted to a Biophase imaging software 13 to form a required phase image;
step S2, reconstructing the shape of the cell sample:
step S2.1, recording a phase map of the sample,
the phase map of the sample is expressed as:
wherein
Showing the total phase shift value of light passing through the transparent sample, h (x, y) the axial physical thickness of light passing through the sample,representing the refractive index of a point within the sample, nmThe refractive index of the environmental liquid where the sample is located is represented, and lambda is the wavelength of light;
considering the heterogeneity of the refractive indexes of the same medium of actual cells, the average refractive index n is introduced for calculationc(x, y, z) instead of
Step S2.2, recording the phase gradient curve of the sample,
xnn, (n ═ 1, 2.. 255) formula three
X represents an axial gradient curve along the X direction, and n represents the division of the phase map into n phase gradient curves according to the number of pixels of the acquired phase map, i.e., 255 × 255;
s2.3, judging the jumping points, judging the number of the jumping points on each phase gradient curve according to a formula IV,
Py(x，y)-Py(x，y-1)＞0and Py(x，y)-Py(x, y +1) > 0 equation four
Py(x, Y) represents a phase gradient value in the Y direction at the coordinate point (x, Y), Py(x, y-1) represents the phase gradient value of the previous point of (x, y), Py(x, y +1) represents the phase gradient value of the point (x, y) subsequent to the point (x, y), and the point satisfying the formula four is called a trip point, and usually appears in pairs (light incidence and light emission), and the phase gradient value P at the coordinate point (x, y)y(x, y) is larger than the phase gradient values of two adjacent points, and is the peak value of the nearby phase gradient, the point is called a jump point, and the boundary information of the sample is determined through the jump point;
s2.4, reconstructing the three-dimensional shape, obtaining a formula V according to the physical thickness of the formula II inverted sample, calculating the physical thickness of the sample, obtaining the three-dimensional shape of the sample through the boundary information and the physical thickness of the sample,
wherein h represents the physical thickness of the sample,
representing the total phase shift value, n, of light passing through the transparent samplec(x，y，z)-nmRepresents the average of a sampleThe difference between the average refractive index and the refractive index of the ambient liquid in which the sample is located.
Example 1:
in order to further illustrate the application effect of the reconstruction method in practice, the invention takes the polystyrene microspheres as experimental samples for experiments.
According to the working principle of a Biophase inverted mirror microscope, phase imaging is carried out on the polystyrene microsphere of the experimental sample, the experimental environment is Olympus lens oil, the refractive index of the environmental liquid is 1.4218, and the wavelength lambda of light is 632.8nm, so that a polystyrene microsphere phase diagram is obtained, as shown in fig. 2 (a);
taking the gradient of the obtained polystyrene microsphere phase diagram 2(a) according to the formula three, for convenience of explanation, taking a gradient curve passing through the center of the polystyrene microsphere phase diagram as an example, as shown in fig. 2(b), and according to the formula four, two points a1 and a2 in fig. 2(b) respectively represent the transition point, i.e., the boundary point, of the polystyrene microsphere phase diagram 2(b), and the refractive indexes at the two points are known, i.e., the average refractive index is 1.5916;
and (3) performing thickness inversion on the polystyrene microsphere along the illumination direction according to a formula five to obtain the three-dimensional morphology of the polystyrene microsphere, and adding absolute values of vertical coordinates of two points in the graph 3 to obtain the thickness of the polystyrene microsphere along the illumination direction as shown in the graph 3.
According to the obtained reconstruction result, as shown in fig. 3, error analysis is performed, the thickness of the polystyrene microsphere reconstructed by the method provided by the invention is 3.98 micrometers, the actual thickness of the polystyrene microsphere is 4 micrometers, the error is 0.5%, and the whole reconstruction process only takes 0.0484 seconds, which indicates that the reconstruction device and the method can be used for real-time detection of the experimental sample and the reconstruction result is better.
TABLE 1
Example 2:
in order to further illustrate the application of the reconstruction method in the actual biological cell reconstruction, the invention takes human blood red blood cells as experimental samples for carrying out experiments.
According to the working principle of a Biophase inverted mirror microscope, performing phase imaging on human red blood cells of an experimental sample, wherein the experimental environment is physiological saline, the refractive index is 1.33, and the wavelength lambda of light is 632.8nm to obtain a phase diagram of the human red blood cells, as shown in fig. 4 (a);
taking the gradient of the obtained human erythrocyte phase diagram 4(a) according to the formula three, for convenience of explanation, taking a gradient curve passing through the center of the human erythrocyte phase diagram as an example, as shown in fig. 4(B), and according to the formula four, two points B1 and B2 in fig. 4(B) respectively represent the jump point, i.e. the boundary point, of the human erythrocyte phase diagram 4(a), and the refractive indexes at the two points are known, and the refractive index is 1.41;
and (3) performing thickness inversion on the human red blood cells along the illumination direction according to a formula five to obtain the three-dimensional morphology of the human red blood cells, as shown in fig. 5. This indicates that the reconstruction apparatus and method can indeed be used for real-time detection of experimental samples.
It should be understood that although the present description has been described in terms of various embodiments, not every embodiment includes only a single embodiment, and such description is for clarity purposes only, and those skilled in the art will recognize that the embodiments described herein may be combined as suitable to form other embodiments, as will be appreciated by those skilled in the art.
The above-listed detailed description is only a specific description of a possible embodiment of the present invention, and they are not intended to limit the scope of the present invention, and equivalent embodiments or modifications made without departing from the technical spirit of the present invention should be included in the scope of the present invention.
Claims (6)
1. A phase imaging-based method for rapidly reconstructing the sub-surface morphology of biological cells is characterized by comprising the following steps:
step S1, cell sample phase image extraction: obtaining a phase image of the cell sample by a microscope imaging system;
step S2, reconstructing the shape of the cell sample:
step S2.1, recording a phase map of the sample, the phase map of the sample being expressed as:
wherein the content of the first and second substances,
representing the total phase shift value of light passing through the transparent sample, h (x, y) representing the axial physical thickness of light passing through the sample, nc(x, y, z) represents the average refractive index of the sample, nmThe refractive index of the environmental liquid where the sample is located is represented, and lambda is the wavelength of light;
step S2.2, recording a phase gradient curve of the sample:
xnn is positive integer formula three
X represents an axial gradient curve along the X direction, and n represents the division of the phase map into n phase gradient curves according to the number of pixels of the acquired phase map, i.e., n × n;
s2.3, judging the jumping point, and determining the boundary information of the sample:
judging the number of jump points on each phase gradient curve according to the formula IV,
Py(x，y)-Py(x，y-1)＞0 and Py(x，y)-Py(x, y-1) > 0 formula four
Py(x, Y) represents a phase gradient value in the Y direction at the coordinate point (x, Y), Py(x, y-1) represents the phase gradient value of the previous point of (x, y), Py(x, y +1) represents a phase gradient value at a point subsequent to (x, y), and a phase gradient value P at the coordinate point (x, y)y(x, y) is larger than the phase gradient values of two adjacent points, and is the peak value of the nearby phase gradient, the point is called a jump point, and the boundary information of the sample is determined through the jump point;
s2.4, three-dimensional shape reconstruction:
obtaining a formula five according to the physical thickness of the formula two inversion sample, calculating the physical thickness of the sample, obtaining the three-dimensional shape of the sample according to the boundary information and the physical thickness of the sample,
wherein h represents the physical thickness of the sample,representing the total phase shift value, n, of light passing through the transparent samplec(x，y，z)-nmRepresenting the difference between the average refractive index of the sample and the refractive index of the ambient liquid in which the sample is located.
2. The phase imaging-based rapid reconstruction method for biological cell subsurface morphology according to claim 1, wherein the microscope imaging system comprises a light source (1), a frosted lens (2), a color filter (3), a first reflector (4), a first objective lens (5), an electric object stage (6), a second reflector (7), a second reflector (8), a 4f imaging system (9), a beam splitter prism (10), a first CCD (11), a second CCD (12) and imaging software (13);
the frosted lens (2), the color filter (3) and the first reflector (4) are distributed side by side along the output direction of the light source (1);
the first objective lens (5), the electric loading platform (6) and the second objective lens (7) are sequentially arranged along the direction of reflected light;
the second reflecting mirror (8), the 4f imaging system (9) and the light splitting prism (10) are sequentially distributed along the parallel light speed, the light path is converged on the light splitting prism (10) and is respectively projected on the first CCD (11) and the second CCD (12), and the first CCD (11) and the second CCD (12) are respectively connected with imaging software (13).
3. The phase imaging-based rapid reconstruction method for the sub-surface morphology of the biological cells according to claim 2, wherein the step S1 of obtaining the phase image of the cell sample by the microscope imaging system specifically comprises:
s1.1, enabling light beams emitted by a light source (1) with the wavelength of lambda to enter a mirror image inverted microscope system, and forming parallel light to enter a first reflector (4) after passing through a frosted lens (2) and a color filter (3);
s1.2, after passing through a first reflector (4), parallel light passes through a first objective (5) and a sample placed on an electric objective platform (6), passes through a second objective (7), and then is converged to a second reflector (8) to form parallel light beams;
and S1.3, the parallel light beam passes through a 4f imaging system (9), is divided into two beams through a beam splitter prism (10), is respectively received by a first CCD (11) and a second CCD (12) of two information collectors, and is finally transmitted to imaging software (13) to form a phase image.
4. The method for rapidly reconstructing the sub-surface morphology of biological cells based on phase imaging according to any one of claims 1 to 3, wherein the microscope imaging system is a Biophase mirror inverted microscope imaging system.
5. The method for rapidly reconstructing the sub-surface morphology of a biological cell based on phase imaging according to any one of claims 4, wherein the Biophase mirror inverted microscope imaging system is an Olympus GX51 mirror inverted microscope system.
6. The phase imaging-based rapid reconstruction method of the sub-surface morphology of the biological cells according to claim 2 or 3, wherein the imaging software (3) is Biophase imaging software.
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114326352A (en) * | 2021-12-31 | 2022-04-12 | 南京理工大学智能计算成像研究院有限公司 | Real-time cell three-dimensional analysis method based on digital holography |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6608717B1 (en) * | 1999-01-29 | 2003-08-19 | Colorado State University Research Foundation | Optical coherence microscope and methods of use for rapid in vivo three-dimensional visualization of biological function |
| CN204116710U (en) * | 2014-09-26 | 2015-01-21 | 江苏大学 | A kind of two step diffraction phase imaging systems |
| CN105806250A (en) * | 2016-03-10 | 2016-07-27 | 中国科学院上海光学精密机械研究所 | High resolution 3D phase microscopy imaging device and imaging method |
| CN110109240A (en) * | 2019-04-08 | 2019-08-09 | 江苏大学 | Binary channels dual wavelength phase micro imaging system and method under Non-orthogonal basis set |
-
2019
- 2019-10-12 CN CN201910966220.2A patent/CN110824688A/en active Pending
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6608717B1 (en) * | 1999-01-29 | 2003-08-19 | Colorado State University Research Foundation | Optical coherence microscope and methods of use for rapid in vivo three-dimensional visualization of biological function |
| CN204116710U (en) * | 2014-09-26 | 2015-01-21 | 江苏大学 | A kind of two step diffraction phase imaging systems |
| CN105806250A (en) * | 2016-03-10 | 2016-07-27 | 中国科学院上海光学精密机械研究所 | High resolution 3D phase microscopy imaging device and imaging method |
| CN110109240A (en) * | 2019-04-08 | 2019-08-09 | 江苏大学 | Binary channels dual wavelength phase micro imaging system and method under Non-orthogonal basis set |
Non-Patent Citations (2)
| Title |
|---|
| YING JI: "A fast morphological reconstruction method of biological cells based on phase imaging", 《OPTIK》 * |
| 徐媛媛: "生物细胞定量相位显微技术及相位恢复方法的新进展", 《激光与光电子学进展》 * |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114326352A (en) * | 2021-12-31 | 2022-04-12 | 南京理工大学智能计算成像研究院有限公司 | Real-time cell three-dimensional analysis method based on digital holography |
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