阅读说明：本技术 基于细胞旋转主动光操控技术的散斑荧光显微方法和系统 (Speckle fluorescence microscopy method and system based on cell rotation active light control technology ) 是由 尹君 王少飞 于凌尧 陈宏宇 胡徐锦 贾源 苑立波 于 2021-07-12 设计创作，主要内容包括：本发明提供的是一种基于细胞旋转主动光操控技术的散斑荧光显微方法和系统。其特征是：该装置光操控部分由三台激光器组成。一台激光光束完成对细胞的稳定捕获,另一台激光器经过声光调制器产生不同的偏转角度,由显微物镜聚焦交替照射到被捕获细胞两端,实现细胞旋转角度的精准主动光操控。细胞每旋转至不同角度并达到稳定状态后,第三台激光器产生动态散斑,激发照明层面内的荧光团,获取细胞的层析图像,最终重构细胞的三维结构图像。本发明构建的系统可实现活体单细胞高时间和高空间分辨率的三维结构成像,具有结构简单、成本低、易操作、非侵入等特点,在生物学、医学和生命科学等许多研究领域中都具有广阔的应用前景。(The invention provides a speckle fluorescence microscopy method and a system based on a cell rotation active light control technology. The method is characterized in that: the light control part of the device consists of three lasers. One laser beam completes stable capture of cells, and the other laser generates different deflection angles through an acousto-optic modulator, and the two deflection angles are focused by a microscope objective and alternately irradiated to the two ends of the captured cells, so that accurate active light control of the cell rotation angle is realized. And after the cells rotate to different angles and reach a stable state, the third laser generates dynamic speckles to excite fluorophores in the illumination layer surface, so that a chromatographic image of the cells is obtained, and finally a three-dimensional structural image of the cells is reconstructed. The system constructed by the invention can realize three-dimensional structure imaging of living unicells with high time and high spatial resolution, has the characteristics of simple structure, low cost, easy operation, non-invasion and the like, and has wide application prospect in many research fields of biology, medicine, life science and the like.)

1. The invention provides a speckle fluorescence microscopy method and a system based on a cell rotation active light control technology. The method is characterized in that: the system consists of a dynamic speckle illumination microscopic imaging system and an optical control system. It consists of laser light sources 1, 13, 18; lenses 2, 3, 6, 7, 14, 15, 20, 21; a micro-displacement stage 4; a scatterer 5; a CMOS camera 8; an imaging lens 9; an optical filter 10; dichroic mirrors 11, 16; apochromatic microobjectives 12, 17; a test cell 23; a mirror 22; an acousto-optic deflector 19. In the system, a laser beam output by a laser light source 1 is expanded by lenses 2 and 3 and forms a speckle pattern through a scatterer 5. After being expanded by the lenses 6 and 7, the light is reflected by the dichroic mirror 11, forms an image of a speckle pattern on the back focal plane of the apochromatic microscope objective 12, and forms full-field illumination on the cell 23 to be measured. The position of the scatterer 5 is adjusted by moving the micro-displacement stage 4, so that the speckle pattern projected on the cell 23 to be measured is changed. By extracting such different pattern variations, high-temporal-rate and high-spatial-rate tomographic images of the test cell 23 are obtained. After the laser output by the laser 13 is expanded by the lenses 14 and 15, the laser is reflected and coupled into the apochromatic microscope objective 17 by the dichroic mirror 16, and is focused on the cell 23 to be detected as captured light, so that the cell is stably captured and detected. The laser light output from the laser 18 is coupled into the acousto-optic deflector 19 to generate a laser beam with a certain deflection angle. Coupled into apochromatic microscope objective 17 via lenses 20, 21. By changing the modulation frequency of the acousto-optic deflector 19 alternately, the focused light beams are focused on two ends of the cell 23 to be detected alternately and are respectively used as rotating light for pushing the cell to rotate and brake light for stopping the cell to rotate, so that accurate active light control on the rotating angle of the cell is realized. When the cells rotate to an angle and reach stability, a fluorescence tomography image of an illumination area is obtained by a dynamic speckle illumination microscopy technology. Under the alternate action of the pushing light and the braking light, the cell 23 to be detected continuously rotates, and the rapid scanning of dynamic speckle illumination in the cell is realized, so that a high-spatial-resolution fluorescence tomography image of a three-dimensional structure in the cell is obtained.

2. The speckle fluorescence microscopy method and system based on cell rotation active light manipulation technique according to claim 1. The dynamic speckle illumination wide-field fluorescence microscopic imaging system mainly comprises a laser light source 1; lenses 2, 3, 6, 7; a scatterer 5; a micro-displacement stage 4; apochromatic microobjective 12; a dichroic mirror 11; an optical filter 10; a test cell 23; an imaging lens 9; a CMOS camera 8. In the system, a laser beam emitted by a laser source 1 is expanded by lenses 2 and 3 and then is projected onto a scatterer 5 to form a speckle pattern, the laser beam is expanded by lenses 6 and 7, an image of the speckle pattern is formed on a focal plane behind an apochromatic microscope objective 12 after being reflected by a dichroic mirror 11, and full-field illumination is formed on a cell 23 to be measured by the apochromatic microscope objective 12. When the cell 23 to be detected rotates to a specific angle under the control of the optical field and reaches a stable state, the position of the scatterer 5 is changed by moving the micro-displacement stage 4, so that the speckle pattern projected on the cell 23 to be detected is changed. Fluorescence signals generated by excitation of different speckle patterns are collected by an apochromatic microscope objective lens 12, background noise is eliminated through a dichroic mirror 11 and an optical filter 10, and a plurality of fluorescence images are synchronously recorded through an imaging lens 9 and a CMOS camera 8. Under the condition of speckle illumination, the fluorescence signal generated by excitation near the focal plane changes most intensely, and the fluorescence tomography image near the focal plane can be extracted by utilizing a root-mean-square algorithm. The cell 23 is controlled to rotate continuously around the axis by changing the intensity distribution of the optical field, so that a three-dimensional structure fluorescence image of the whole cell 23 to be detected is obtained.

3. The speckle fluorescence microscopy method and system based on cell rotation active light manipulation technique according to claim 1. The light control system mainly comprises laser light sources 13 and 18; a mirror 22; lenses 14, 15, 20, 21; a dichroic mirror 16; an acousto-optic deflector 19; apochromatic microobjective 17. The light manipulation part is composed of capture light split by the laser 1 and deflectable light emitted by the laser 18 and controlled by the acousto-optic deflector 19, and the capture light is used for capturing cells to be detected, so that the cells are fixed at a position to facilitate imaging and rotating around a fixed axis. The laser emitted by the laser 18 enters the acousto-optic deflector 19, the acousto-optic deflector 19 can change the angle of the laser, the laser finally reaches one side of the cell through the lens to push the cell, when the cell rotates a certain angle, the light is deflected to the other direction through the action of the acousto-optic modulator 19 and reaches the other side of the cell to brake the cell, and when the cell is static, the CMOS camera 8 collects the structures of the cell at different angles again, and the three-dimensional structure of the cell is obtained through repeated times.

(I) technical field

The invention relates to a speckle fluorescence microscopy method and a speckle fluorescence microscopy system based on a cell rotation active light control technology, which can be used for capturing and controlling living unicells and imaging a three-dimensional structure with high time resolution and high spatial resolution, and belongs to the field of biological optical tweezers and biological imaging.

(II) background of the invention

Cells are the basic units of structure and function of an organism, and also the basic units of life activities. Cells are capable of proliferation through division and are the basis for the ontogeny and phylogeny of organisms. The cells are either independent as life units or a plurality of cells form cell groups or tissues or organs, systems and the whole; the cell is a basic unit of heredity and has totipotency of heredity. All organisms, except viruses, are composed of cells.

With the increasingly intensive exploration of the nature of life activities, it is desirable to gain a clearer understanding of the structure and function of cells through more detailed observation of the internal structure of cells. Biopharmaceuticals and other biological products can be developed by studying cells. For example, protein preparations with high purity, such as various antibodies, receptors, growth factors, cytokines, blood factors, neurotransmitters, have been produced in large quantities by cell engineering and genetic engineering techniques, and these products are commercialized and widely used in medical diagnosis and therapeutic practice. The rapid development of the research of genomics and proteomics inevitably promotes the rapid development of the biological preparation industry and obtains greater economic benefit.

At present, many experiments on cells need to be performed under conditions that maintain the activity of the cells. The biological activity of the cells can be maintained, so that not only can special biological phenomena under the active condition be observed, but also people can be helped to better understand the internal structure and the operation mode of the cells. Therefore, maintaining cell viability is of far-reaching interest.

The cytological basis in exploring human health and disease is the observation of cells, and therefore it is critical to study the cells of interest from a spatiotemporal and molecular level. Microscopic imaging is a very important tool in cell biology, which enables detailed investigation of samples in their structural environment, as well as analysis of organelles and macromolecules. It is important to select an appropriate microscopic imaging method if it is desired to sufficiently expand the research efforts of itself and obtain high quality data. The requirements of current medical research on the resolution and precision of a microscope are high, more complex research needs higher-performance experimental instruments, and in recent years, the field of biological imaging always makes research popular, and new technology which is changed day by day makes experimental methods diversified.

The traditional wide-field fluorescence microscope collects exciting light through an objective lens and collects fluorescence signals of a sample for imaging. It can be seen by illumination that although the light in the focal plane is the strongest, the sample above and below it will also be illuminated, leading to the introduction of additional phototoxicity, affecting the biological activity of the sample, and even causing cell death and interfering signals outside the imaging focal plane to enter the image, resulting in reduced image resolution and contrast. According to the method for scanning the using point of the laser scanning confocal microscope, the pinhole is introduced into the detection end, stray light outside a focal plane is filtered, the resolution, particularly the longitudinal resolution, is improved, and three-dimensional imaging can be realized. However, when the excitation light is focused, the upper and lower areas are still illuminated. Because of the point scanning imaging, in order to achieve faster speed, the time for irradiating each point by the light beam is very short, the quantum efficiency of the imaging element is very low, and stronger excitation power is needed. Photobleaching and phototoxicity are more severe than with conventional wide field fluorescence microscopes. Two-photon laser scanning microscopes can greatly reduce the damage of phototoxicity. Due to the use of near infrared laser illumination, phototoxicity to living samples is greatly reduced and deeper samples can be penetrated. However, the two-photon signal is weak, the acquisition speed is very slow, the method is not suitable for dynamic imaging of a large sample, and the cost is very high, so that the application range of the method is limited.

With the continuous development of imaging technology, the method has deep layer chromatography resolution capability, and a wide-field dynamic speckle microscopic imaging method is widely applied. The technology has the advantages of high imaging speed, high time and high spatial resolution, no need of external source marks, simple structure, low cost and the like.

The dynamic speckle microscopic imaging technology has the ability of chromatographic resolution, and a multilayer chromatographic image needs to be obtained in order to obtain the three-dimensional structure of an object to be detected, so that the focusing position of a microscope needs to be continuously adjusted, and the operation is inconvenient. The invention adjusts the position of the cell to be detected by continuously changing the light field intensity of the cell to be detected and performs imaging, and the operation is simple. After years of development of the dynamic speckle illumination wide-field fluorescence microscope, the imaging speed and resolution meet most experimental requirements, and a mode for controlling and fixing a sample is not ignored. The fixation of the sample also has great influence on imaging, and in a dynamic speckle illumination wide-field fluorescence microscopic imaging system, in order to acquire a complete three-dimensional structural image of a cell, the cell needs to be rotated or moved, so that complete information of different layers of the cell can be acquired. The most used technology of the prior art is to add a micro-displacement table to control the axial movement of cells to be detected; or moving the light sheet to realize the tomography of the cells by scanning the sample cells.

The invention relates to a speckle fluorescence microscopy method and a system based on a cell rotation active light control technology. The cells are precisely controlled by specially designed space light to rotate around a specific axis. After the cells rotate to each angle and reach a stable state, a chromatographic image of the cells is obtained by using a wide-field fluorescence microscopic imaging technology of dynamic speckle illumination. And finally reconstructing a three-dimensional structural image of the whole cell by obtaining cell chromatographic images at different angles.

Disclosure of the invention

The invention aims to provide a speckle fluorescence microscopy method and a system based on a cell rotation active light control technology, which have the advantages of high imaging speed, high time and space resolution, simple structure, no need of exogenous marking, non-invasion and the like.

In a wide field fluorescence microscopy system with dynamically changing speckle pattern illumination, when a laser beam passes through a constantly changing scatterer 5, a series of randomly changing speckle patterns are formed on the back focal plane of an apochromatic microscope objective 12, and the speckle patterns are used for illuminating a cell 23 to be measured. The fluorescence signal generated after the cell 23 to be detected is excited is divided into two sources, one is the fluorescence signal from the focal plane of the field of view of the apochromatic microscope objective 12, and the other is the background fluorescence signal from the focal plane of the field of view of the apochromatic microscope objective 12. With the change of the illumination speckle pattern, the scattered fluorescence intensity generated by the speckle illumination changes violently in the focal plane of the apochromatic microscope objective 12, but slowly at the place outside the focal plane of the field of view, and the signal characteristic is the basis for realizing tomography. A series of changed speckle patterns on a specific layer of the cell 23 to be detected are recorded by the CMOS camera 8, and a fluorescence signal of the layer can be extracted by using a special algorithm, so that the cell has a tomography function.

Wherein N is the number of images in the image sequence, I_iIs the intensity of the ith image, I_RmsIn order to acquire root mean square images of N images, namely tomography, the clear fluorescence tomography images can be obtained by taking 50-60N generally.

When a sample to be detected is irradiated by the dynamic speckle, the fluorescent marking dye in the cell is excited and emits fluorescence, and the fluorescence is collected by the detection objective lens and transmitted to the CMOS camera, so that the effect of imaging a thin layer of the cell is realized. In order to realize the fixation and the control of the cells, the invention adds the optical control system, which can realize the precise control of the cells and is mainly completed by the acousto-optic modulator 19. The optical power during pushing is slightly larger than that during braking, so as to convert the angle of the laser by the AOD, the optical power should be changed accordingly, in order to give the cell a certain time to rotate. One light path shown in fig. 2 is used for pushing the cell to rotate the cell, and after the cell rotates a certain angle, the AOD changes the deflection angle of the light, and another light path is used for pushing the cell on the other side of the cell to brake the cell. And (3) no pulsed light is input after the cell is stopped, the cell is in a static state, the period is used for cell imaging, and the process is continuously repeated after the period. After the cells are controlled to rotate once and are stabilized, the CMOS camera acquires an image of one layer of the cells once, and after the cells are rotated for a plurality of times, a structure of a plurality of layers of the cells can be obtained, as shown in fig. 4.

The dynamic speckle illumination wide-field fluorescence microscopic imaging system mainly comprises a laser light source 1; lenses 2, 3, 6, 7; a scatterer 5; a micro-displacement stage 4; apochromatic microobjective 12; a dichroic mirror 11; an optical filter 10; a test cell 23; an imaging lens 9; a CMOS camera 8. In the system, a laser beam emitted by a laser source 1 is expanded by lenses 2 and 3 and then is projected onto a scatterer 5 to form a speckle pattern, the laser beam is expanded by lenses 6 and 7, an image of the speckle pattern is formed on a focal plane behind an apochromatic microscope objective 12 after being reflected by a dichroic mirror 11, and full-field illumination is formed on a cell 23 to be measured by the apochromatic microscope objective 12. When the cell 23 to be detected rotates to a specific angle under the control of the optical field and reaches a stable state, the position of the scatterer 5 is changed by moving the micro-displacement stage 4, so that the speckle pattern projected on the cell 23 to be detected is changed. Fluorescence signals generated by excitation of different speckle patterns are collected by an apochromatic microscope objective lens 12, background noise is eliminated through a dichroic mirror 11 and an optical filter 10, and a plurality of fluorescence images are synchronously recorded through an imaging lens 9 and a CMOS camera 8. Under the condition of speckle illumination, the fluorescence signal generated by excitation near the focal plane changes most intensely, and the fluorescence tomography image near the focal plane can be extracted by utilizing a root-mean-square algorithm. The cell 23 is controlled to rotate continuously around the axis by changing the intensity distribution of the optical field, so that a three-dimensional structure fluorescence image of the whole cell 23 to be detected is obtained.

The light control system mainly comprises laser light sources 13 and 18; a mirror 22; lenses 14, 15, 20, 21; a dichroic mirror 16; an acousto-optic deflector 19; apochromatic microobjective 17. The light manipulation part is composed of capture light split by the laser 1 and deflectable light emitted by the laser 18 and controlled by the acousto-optic deflector 19, and the capture light is used for capturing cells to be detected, so that the cells are fixed at a position to facilitate imaging and rotating around a fixed axis. The laser emitted by the laser 18 enters the acousto-optic deflector 19, the acousto-optic deflector 19 can change the angle of the laser, the laser finally reaches one side of the cell through the lens to push the cell, when the cell rotates a certain angle, the light is deflected to the other direction through the action of the acousto-optic modulator 19 and reaches the other side of the cell to brake the cell, and when the cell is static, the CMOS camera 8 collects the structures of the cell at different angles again, and the three-dimensional structure of the cell is obtained through repeated times.

(IV) description of the drawings

FIG. 1 is a schematic structural diagram of a speckle fluorescence microscopy method and system based on a cell rotation active light manipulation technology.

FIG. 2 is a schematic view of a light manipulation section consisting of a fixed beam of light and an alternating laser beam to fix and manipulate cells, showing the structure of the capturing and manipulating light.

FIG. 3 is a power diagram of light for manipulating cell fixation and rotation.

Fig. 4 is a schematic view of a method of imaging a cell, in which different layers of the cell are imaged by fixing and rotating the light manipulation part of fig. 2 a plurality of times by a certain angle.

FIG. 5 is a schematic diagram of a dynamic speckle illumination wide-field fluorescence microscopy technique.

Description of reference numerals: 1-a laser light source; 2-a lens; 3-a lens; 4-micro displacement table; 5-scatterers; 6-a lens; 7-a lens; 8-CMOS camera; 9-an imaging lens; 10-an optical filter; 11-a dichroic mirror; 12-apochromatic microobjective; 13-a laser light source; 14-a lens; 15-a lens; 16-a dichroic mirror; 17-apochromatic microobjective; 18 a laser light source; 19-an acousto-optic deflector; 20-a lens; 21-a lens; 22-a mirror; 23-test cells.

(V) detailed description of the preferred embodiments

The present invention is further described in detail below with reference to examples to enable those skilled in the art to practice the invention with reference to the description.

It will be understood that terms such as "having," "including," and "comprising," as used herein, do not preclude the presence or addition of one or more other elements or groups thereof.

A speckle fluorescence microscopy method and system based on cell rotation active light control technology. The method is characterized in that: the system consists of a dynamic speckle illumination microscopic imaging system and an optical control system. It consists of laser light sources 1, 13, 18; lenses 2, 3, 6, 7, 14, 15, 20, 21; a micro-displacement stage 4; a scatterer 5; a CMOS camera 8; an imaging lens 9; an optical filter 10; dichroic mirrors 11, 16; apochromatic microobjectives 12, 17; a test cell 23; a mirror 22; an acousto-optic deflector 19. In the system, a laser beam output by a laser light source 1 is expanded by lenses 2 and 3 and forms a speckle pattern through a scatterer 5. After being expanded by the lenses 6 and 7, the light is reflected by the dichroic mirror 11, forms an image of a speckle pattern on the back focal plane of the apochromatic microscope objective 12, and forms full-field illumination on the cell 23 to be measured. The position of the scatterer 5 is adjusted by moving the micro-displacement stage 4, so that the speckle pattern projected on the cell 23 to be measured is changed. By extracting such different pattern variations, high-temporal-rate and high-spatial-rate tomographic images of the test cell 23 are obtained. After the laser output by the laser 13 is expanded by the lenses 14 and 15, the laser is reflected and coupled into the apochromatic microscope objective 17 by the dichroic mirror 16, and is focused on the cell 23 to be detected as captured light, so that the cell is stably captured and detected. The laser light output from the laser 18 is coupled into the acousto-optic deflector 19 to generate a laser beam with a certain deflection angle. Coupled into apochromatic microscope objective 17 via lenses 20, 21. By changing the modulation frequency of the acousto-optic deflector 19 alternately, the focused light beams are focused on two ends of the cell 23 to be detected alternately and are respectively used as rotating light for pushing the cell to rotate and brake light for stopping the cell to rotate, so that accurate active light control on the rotating angle of the cell is realized. When the cells rotate to an angle and reach stability, a fluorescence tomography image of an illumination area is obtained by a dynamic speckle illumination microscopy technology. Under the alternate action of the pushing light and the braking light, the cell 23 to be detected continuously rotates, and the rapid scanning of dynamic speckle illumination in the cell is realized, so that a high-spatial-resolution fluorescence tomography image of a three-dimensional structure in the cell is obtained.

In the system, a laser beam emitted by a laser light source 1 is expanded by lenses 2 and 3 and then is projected onto a scatterer 5 to form a speckle pattern, the laser beam is expanded by lenses 6 and 7, an image of the speckle pattern is formed on a focal plane behind an apochromatic microscope objective 12 after being reflected by a dichroic mirror 11, and full-field illumination is formed on a cell 23 to be measured by the apochromatic microscope objective 12. When the cell 23 to be detected rotates to a specific angle under the control of the optical field and reaches a stable state, the position of the scatterer 5 is changed by moving the micro-displacement stage 4, so that the speckle pattern projected on the cell 23 to be detected is changed. Fluorescence signals generated by excitation of different speckle patterns are collected by an apochromatic microscope objective lens 12, background noise is eliminated through a dichroic mirror 11 and an optical filter 10, and a plurality of fluorescence images are synchronously recorded through an imaging lens 9 and a CMOS camera 8. Under the condition of speckle illumination, the fluorescence signal generated by excitation near the focal plane changes most intensely, and the fluorescence tomography image near the focal plane can be extracted by utilizing a root-mean-square algorithm. The cell 23 is controlled to rotate continuously around the axis by changing the intensity distribution of the optical field, so that a three-dimensional structure fluorescence image of the whole cell 23 to be detected is obtained.

In the system, laser emitted by a laser 18 enters an acousto-optic deflector 19, the acousto-optic deflector 19 can change the angle of the laser, the laser finally reaches one side of a cell through a lens to push the cell, when the cell rotates a certain angle, light is deflected to the other direction through the action of an acousto-optic modulator 19 and reaches the other side of the cell to brake the cell, and when the cell is static, a CMOS camera 8 collects the structures of the cell at different angles again, and the three-dimensional structure of the cell is obtained through repeated operation.

The above examples are provided for the purpose of describing the invention only, and are not intended to limit the scope of the invention. The scope of the invention is defined by the appended claims. Various equivalent substitutions and modifications can be made without departing from the spirit and principles of the invention, and are intended to be within the scope of the invention.