Common-path multimodal threedimensional fluorescence and phaseimaging system
Manoj Kumar
Xiangyu Quan
Yasuhiro Awatsuji
Chaoyang Cheng
Mitsuyasu Hasebe
Yosuke Tamada
Osamu Matoba

Manoj Kumar, Xiangyu Quan, Yasuhiro Awatsuji, Chaoyang Cheng, Mitsuyasu Hasebe,
Yosuke Tamada, Osamu Matoba, “Common-path multimodal three-dimensional fluorescence andphase imaging system,” J. Biomed. Opt. 25(3), 032010 (2020), doi: 10.1117/1.JBO.25.3.032010

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Common-path multimodal three-dimensional
fluorescence and phase imaging system
Manoj Kumar,a,* Xiangyu Quan,a Yasuhiro Awatsuji,b Chaoyang Cheng,c,d
Mitsuyasu Hasebe,c,d,e Yosuke Tamada,c,e,f and Osamu Matobaa,*aKobe University, Graduate School of System Informatics, Kobe, Japan
Kyoto Institute of Technology, Faculty of Electrical Engineering and Electronics, Kyoto, Japanc
National Institute for Basic Biology, Okazaki, Japand
ERATO, JST, Okazaki, Japane
SOKENDAI (The Graduate University for Advanced Studies), School of Life Science,
Okazaki, Japanf
Utsunomiya University, School of Engineering, Utsunomiya, Japanb

Abstract. A stable multimodal system is developed by combining two common-path digitalholographic microscopes (DHMs): coherent and incoherent, for simultaneous recording andretrieval of three-dimensional (3-D) phase and 3-D fluorescence imaging (FI), respectively,of a biological specimen. The 3-D FI is realized by a single-shot common-path off-axis fluorescent DHM developed recently by our group. In addition, we accomplish, the phase imaging
by another single-shot, highly stable common-path off-axis DHM based on a beam splitter.
In this DHM configuration, a beam splitter is used to divide the incoming object beam into two
beams. One beam serves as the object beam carrying the useful information of the object understudy, whereas another beam is spatially filtered at its Fourier plane by using a pinhole andit serves as a reference beam. This DHM setup, owing to a common-path geometry, is lessvibration-sensitive and compact, having a similar field of view but with high temporal phasestability in comparison to a two-beam Mach–Zehnder-type DHM. The performance of the proposed common-path DHM and the multimodal system is verified by conducting various experiments on fluorescent microspheres and fluorescent protein-labeled living cells of the moss
Physcomitrella patens. Moreover, the potential capability of the proposed multimodal systemfor 3-D live fluorescence and phase imaging of the fluorescent beads is also demonstrated. The
obtained experimental results corroborate the feasibility of the proposed multimodal system andindicate its potential applications for the analysis of functional and structural behaviors of abiological specimen and enhancement of the understanding of physiological mechanisms andvarious biological diseases. © The Authors. Published by SPIE under a Creative Commons Attribution
4.0 Unported License. Distribution or reproduction of this work in whole or in part requires full attributionof the original publication, including its DOI. [DOI: 10.1117/1.JBO.25.3.032010]

Keywords: multimodal; common-path configuration; digital holography; three-dimensional
fluorescence imaging; three-dimensional phase imaging.
Paper 190206SSRR received Jun. 22, 2019; accepted for publication Jan. 14, 2020; published
online Feb. 6, 2020.

1 Introduction
Various multimodal imaging systems with different configurations and for different purposes
have been recently developed because these systems enable one to analyze the functional andstructural behaviors of a biological specimen at a single examination and, therefore, facilitate abetter understanding of the behavior of molecular, cellular, and disease biology.1–9 The multimodal systems were developed for simultaneous fluorescence and quantitative phase imaging by
incorporating the two-dimensional (2-D) epifluorescence microscopy with the diffraction phasemicroscopy by Park et al.1 and with the Mach–Zehnder-type digital holographic microscopy(DHM) by Pavillon et al.2 and Quan et al.3 A multimodal approach that incorporates confocal*Address all correspondence to Manoj Kumar, E-mail: manojklakra@gmail.com; Osamu Matoba, E-mail: matoba@kobe-u.ac.jp

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Raman, confocal reflectance, and quantitative phase microscopy4 has demonstrated the potential
for retrieving the molecular specific and morphological information. Optical diffraction tomography (ODT) is another technique to reconstruct the three-dimensional (3-D) quantitative phaseimaging from the recorded multiple 2-D holograms. This technique was exploited with the optofluidic rotation of suspended cells by Schürmann et al.5 to measure the 3-D correlated refractive
index and fluorescence data for a quantitative interpretation of the nuclear refractive index.
Further, a multimodal system was developed by integrating the ODT and 3-D structured illumination microscopy by Shin et al.6 for the measurement of 3-D refractive index and fluorescence
distribution of live cells. The structured illumination microscopy-based multimodal system7 isdemonstrated for 3-D subdiffraction multimodal imaging of both quantitative phase and fluorescence. Chowdhury et al.8 and Nygate et al.9 proposed the multimodal systems based on theprinciple of off-axis holographic multiplexing to obtain the quantitative phase and fluorescenceimaging (FI) of the biological cells using a single camera. These systems,8,9 owing to the use of
single camera for recording both the phase hologram and the fluorescence image, are free fromimage registration issues.
A multimodal system combining the DHM with the FI may address several critical concernsof biology. The DHM system concedes the structural information by exploiting the optical pathlength shifts through the biological specimen, and the FI reveals the functional details of thespecific molecules of interest in the specimen. Thus, a multimodal system comprising a DHM
and an FI provides two distinct information of the specimen simultaneously through a single
examination. Our group previously proposed a multimodal system in which phase imaging isrealized by Mach–Zehnder-type DHM.3 However, the phase measurement is less stable due tothe two-arm configuration of DHM. Furthermore, it is not easy to make it compact in the opticalsetup. For the time-lapse measurement of live cell imaging in biological applications, in thispaper, we propose a single-shot common-path off-axis DHM based on a beam splitter. Then,
we developed a multimodal system comprising the proposed DHM and another single-shotcommon-path off-axis fluorescent digital holographic microscope (FDHM), which was recently
developed by our group.10 The proposed multimodal system enables one to provide a stablesystem of 3-D phase and 3-D FI of a biological specimen in a common hybrid platform.
The 3-D fluorescence microscopy has received significant interest since it is becoming a
crucial tool in molecular and cellular biology to understand the dynamics of specific molecules,
organelles, and structures in a biological sample. Several techniques have been used in highresolution 3-D FI such as confocal,11 two-photon,12 or light sheet microscopy.13 However, thesemethods are inherently limited in terms of speed or volume, because they all involve scanning.
Light field microscopy14,15 achieves single-shot 3-D capture but sacrifices resolution. Coded
aperture microscopy16–19 provides high-resolution imaging with single-shot capture, but it
requires an extremely sparse sample. On the other hand, continuous progress in the field of
incoherent holography opens new possibilities of 3-D FI. Digital holography can be adopted
to fluorescence microscopy for recording and retrieving the 3-D information of incoherent
fluorescent objects.20–24 Our group reported a fluorescent digital holographic system by using adual-focusing lens with a diffraction grating.23 In this configuration, the 0-th order unmodulated
light is cut out and the interference occurs between the two first orders. However, the major
limitation of this configuration is that the utilization factor of the light of the first orders becomesvery low. The aforementioned limitation of the incoherent digital holographic system is resolved
by proposing a modified configuration of the common-path off-axis incoherent digital holographic system10 for the 3-D FI of biological samples.
The 3-D phase imaging techniques provide morphological information about the structureand dynamics of the transparent specimen.25,26 An off-axis DHM is an ideal tool for studying
various biological parameters, including 3-D imaging and parameter extraction, and for themeasurement of 3-D profiling and tracking,27 refractive index,28 spectral dispersion,29 dry mass
localization,30 and optimum focus determinations.31 Moreover, the technique has been employed
for monitoring cell growth, characterizing cellular motility, and investigating the subcellularmotions of living cells.32 The DHM systems usually employ the two-beam Mach–Zehnder interferometric configuration for quantifying the cellular and subcellular structures. In this geometry,
two beams, following separate paths and passing through separate sets of optical components,
are used to form the interference pattern on the image sensor. These separate paths for the object
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and reference beams may lead to lower spatial and temporal phase stability,33 limitation on measuring small cell thickness fluctuation,34 and complex and costly system setup. These complications can be overcome by employing a common-path configuration.35–43 In common-path
DHM systems, the object and reference beams follow approximately the same path and, therefore, make the systems less prone to environmental vibrations/perturbations. However, in such
systems, both beams carry identical information and have enormous chances of overlapping at
the image sensor. To overcome this problem, self-referencing techniques, in which the reference
beam consists of only a small portion of the object beam, which does not carry object information, are proposed.35,38,44 Also, approaches to employing a pinhole to one of the beams
at its Fourier plane in order to erase all the object information in one beam and it is serving asa reference beam, have been reported.37,45,46
In this paper, we propose the common-path off-axis configuration by employing a cube beam
splitter, which divides the incoming object beam into two beams, and a pinhole is used to filter
spatially one of the beams at its Fourier plane, serving a reference beam. The beam splitter-based
common-path DHM systems have been reported previously,44,47 where the system44 is based on
the self-referencing method, and in Ref. 47, two π phase-shifted holograms are recorded andthese two holograms are processed by using an algorithm based on the subtraction of the two
fields of view (FOVs) in order to eliminate the direct current (DC) term. These approaches arefacing two major problems: (1) there is a possibility of overlapping of the object information at
the image plane and may lead to generating twin images of the object and (2) if the first problem
is overcome by utilizing only one half of the incident beam for object visualization, and anotherhalf is used for the reference beam, then, this process reduces the overall FOVs of the system byhalf. Moreover, in Ref. 47, since two holograms are recorded simultaneously by utilizing the halfof the sensor area for the transmitted object beam from the beam splitter and another half area by
the reflected object beam, which is π phase-shifted by the transmitted beam, it reduces the FOVof the system. Therefore, these problems can be overcome by spatially filtering one of the beams
at its Fourier plane using a pinhole, obtained after passing through the beam splitter. Further, toretrieve the phase distribution in coherent DHM, we adopted a single-shot holographic methodby utilizing principal component analysis (PCA)-based phase aberration compensation
method,48 which enables the system for the investigation of fast-dynamic events. Therefore, onlya single hologram is recorded in the presence of the object and processed to obtain the phase
information. Further, both the proposed, coherent and incoherent, DHMs are integrated todevelop a new configuration of the multimodal system, which could, indeed, have the capability
to provide high-contrast functional imaging along with structural details of the biological specimen on a single platform. It is possible to extract important intrinsic biophysical parameters of
the biological specimen from the proposed multimodal system.

2 Methodology
2.1 Three-Dimensional Fluorescence Imaging System
The multimodal system comprises two DHMs for 3-D fluorescence and phase imaging.
Figure 1(a) shows the schematic of the common-path off-axis fluorescent digital holographic
system for 3-D FI recently developed by our group.10 This fluorescent microscope is accomplishedby embedding a focusing lens with a diffraction grating, as shown in Fig. 1(b), onto a phase-mode
spatial light modulator (SLM). This pattern allows splitting the incident fluorescent light fromthe object into two light waves with slightly different propagation directions in order to achieve
off-axis interference. Figure 1(c) shows the focused image of the fluorescent beads of size
∼10.4 μm when no pattern is displayed on the SLM, and Fig. 1(d) depicts the two fluorescentlights: one unmodulated and another modulated by the pattern [shown in Fig. 1(b)] displayed on
the SLM. These two wavefronts interfere at the image sensor plane and form a fluorescent digitalhologram, as shown in Fig. 1(e), by the help of a linear polarizer, when the sample (fluorescentbeads) is moved in the () z direction by a small distance, say −80 μm, as in this case.
If the radii of two wavefronts are denoted as rm and ru by setting the focal length of f SLM ¼
f 0 and infinity, respectively, the reconstructed distance from the image sensor plane is describedas zh ¼ rm ru ∕rm − ru . From the recorded fluorescence hologram, the 3-D object information can
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Fig. 1 Incoherent digital holographic system for 3-D FI. (a) Schematic representation of thecommon-path off-axis digital holographic setup. (b) The phase pattern displayed on the SLM,(c) focused image of the fluorescent beads, and an enlarged view of one bead is also shown sideways, (d) image obtained when the pattern shown in Fig. 1(b) displayed on the SLM, and an
enlarged view of one bead is also shown sideways, (e) recorded fluorescent hologram obtainedby moving the sample in the z direction by −80 μm, (f) reconstructed image of the fluorescentbeads, and (g) normalized intensity plot for the recorded and reconstructed selected fluorescencebeads across the line AB, marked in (f).

be reconstructed by using the Fresnel propagation algorithm. Figure 1(f) shows the reconstructed
image of the fluorescent beads, and the normalized intensity plot is shown in Fig. 1(g) for therecorded and reconstructed selected fluorescence beads across the line AB, marked in Fig. 1(f).
The signal-to-noise ratio (SNR) for the recorded image (SNR ¼ 30.4445) and the reconstructed
image (SNR ¼ 29.8611) are almost the same. This shows the good performance of the system.

2.2 Three-Dimensional Phase Imaging System
The phase imaging is accomplished by a single-shot common-path off-axis DHM using a cube
beam splitter. Figure 2 shows the schematic of the experimental setup of the proposed beam
splitter-based common-path DHM. The collimated laser light (He-Ne laser, λ ¼ 632.8 nm)
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Fig. 2 Schematic representation of the proposed common-path off-axis DHM setup. BS, Beamsplitter; SF, spatial filter; L1 to L4, lenses.

transilluminates the sample mounted on a motorized translational stage. The light transmitted
through the sample is collected by a microscopic objective lens [40× magnification, numericalaperture (NA) = 0.65] and collimated by the lens L2 (focal length ¼ 100 mm). The collimatedlight is focused by L3 (focal length ¼ 150 mm) and allowed to pass through a cube beam
splitter, BS, which divides the incident object beam into two beams. Since both the beams
carry object information, their interference on the image sensor may bear the overlapping issue.
To avoid the overlapping, one beam is spatially filtered at the Fourier plane by using a pinhole(50 μm, diameter), mounted on a 3-D translational stage. The pinhole acts as a spatial filter andis positioned in such a way that it blocks the higher frequency components and allows only the
DC component of the beam to pass and converted into a spherical reference beam, in which all
the object information is erased. After passing through a lens L4, the reference wave becomes atilted plane wave. This is good for ideal off-axis holography. The orientation of the beam splitter
is made in such a way that the two divided beams have sufficient lateral separation. The interference of the object beam and the reference beam is recorded by a CMOS camera (Sony Pregius
IMX 249, sensor format: 1920 × 1200 pixels, pixel size of 5.86 μm).

3 Experiments and Results
3.1 Common-Path Digital Holographic MicroscopyFirst, the performance of the single-shot common-path off-axis DHM is demonstrated. The proposed system, owing to its common-path configuration, shows high temporal stability comparedto the conventional two-beam configuration of DHMs. To measure the temporal stability of thesystem, a series of holograms, without the presence of the object, are recorded at the rate of 40
frames per second, for 100 s without any vibration isolation. Then, the phase distributions arereconstructed numerically for all the 4000 holograms, and the phase difference distributions arecalculated for all the frames by comparing the reconstructed phase distributions to that of the firstrecorded hologram. The standard deviation of the phase difference for 10,000 random pixel
points in the same area of every phase difference distribution is calculated. Figure 3 shows thehistogram of the standard deviation of the proposed setup indicating that a mean fluctuation is0.0098 rad. On the other hand, the mean variation of phase is ∼0.2 rad for the traditional twobeam (e.g., Mach–Zehnder) interferometer.3 Therefore, the proposed setup shows improved
temporal stability in comparison to its counterparts.
Then the imaging capability of the proposed DHM is demonstrated by performing several
experiments on objects, such as a United States Air Force (USAF) resolution chart, microspherebeads, and 3-D biological sample. Only a single hologram, in the presence of the object, isJournal of Biomedical Optics

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Fig. 3 Temporal stability of the proposed setup. Histogram of the standard deviation between
reconstructed phase distributions.

recorded and is further used to extract the object intensity and phase distribution. Figures 4–6
show the experimental results on the USAF resolution chart. Figures 4(a) and 4(b) show therecorded hologram and the enlarged view of the selected region of the recorded hologram,respectively. Figures 4(c)–4(e) show the Fourier spectrum of the recorded hologram, filteredþ1 order, and þ1 order centered, respectively. A spherical phase curvature is introduced in theobject wave after passing through the microscopic objective and that must be compensated. The
numerical phase aberration compensation method based on the PCA is utilized in order to accurately recover the phase information.48 This method is based on the decomposition of the phase
map into a set of values of uncorrelated variables. These variables are called principal components and from the first principal component the aberration term is retrieved. The first principal
component of the exponential term of the filtered hologram is estimated by using a singular value
decomposition. Then the linear and the quadratic coefficients can be identified using leastsquares fitting and their conjugate is multiplied with the filtered hologram in order to obtain
aberration-free phase distribution. These steps involved extracting aberration-free phase distribution using the PCA method are demonstrated in Figs. 5(a)–5(c). Figure 5(a) shows the raw

Fig. 4 Common-path off-axis DHM results of USAF resolution chart: (a) recorded digital hologram,(b) the enlarged view of the selected region showing the fringes, (c) Fourier spectrum of thehologram, (d) filtered þ1 order, and (e) þ1 order centered (contrast adjusted).
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Fig. 5 (a) Raw sampled phase, (b) conjugate phase extracted, and (c) compensated spectrum.

Fig. 6 (a) The reconstructed intensity image corresponding to the recorded hologram shown in
Fig. 4(a) and (b) unwrapped phase map.

Fig. 7 Common-path off-axis DHM experimental results of living plant cells of protonemata, thehypha-like structure of Physcomitrella: (a) digital hologram and (b)–(e) some of the retrieved
wrapped phase maps at different in-focus planes (the in-focus region is indicated by the blue
arrows). (Video 1, mp4, 6442 KB [URL: https://doi.org/10.1117/1.JBO.25.3.032010.1]).

sampled phase distribution carrying the phase aberration. Figure 5(b) shows the obtained phaseaberration distribution using the PCA method. The conjugate of this aberration term is multipliedwith the sampled hologram [Fig. 5(a)] and results in the modification of the original region of thespectrum. The new modified spectrum is shown in Fig. 5(c). Then the numerical reconstruction
process is performed to obtain the aberration-free phase distribution. Figures 6(a) and 6(b) show
the retrieved intensity and phase distribution corresponding to the recorded hologram shown in
Fig. 4(a). The PCA-based phase aberration compensation method does not require prior knowledge either of the object or of the setup and shows efficient performance with promising results.48
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In the next experiments, the capability of the proposed DHM system is demonstrated on
a 3-D biological sample, the living plant cells. As the observation target, we used the moss
Physcomitrella patens (Physcomitrella).49 In Physcomitrella, the genome is sequenced,50 thecell identity is clear,49 and the body size is compact, all of which make Physcomitrella oneof the model organisms for modern biology. Therefore, Physcomitrella is suitable as the observation target using the proposed system. Figure 7 shows the experimental results of the proposed
DHM on the living plant cells of protonemata, the hypha-like structure of Physcomitrella. The
recorded hologram of the 3-D sample is shown in Figs. 7(a) and Figs. 7(b)–7(e) show the
wrapped phase maps of the four different in-focus planes obtained from the recorded hologram,where blue arrows indicate the in-focus regions. Video 1 depicts the movie of the recovered
in-focus phase imaging from one plane [corresponding to the in-focus plane of Fig. 7(b)] to
another [to the in-focus plane of Fig. 7(e)].

3.2 Multimodal System
In this section, we demonstrate the performance of the multimodal imaging system developed by
combining the common-path off-axis DHM and the common-path off-axis FDHM, in order toretrieve simultaneously both the 3-D phase and 3-D fluorescence images. Figure 8 shows theschematic of the proposed multimodal system. Here, we use two image sensors for fluorescenceand phase imaging. For the applications of biological samples, the optical power difference is
too much to record both holograms by a single image sensor because the fluorescence light is
too weak to avoid phototoxicity. However, two cameras create an image registration problem.
In other applications, such as material sciences, a single image sensor is ideal for fabricating an
integrated multimodal system. The performance of the proposed multimodal system is demonstrated by performing experiments on microsphere fluorescent beads and fluorescent proteinlabeled living plant cells. A blue laser (wavelength, λ ¼ 473 nm) is used as a light source forthe incoherent DHM system, to excite the fluorescent object used in the study. The laser beamis spatially filtered, collimated, and then reflected from a dichroic mirror (DM1, Thorlabs,
DMLP490R) and entered into the objective lens (40× magnification, NA ¼ 0.65). The incident

Fig. 8 Optical schematic of the proposed multimodal system for the measurement of the 3-D
fluorescence and the 3-D phase of the specimen.
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March 2020 • Vol. 25(3)Kumar et al.: Common-path multimodal three-dimensional fluorescence and phase imaging systemlaser light excites the fluorescent object. First, an experiment is performed on microsphere fluorescent beads of size ∼10.4 μm. The beads, mounted on the 3-D translational stage, are excitedby the collimated laser beam in an epi-illumination configuration. The fluorescent beads emit theyellow fluorescence with wavelengths ranging from 550 to 600 nm. This fluorescent light travels
back through the objective lens, transmits through DM1, and is reflected from another dichroic
mirror, DM2 (Thorlabs, DMLP605R). The Fourier transform of the object beam located at thefocused plane of the objective lens is projected onto the plane of the phase-mode SLM (Holoeye
pluto, 1920 × 1080 pixels, 8 μm pixel pitch, phase-only modulation) by a 4f relay system(L4 → L5). Here, the back focal plane of the objective lens is imaged on the phase-mode SLM.
A lens function with focal length f SLM ¼ 800 mm and a diffraction grating function with grating
period dh ¼ 300 μm were displayed onto the SLM, which generates two distinct wavefronts at
respective angles of the incident beam. These two wavefronts are then imaged by a tube lens
(focal length ¼ 200 mm) and allowed to interfere on to the faceplate of the electron multiplying
charge-coupled device (EMCCD) sensor (Andor iXon 888, sensor format: 1024 × 1024 pixels,
pixel size of 13 μm, sensor diagonal of 18.8 mm) and hence form a fluorescent digital hologram.
A linear polarizer is placed before the EMCCD sensor in order to allow the interference ofFig. 9 Experimental results of the multimodal system of microsphere beads. Phase imaging
results: (a) phase hologram, (b) wrapped phase distribution, (c) 2-D unwrapped phase map, and(d) 3-D unwrapped phase distribution of a selected bead. FI results: (e) original focused image ofthe fluorescent beads, (f) fluorescent digital hologram obtained by moving the beads by 80 μm
along the z direction, and (g) reconstructed image of the fluorescent beads.
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two beams. The volume size of the 3-D fluorescence system we demonstrated in the experiments
is 330 × 330 × 100 μm3 . The axial size can be more extended. The axial measurable size will be
determined by setting the required resolution to be reconstructed.
The proposed common-path off-axis DHM system for phase imaging uses a He-Ne laser(λ ¼ 632.8 nm) to transilluminate the microsphere fluorescent beads mounted on the translational stage. The collimated beam illuminates the microsphere beads and is subsequently magnified by the microscope objective and collimated using the lens L4. The object beam passes
through both the DMs and again focused by using the lens L6. This object beam is divided into
two beams by using the beam splitter, BS, in which one beam behaves as an object beam carrying
the object information and the other beam is spatially filtered at its Fourier plane by using
a pinhole of size 50 μm and serves the reference beam. The interference of the reference andobject beams is recorded by a CMOS camera (Sony Pregius IMX 249, sensor format:

Fig. 10 Experimental results of the multimodal system of living protonema cells of Physcomitrella.
FI results: (a)–(c) original focused images of the nuclei (670 × 1024 pixels). The yellow arrow, inthese figures, indicates the focused nuclei, (d) fluorescent digital hologram, and (e)–(g) reconstructed focused images of the nuclei correspond to Figs. (a)–(c). Phase imaging results: (h) phase
hologram and (i)–(k) 2-D unwrapped phase maps corresponding to three focused planes.
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1920 × 1200 pixels, pixel size of 5.86 μm). The volume size of the fabricated phase imaging
system is 280 × 176 × 80 μm3 . The axial size can also be more extended. The axial measurable
size will be determined by setting the required resolution to be reconstructed.
Figure 9 shows the experimental results of the proposed multimodal system on microsphere
fluorescent beads of size ∼10 μm. Figure 9(a) shows the phase hologram recorded by commonpath off-axis DHM. From this single-phase hologram, the phase information is retrieved by the
PCA-based phase aberration compensation method. Figures 9(b) and 9(c) show the retrieved
wrapped and 2-D unwrapped phase maps, respectively, of the fluorescence beads. The 3-D phase
distribution of a selected bead is shown in Fig. 9(d). Concurrently, the fluorescent beads areimaged by FDHM. Figure 9(e) shows the focused image of the microsphere fluorescent beads.
Then, the stage is moved in the z direction by 80 μm, and a fluorescent digital hologram,as shown in Fig. 9(f), is recorded. The fluorescent hologram is recorded by projecting a lensfunction and a diffraction grating function on to the SLM. A bandpass filter centered at 575 
12.5 nm was placed in front of an EMCCD sensor in order to improve the fringe visibility of
the holograms. Figure 9(g) shows the reconstructed image of the fluorescent beads retrieved
from the recorded digital fluorescent hologram by the Fresnel propagation algorithm at thereconstruction distance of 1009 mm.
In the next experiment, we experimentally demonstrate the 3-D fluorescence and 3-D phaseimaging capability of the proposed multimodal system on living plant cells of Physcomitrella,
where the “Citrine” yellow fluorescent protein gene (YFP)51 was inserted into a histone H3.3
locus (Pp3c18_1448150) (see Fig. S1 and Supplementary text in the Supplementary Material,
for more details), resulting in strong expression of H3.3-YFP in the nuclei.
Figures 10(a)–10(c) show the various focused fluorescence images of the nuclei of the living
plant cells distributed in the 3-D space. The yellow arrow, in these figures, indicates the focused
nuclei. The focused plane corresponding to Fig. 10(c) is moved by 60 μm in the z direction and afluorescent digital hologram is recorded, as shown in Fig. 10(d), by projecting a lens function(with a focal length of 800 mm) and a diffraction grating function (with a grating period of
300 μm) on to the SLM. Figures 10(e)–10(g) show the reconstructed focused images corresponding to Figs. 10(a)–10(c), obtained at 660, 825, and 1030 mm, which correspond to 60,
70, and 80 μm, respectively, in the object space. The phase imaging results of the same plant
cells are shown in Figs. 10(h)–10(k). Figure 10(h) shows the recorded phase hologram, andthe unwrapped phase maps at three different focal planes are shown in Figs. 10(i)–10(k).
Chloroplasts, which strongly delay the phase52 and thus appear as dark spots in Figs. 10(i)–10(k),are clearly imaged near the focal plane. Taken together, the proposed multimodal approach canretrieve the 3-D structure of the cells as well as the 3-D position of the fluorescent protein-labeled
nuclei in living plant cells. These results show the high potential of the proposed system toobserve the 3-D behavior of living cells in a single-shot measurement.
Further, the 3-D live fluorescence and phase imaging of the moving fluorescent beads in a
volume is also demonstrated by the proposed multimodal system. Figures 11(a) and 11(b) show
the retrieved unwrapped phase and reconstructed fluorescence image of the moving bead,Fig. 11 3-D live phase and FI results: (a) unwrapped phase map and (b) fluorescence image of themoving fluorescent bead at t ¼ 1.21 s. Also, see Video 2 (mp4, 5984 KB [URL: https://doi.org/10.1117/1.JBO.25.3.032010.2]) (retrieved unwrapped phase distribution) and Video 3 (mp4, 75 KB[URL: https://doi.org/10.1117/1.JBO.25.3.032010.3]) (reconstructed fluorescence image).
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respectively, at a time instant (t ¼ 1.21 s), obtained from the digital phase and fluorescenceholograms recorded by the multimodal system. The movie of the retrieved unwrapped phaseof the moving microsphere bead is shown in Video 2, whereas the movie of the reconstructed
fluorescence images of the same bead is shown in Video 3.

4 Conclusion
First, a single-shot common-path off-axis coherent DHM based on a beam splitter is proposed.
The common-path DHM is simple, compact, less vibration-sensitive, and provides high temporalphase stability of ∼0.0098 rad. Several experiments were performed in order to verify theimaging capability of the proposed highly stable DHM. Then, a new configuration of the multimodal system, by incorporating the proposed DHM in a combination of a single-shot commonpath off-axis fluorescent digital holographic system, is demonstrated. The feasibility of the
proposed multimodal system is exhibited by performing several experiments on fluorescentbeads and living plant cells. The 3-D live fluorescence and phase imaging of the fluorescentbeads is also demonstrated by the multimodal system efficiently. The experimental imaging
results obtained by the proposed multimodal system corroborate the imaging capability of thesystem. The proposed multimodal system could be beneficial for the simultaneous measurementof the molecular-specific quantitative analysis and specific localized regions of the sample.
Taken together, the system could be utilized for the comprehensive analysis of the living biological materials with specific molecular and biophysical dynamics, and physiological andpathological processes at a single platform. For example, the imaging of the dynamic phenomena, including cytoskeleton dynamics in the whole cells,53 neuronal activation in the brain andnerves,54 and morphogenetic flow during embryogenesis,55 could be studied. Therefore, such
multimodality imaging systems could find an important role in a deeper understanding ofcellular and developmental biology, monitoring of disease progression, and helpful in theirimproved diagnosis.

Disclosures
The authors declare that there are no conflicts of interest related to this article.

Acknowledgments
Japan Society for the Promotion of Science KAKENHI (Nos. 18H03888, 17F17370, 17H03703,
and 18H04790), JST Core Research for Evolutional Science and Technology Grant No.
JPMJCR1755, and ERATO, JST, Japan.

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Manoj Kumar is the JSPS postdoctoral research fellow at the Department of System
Informatics at Kobe University, Japan. He received his PhD in optical engineering fromthe Indian Institute of Technology Delhi, New Delhi, in 2016. His research interests include
3D imaging, 3D fluorescence microscopy, digital holography, biomedical optics, and speckle
metrology. He is a member of the Optical Society of America (OSA).
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Xiangyu Quan is an assistant professor at the Department of System Informatics at Kobe
University, Japan. She received her BS degree from Beijing Information Science and Technology
University in China and received her ME, DE degrees from Kobe University in 2015 and 2017,
respectively. Her research interests include quantitative phase imaging microscopy, 3D fluorescence microscopy, and optogenetic light stimulation tools by digital holographic methods.
She is a member of OSA and SPIE.
Yasuhiro Awatsuji received his BE, ME and DE degrees from Osaka University, in 1992, 1994
and 1997, respectively. He was a research associate from 1997 to 2005, and an associate professor from 2005 to 2014 at Kyoto Institute of Technology (KIT). He has been a professor at KIT
since 2014. His research interests are in the area of information optics with emphasis on holography. He is a senior member of SPIE and OSA.
Chaoyang Cheng is currently working at Hitachi High-Tech Corporation, Japan, as a senior
engineer. He received his PhD from the University of Tokyo in 2002. He was working on plantdevelopment using the moss Physcomitrella patens during 2006–2012. His research interest is
on bioinformatics, genomics, and epigenetics.
Mitsuyasu Hasebe: Biography is not available.
Yosuke Tamada is an associate professor at Utsunomiya University in Japan. He received his
PhD in life science in 2005 from Kyoto University. He was a postdoctoral researcher at the
University of Wisconsin-Madison until 2009 and an assistant professor at National Institute for
Basic Biology in Japan until 2019. His current research interests include live-cell imaging, optical cell manipulation, and developmental biology using plants. He is a member of the OpticalSociety of Japan.
Osamu Matoba is the professor at the Graduate School of Systems Science, Kobe University.
He received his PhD in applied physics from Osaka University. His research interests include
multimodal 3D imaging using digital holography, transport of intensity equation, light field andoptical sound field imaging, imaging through scattering tissue, and 3D display. He is a fellow of
OSA and SPIE.

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