Fig. 1. Several main mechanisms for object- and reference-beam interference under different illumination conditions. (a) Coherent illumination; (b) partially coherent illumination; (c) spatial incoherent illumination, where CPM is the computer-generated phase mask for beam dividing

Fig. 2. Optical path structure of conventional off－axis digital holographic microscopy system^[2]

Fig. 3. Optical path of common－path off－axis digital holographic microscopy system^[23]

Fig. 4. Reconstructed red blood cells (RBCs) phase images^[51]. (a) Reconstructed phase image of stomatocyte; (b) reconstructed phase image of discocyte; (c) reconstructed phase image of stomatocyte after processing by watershed segmentation algorithm; (d) reconstructed phase image of discocyte after processing by watershed segmentation algorithm; (e) phase image of individual RBC obtained after segmentation; (f)(g)(h) images obtained by further segmentation of phase image of individual RBC with labeled watershed segmentation algorithm

Fig. 5. Monitoring of neural cell dynamics using digital holographic phase contrast microscopy^[52]. (a) Quantitative phase contrast image of a patched mouse cortical neuron; (b) local excitation on the neuron triggered a strong transient decrease of phase signal

Fig. 6. In-focused reconstructed images at different depth-planes^[55]. (a) 0.960 mm; (b) 0.995 mm; (c) 3.268 mm; (d) 12.010 mm; (e) 2.090 mm; (f) 8.620 mm; (g) 1.050 mm; (h) 3.039mm; (i) 4.440 mm

Fig. 7. Large field-of-view and high resolution microscopy imaging of biological samples based on lens-free coaxial digital holographic system^[68]. (a) Full field-of-view lens-free amplitude image of invasive ductal carcinoma of human breast; (b) zoomed-in regions outlined by the yellow squares in Fig. (a); (c) traditional microscopy imaging; (d) holograms

Fig. 8. Scheme of optical path and basic principle of parallel phase shifting digital holography^[77]. (a) Optical path; (b) details of spatial-multiplexed parallel polarizing component that mounted in front of image sensor; (c) in the recorded hologram, different phase shifting values are assigned to different pixels

Fig. 9. Coaxial digital holographic three-dimensional tomographic imaging realized based on compressive sensing algorithm^[82]. (a) Recorded hologram; (b)(c) images of 3D object at two different axial planes; (d) compressive sensing reconstructed images at different reconstruction distances

Fig. 10. Schematic of point diffraction interferometer based interference microscopic imaging system^[22]. (a) Schematic of optical path; (b) quantitative phase contrast imaging results of red blood cells

Fig. 11. Quantitative phase-contrast images^[95]. (a) Quantitative phase-contrast image of stripy sarcomere captured by digital holographic microscopy system with coherent light; (b) quantitative phase-contrast image of stripy sarcomere captured by digital holographic microscopy system with low coherence ultrashort pulse laser; (c) two-dimensional height profiles along the red and blue lines in (a) and (b)

Fig. 12. Schematic of frequency domain OCT system^[96]

Fig. 13. Imaging results of retina using frequency domain OCT system^[97]

Fig. 14. Example of a bronchial cross section from a chronic obstructive pulmonary disease sample^[99] (scale bars: 0.5 mm). (a) Histology image; (b) attenuation coefficient shown on a logarithmic scale; (c) OAxU, displayed from 0 to 1; (d) relative optic axis orientation, displayed from 0°－180°

Fig. 15. Optical path of FINCH three-dimensional fluorescence microscopy system and three-dimensional reconstructed images of pollen. (a) Optical path^[13]; (b) three-dimensional reconstructed images^[120]

Fig. 16. Three-dimensional tomographic imaging using compressive FINCH^[129]

Fig. 17. Imaging results of computational adaptive optics three-dimensional fluorescence microscopy^[134]. (a)(d) Wide-field fluorescence microscopic imaging results in a system with optical aberration; (b)(e) FINCH reconstructed images obtained by using conventional diffraction propagation algorithm; (c)(f) computational adaptive optic (AO) corrected images; (g) reconstructed images of microspheres without (upper row ) and with (lower row) computational AO correction, scale bar represents 880 nm

Fig. 18. Super resolution fluorescence self-interference holographic imaging based on birefringence device^[14]. (a)(c) Wide-field microscopic images of Golgi apparatus; (b)(d) super resolved holographic reconstructed images of Golgi apparatus at same numerical aperture

Fig. 19. Wide-field/confocal dual-mode fluorescence self-interference super resolution imaging^[130]. (i) Wide-field and self-interference FINCH super resolved images of fluorescence beads; (ii) microtubule obtained by confocal microscopy and confocal self-interference holographic super resolved microscopy CINCH

Fig. 20. Schematic of SELFI fluorescence self-interference three-dimensional super resolution microscopy^[10]

Fig. 21. SELFI super resolved imaging of thick biological sample^[10]

Fig. 22. Three-dimension localization based on self-interference digital holography^[141]. (a) Scheme of imaging principle；(b) hologram of a single fluorescent microsphere; (c) localization results plotted in three dimensions