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Holography

Holography is a technique that uses interference patterns of light waves to create three-dimensional images of objects.
It involves recording the wavefronts of light reflected from an object and then reconstructing the image by illuminating the recorded pattern with a coherent light source.
Holography has a wide range of applications in fields such as imaging, data storage, and optical communication.
Researchers can use PubCompare.ai to easily locate relevant protocols from literature, pre-prints, and patents, and identify the best methods and products for their holography research needs, ensuring seamless and efficient experimentation on this important techology.

Most cited protocols related to «Holography»

1
Holographic Microscope for Targeted Photolysis
The holographic microscope (Fig. 1a) was mounted around a commercial epi-fluorescence upright microscope (Olympus BX50WI). As a source for uncaging laser we used a 405nm diode laser (CUBE 405−50, Coherent).
The output beam was expanded (25x) to match the input window of a PALM-SLM (PPM X8267, Hamamatsu) which operates in reflection mode. A 4f telescope (L1 = 750mm, L2 = 300mm) was used to image via a dichroic mirror (DM) (Chroma Technology 425DCXR) the plane of the SLM to the rear aperture of the objective (LUMPLFL60XW/IR). The main source of power loss with an SLM device is related to the portion of un-diffracted light that forms an unwanted central spot (zero order) in the excitation field and to the light diffracted into higher orders (about 40% in total). The diffracted beam was spatially displaced from the zero order spot by introducing a phase grating in the hologram. The zero order spot, the higher orders and the ghost image were eliminated by placing a beam blocker and a diaphragm in the intermediate Fourier plane. This reduced the excitation field to a square of approximately 50×50µm2 (link). Alexa 594 was excited with a 75-W Xenon arc source coupled to a monochromator (Optoscan, Cairn Research) (centre-wavelength at 540nm, slit width 30nm) and imaged using an emission filter Chroma Technology HQ 600/40M. The laser intensity and duration were controlled using a 1MHz Digital-to-Analog Converter (DAC) (National Instruments 6713), whose output clock was linked to the clock of the Analog-to-Digital Converter (ADC), in order to synchronize the illumination pulse and voltage-clamp acquisition. Sample fluorescence was captured on a CCD camera (CoolSNAP HQ2, Roper Scientific), at the upper port of the microscope. For the experiments on cerebellum slices a similar setup was integrated into a modified photolysis system (Prairie Technologies, WI, USA) on an upright microscope (Nikon) equipped with a 100x water immersion objective (Nikon, Plan 1.1 NA) and a 405 nm diode laser (Deep Star, Omicron, Germany). For a description of preparation of brain slices, recording conditions and data analysis see Supplementary Method online.
Lutz C., Otis T.S., DeSars V., Charpak S., DiGregorio D.A, & Emiliani V. (2008). Holographic photolysis of caged neurotransmitters. Nature methods, 5(9), 821-827.
Publication 2008
Alexa594 Arecaceae Brain Cerebellum Fluorescence Holography Lasers, Semiconductor Light Medical Devices Microscopy Microscopy, Fluorescence Photolysis Pulse Rate Red Cell Ghost Reflex Submersion Telescopes Vaginal Diaphragm Xenon
2
Multibeam Bessel Microscopy Imaging

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Publication 2012
Eye Fluorescence Holography Microscopy Phototoxicity
3
Twin-Image Elimination in Holographic Microscopy
The first method falls under the broad category of Interferometric Phase-Retrieval Techniques and is applicable to cases where the recorded intensity is dominated by the holographic diffraction terms.31 (link)–33 The first step is the digital reconstruction of the hologram, which is achieved by propagating the hologram intensity by a distance of z2 away from the hologram plane yielding the initial wavefront Urec. As a result of this computation, the virtual image of the object is recovered together with its spatially overlapping defocused twin-image. It is important to note that the recorded intensity can also be propagated by a distance of −z2. In this case, the real image of the object can be recovered, while the defocused virtual image leads to the twin-image formation.
Due to the small cell-sensor distance in the incoherent holographic microscopy scheme presented here, the twin-image may carry high intensities, especially for relatively large objects like white blood cells. In such cases, the fine details inside the micro-objects may get suppressed. Similarly, the twin-images of different cells which are close to each other get superposed, leading to an increase in background noise. This issue is especially pronounced for microscopy of dense cell solutions, where the overlapping twin images of many cells lowers the counting accuracy due to reduced SNR.
In order to eliminate the twin-image artifact, an iterative approach using finite support constraints is utilized.33 Basically, this technique relies on the fact that duplicate information for the phase and amplitude of the object exists in two different reconstruction planes at distances +z2 and −z2 from the hologram plane, where the virtual and real images of the object are recovered, respectively. Therefore, a twin-image-free reconstruction in one of the image planes can be obtained, while filtering out the duplicate image in the other plane. Without loss of generality, we have chosen to filter out the real image to obtain a twin-image-free reconstruction in the virtual image plane at −z2. Due to the finite size of the micro-objects, the real image of the object only occupies the region inside its support, while the defocused twin-image image spreads out to a wider region around the object, also overlapping with the real image inside the support. Hence, deleting the information only inside the support ensures that the real image is completely removed from the reconstructed wavefront. Nevertheless, the virtual image information inside the support is also lost, and the iterative technique tries to recover the missing information of the virtual image by going back and forth between the virtual and real image planes, recovering more of the lost information at each iteration. The success of this algorithm is highly dependent on the Fresnel number of the recording geometry, which is given by Nf = n(object size)2/(λz). It is reported that the technique proves successful for Fresnel numbers as high as 10.33 For RBCs of approximately 7µm diameter, the typical recording geometries presented here involve Fresnel numbers of <0.2; hence, the twin-image elimination method yields highly satisfactory results.
The steps of twin-image elimination are detailed below:

Initially the real image, which is the back-projected hologram at a distance of +z2, is used for determining the object support. Object support can be defined by either thresholding the intensity of the reconstructed image, or searching for its local minima.

The region inside the support is deleted and a constant value is assigned to this region as an initial guess for the deleted part of the virtual image inside the support as shown below: Uz2(i)(x,y)={Urec,x,y∉SU¯rec,x,y∈S where Uz(i)(x,y) denotes the field at the real image plane after the ith iteration. S represents the area defined by the object support, and Ūrec is the mean value of Urec within the support.

Then, the field at the real image plane is back propagated by −2z2 to the virtual image plane. Ideally, the reconstruction at this plane should be free from any twin-image distortions. Therefore, the region outside the support can be set to a constant background value to eliminate any remaining out-of-focus real image in the virtual image plane. However, this constraint is applied smoothly as determined by the relaxation parameter β below, rather than sharply setting the image to d.c. level outside the support: U−z2(i)(x,y)={D−D−U−z2(i)β,x,y∉SU−z2    (i)   ,x,y∈S where D is the background in the reconstructed field, which can either be obtained from a measured background image in the absence of the object, or can simply be chosen as the mean value of the field outside the object supports at the virtual image plane. β is a real valued parameter greater than unity, and is typically chosen around 2–3 in this article. Increasing β leads to faster convergence, but compromises the immunity of the iterative estimation accuracy to background noise.

The field at the virtual image plane is forward propagated to the real-image plane, where the region inside the support now has a better estimate of the missing part of the virtual image. The region outside the support can be replaced by Uz2(1)(x,y), the original reconstructed field at the real image plane, as shown below: Uz2(i+1)(x,y)={Uz2(1),x,y∉SUz2(i+1),x,y∈S

Steps c to d can be repeated iteratively until the final image converges. In most cases in this article, convergence is achieved after 10–15 iterations. This iterative computation takes around 4 seconds for an image size of ~5 Mpixels using a regular CPU (central processing unit – e.g., Intel Q8300) and it gets >40× faster using a GPU (graphics processing unit – e.g., NVIDIA GeForce GTX 285) achieving <0.1 sec computation time for the same image size.

Mudanyali O., Tseng D., Oh C., Isikman S.O., Sencan I., Bishara W., Oztoprak C., Seo S., Khademhosseini B, & Ozcan A. (2010). Compact, Light-weight and Cost-effective Microscope based on Lensless Incoherent Holography for Telemedicine Applications. Lab on a chip, 10(11), 1417-1428.
Publication 2010
Erythrocytes Holography Interferometry Leukocytes Microscopy Neoplasm Metastasis Reconstructive Surgical Procedures Response, Immune Twins
4
Raman Spectroscopy of Bone Samples
All Raman spectra were obtained from 10 points randomly distributed over the polished surface per bone sample using a confocal Raman system (Renishaw InVia Raman microscope) with a holographic grating (1200 lines/mm) providing ~1 cm−1 spectral resolution and a 830 nm laser source (Renishaw). Each spectrum was obtained as the average of 10 consecutive spectra with each collected for 5 seconds using a 20X objective (NA=0.40), focusing the laser into a ~2.5 µm spot on each sample. Daily silicon and laser power measurements (~35 mW) before and after data collection ensured wavenumber calibration and light throughput, respectively. Background fluorescence was removed from all spectra using fourth order polynomial fitting algorithm (53 (link)).
Unal M., Uppuganti S., Leverant C.J., Creecy A., Granke M., Voziyan P, & Nyman J.S. (2018). Assessing Glycation-mediated Changes in Human Cortical Bone with Raman Spectroscopy. Journal of biophotonics, 11(8), e201700352.
Publication 2018
Bones Fluorescence Holography Light Microscopy Neoplasm Metastasis Silicon
5
Holographic Light Patterning for Fluorescence Microscopy
The optical system, schematically depicted in Fig. 1 and Supplementary Fig. 11, was built around a commercial Olympus IX71 inverted microscope, modified in order to accommodate two opposite-facing objectives, OBJ1 and OBJ2, for excitation and fluorescence collection, respectively. To this end, the condenser lens of the microscope was substituted with a dielectric mirror and an Olympus LUMPLFL60xW/IR2, NA 0.90 objective (OBJ1). The expanded (× 10) beam of a Ti:Sapphire laser (MaiTai Deep-See, Spectra-Physics) covered the active area of a first LCOS-SLM (X10468-07, Hamamatsu Photonics; SLM1), which modulated the phase of the incoming beam to create a first image of the desired intensity pattern on the diffraction grating (830 l/mm, 53004ZD02-035R, Richardson Gratings; G) for TF through the lens L1 (f1=500 mm). 2D-phase holograms were calculated using a standard GS algorithm20 (link)33 . The first diffraction order was subsequently collimated by lens L2 (f2=500 mm) and impinged on a second SLM (X10468-07, Hamamatsu Photonics; SLM2), which was imaged at the back focal plane of the excitation objective, OBJ1, via a 2:1 telescope (lenses L3, f3=1,000 mm and L4, f4=500 mm). Suppression of the zero-order spot arising from SLM1 was achieved by using two cylindrical lenses (fL1=1,000 mm and fL2=−1,000 mm) oriented at +45° and −45° with respect to the grating lines64 (link).
Holographic light patterns generated at the sample volume illuminated a thin spin-coated fluorescent layer of rhodamine-6G in polymethyl methacrylate 2% w/v in chloroform and the induced fluorescence was imaged on a CCD camera (CoolSNAP HQ2, Roper Scientific) through OBJ2 (Olympus UPLSAPO60XW, NA 1.2). For 3D reconstruction of illumination volumes, OBJ2 was fixed and focused on the fluorescent layer, while OBJ1 was moved along the axial direction with a piezo positioner of 1 mm range when working in closed loop (PI N-725.2A PIFOC). The two SLMs, the CCD camera, the piezo positioner, lasers and other electronic components of the set-up were controlled by a custom-developed interface in LabVIEW. GS-based algorithms were run in MATLAB.
When the set-up was used for generation of multiplane holographic patterns (not temporally focused) a mirror replaced the diffraction grating, and SLM2 was either used in reflectance mode by applying only the flatness correction phase mask of the device or was replaced by a mirror. Both the grating and SLM2 were mounted on magnetic bases enabling fast switching between the different configurations. The multiplane GS algorithm used in this case was run in a custom-designed C++ software interface, Wavefront Designer20 (link).
Hernandez O., Papagiakoumou E., Tanese D., Fidelin K., Wyart C, & Emiliani V. (2016). Three-dimensional spatiotemporal focusing of holographic patterns. Nature Communications, 7, 11928.
Publication 2016
Chloroform Fluorescence Holography Lens, Crystalline Light Medical Devices Microscopy Polymethyl Methacrylate Reconstructive Surgical Procedures rhodamine 6G Sapphire Sirolimus Telescopes

Most recents protocols related to «Holography»

1
Raman Spectroscopy of Spores using LTRS
We acquired Raman spectra from spores using our custom-built LTRS instrument. The instrument is built around an inverted microscope (IX71, Olympus) [44 , 60 (link)]. We used a Gaussian laser beam operating at 785 nm (Cobolt 08-NLD) that is coupled into the microscope using a dichroic shortpass mirror with a cut-off wavelength of 650 nm (DMSP650, Thorlabs). Imaging and focusing of the beam were achieved by a 60 × water immersion objective (UPlanSApo60xWIR, Olympus) with a numerical aperture of 1.2 and a working distance of 0.28 mm. The same laser was used for Raman light excitation. In general, we operated the laser at a fixed output power of 100 mW corresponding to a power of about 60 mW in the sample (total energy of 1.2 J when exposed for 20 seconds). This power chosen was well below those previously recorded to damage spores [61 (link), 62 (link)].
We collected the backscattered light by the microscope objective and passed it through a notch filter (NF785-33, Thorlabs) to reduce the Rayleigh scattered laser line. Further, to increase the signal-to-noise ratio, we mounted a 150 μ m diameter pinhole in the focal point of the telescope. The filtered light was coupled into our spectrometer (Model 207, McPherson) through a 150 μ m wide entrance slit where a 600 grooves/mm holographic grating disperses the light [63 (link)]. The Raman spectrum was then captured using a Peltier cooled CCD detector (Newton 920N-BR-DDXW-RECR, Andor) operated at -95 ∘ C. Our system has a Raman wavenumber spectral resolution of < 3 cm -1 and accuracy of ∼ 3 cm -1 .
Malyshev D., Jones I.A., McKracken M., Öberg R., Harper G.M., Joshi L.T, & Andersson M. (2023). Hypervirulent R20291 Clostridioides difficile spores show disinfection resilience to sodium hypochlorite despite structural changes. BMC Microbiology, 23, 59.
Publication 2023
Holography Light Light Microscopy Long Terminal Repeat Microscopy Neoplasm Metastasis Spores Submersion Telescopes
2
Holographic Analysis of Corrosion Dynamics
The holographic recording system was the same as that used in our previous study [19 (link)], as shown in Fig. S2. The soluble corrosion products changed their concentration (Δc) at the interface during anodic dissolution, followed by a corresponding change in refractive index (Δn) and phase difference (ΔΦ). ΔΦ, Δc, and Δn are related by Equation (1) [20 (link)]. where k, λ0, and d are the concentrative refractivity, light wavelength, and geometrical path length, respectively.
Xu D., Sang C., Yuan B, & Li L. (2023). Investigation of the effects of the magnetic field on the anodic dissolution of alloy 690 in SO42− + SCN− solution using digital holography. Heliyon, 9(2), e13566.
Publication 2023
Corrosion Holography Light Ocular Refraction
3
Retinal Illumination Glare Measurement System
A custom-made experimental system shown in Fig. 4 was developed with the aim of illuminating the retina with wide-angle distribution light in a coaxial way to the observation of a luminous sinusoidal stimulus. The system includes a circular glare source composed of a holographic light shaping diffuser (Light Shaping Diffusers, Luminit, LLC) back-illuminated by a white LED (Cree LED XLamp XM-L2). The luminous intensity of the source is controlled by an external dimmer. The angular distribution of the source is modified by means of removable 3D-printed masks with different angular apertures. This configuration creates uniform discs instead of the conventional annuli configurations7 (link). Throughout the manuscript, we refer to angular size as the angular distribution of the uniform discs. For this experiment, four masks were used (with diameters 12.6 mm, 17.73 mm, 21.81 mm, and 26.67 mm), so the angular sizes subtended by the glare source once it was throughout the system were 24°, 33°, 40°, and 48°.

Optical layout of the experimental system: CL collimating lens, BS beam splitter.

A relay telescopic system consisting of two achromatic doublet lenses conjugates the aperture of CL (45 mm focal length) with the pupil plane of the subject providing extended Maxwellian illumination. Then, the glare source and the CS test are directly projected on the retina minimizing unwanted factors affecting the disability glare measurement such as the pupil size and scattering contributions from iris and sclera27.
The visual stimuli consist of a contrast sensitivity test generated by Contrast-Test software (Opto-software). The software generates sinusoidal gratings that, through the system, present a total angular size of 9.8° with spatial frequencies of 0.2, 0.3, 0.6, 0.9, 1.2, and 1.8 cycles per degree (c/°) and contrast levels of 20, 11.1, 5.5, 3.12, 1.66, 0.87, 0.47, 0.25 and 0.12%. The luminance values of the test range from 46.5 cd/m2 for gratings with minimum contrast to 20.9 cd/m2 for grating with maximum contrast, so photopic conditions are maintained independently of the glare source luminance. A 50:50 beam splitter allows coaxial pathway of the visual target (displayed on an LCD monitor) and the glare source. The whole optical system was mounted on a 30 × 45 cm optical board coupled to a chin rest to facilitate alignment of the system axis with the subject's visual axis.
Casado P., Ávila F.J., Collados M.V, & Ares J. (2023). A study on disability glare vision in young adult subjects. Scientific Reports, 13, 3508.
Publication 2023
Chin Color Vision Contrast Sensitivity Disabled Persons Epistropheus Glare Holography Iris Lens, Crystalline Light Lighting lumin Pupil Retina Sinusoidal Beds Telescopes Visual Pathways
4
Ultrasound Haptic Holographic Display
The holographic haptic display (UHEV1, Ultrahaptics Ltd.) comprised a planar array of N ultrasound emitters. Such a display focuses sound in air by applying a phase delay to each transducer signal. Constructive interference yields localized regions of high differential pressure, sufficient to impart time-varying displacements to the skin (1 (link), 2 ). The differential acoustic pressure field may be described by p(x,t)=∑n−1N14πrnanexp[j(krn−ωt−ϕn)] where x is a position within the Fresnel zone of the array, an is the amplitude of the acoustic pressure wave emitted from transducer n, k = ω/c is the wave number, f = ω/(2π) = 40 kHz is the ultrasound carrier frequency, c is the speed of sound, rn = ‖x − xn‖ is the distance from x to the location xn of transducer n, and ϕn is the corresponding phase delay. Focusing at a location xf is achieved by matching the phase delays, ϕn, to the propagation time for a wavefront to reach the focus ϕn = ω‖xf − xn‖/c, thus yielding constructive interference. The focal width, δ, satisfies a Rayleigh diffraction limit, with δ ⪆ c/(2f).
Ultrasound frequency oscillations cannot be directly felt via touch. In haptic holography, palpable low-frequency mechanical signals are produced via a nonlinear phenomenon known as acoustic radiation pressure. Neglecting viscosity, the Langevin acoustic radiation force FL imparted to an object (here, the skin) at a focus location is, to second order, given by FL=−∬SdS(⟨p2⟩I+ρ0⟨u1⊗u1⟩)⋅n where p, ρ, and u are the fluid pressure, density, and velocity fields. The angular brackets denote time-averaged quantities, n is the surface normal, I is the unit tensor, and S is a surface region containing the focus location. Subscripts 0, 1, and 2 refer to successive terms in a perturbation expansion about a quiescent fluid configuration (33 –36 ). Applying the same expansion to the Navier-Stokes equation yields an expression for 〈p2〉 in terms of lower-order quantities ⟨p2⟩=121ρ0c02⟨p12⟩−12ρ0⟨∣u1∣2⟩
Averaged over 1 cycle of oscillation, only the quadratic terms are nonzero. Together, they yield a nonvanishing, low-frequency force FL(x, t) that elicits vibrations in the skin (see Supplementary Text). The time evolution of these vibrations is governed by a driven elastic wave equation FL(x,t)={−m∂2∂t2+μ∇2+[(K+μ/3)∇]∇⋅}ξ(x,t)
Here, ξ(x, t) is tissue displacement, and m, μ, and K are the mass density, shear modulus, and bulk modulus, respectively. Plane wave solutions, ξ(x,t)=Ar^ej(k⋅x−ωt) , describe oscillations along polarization directions r^ . Because of the low-frequency content of the acoustic radiation force and high propagation speed of compression waves, most acoustic energy is transferred to shear (transverse) wave components, k^⋅r^=0 . For skin or soft tissues, shear wave speeds, c=μ/m , are frequency dependent and can range from 1 to 10 m/s at the tactile frequencies applicable to this study (22 (link), 23 ). Because of viscoelasticity, wave amplitudes are also attenuated in a frequency-dependent manner with increasing propagation distance (30 (link)).
Reardon G., Dandu B., Shao Y, & Visell Y. (2023). Shear shock waves mediate haptic holography via focused ultrasound. Science Advances, 9(9), eadf2037.
Publication 2023
Acoustics Biological Evolution Dietary Fiber Electromagnetic Radiation Feelings Holography Pressure Skin Sound Sound Waves Tissues Touch Transducers Ultrasonics Vibration Viscosity
5
Vibrotactile Perception of Scanning Motion
We examined the relationship between wake formation and tactile motion perception by analyzing a human hand vibrometry dataset and a behavioral dataset that were captured in a previous study by the authors (14 ). In all of the human participant studies, before data collection, written informed consent was gathered for all participants. The experiments were conducted according to the protocol approved by the human participants committee of our institution. The vibrometry experiment measured ultrasound-elicited skin vibrations in the direction normal to the volar (palmar) surface of a human hand using a scanning laser vibrometer (PSV-500, Polytec; sampling rate, 125 kHz). The focused ultrasound haptic display was used in the same manner as in the elastomer experiments. The hand was fixed to a vibration-isolated table in an open posture using 3D-printed brackets affixed to the fingernails via an adhesive, with the arm positioned in a relaxed posture (Fig. 5C). A constant-intensity source scanned along a 16-cm path to or from the base of the thenar eminence to the tip of digit 2. To facilitate comparison with the perception experiment, we modulated the scanning path in a similar manner to what is commonly used in haptic holography. Thus, the scan path consisted of a zigzag pattern with a 2-cm path width. The focus traversed the nominal motion path (along the path of the finger) at scan speeds vl = 1,2,4,7,11 m/s and was laterally modulated transverse to this primary motion axis, in alternating directions, with velocity vmod = ± 2.5 m/s (see Supplementary Text). For each speed, we analyzed the wake length, or spatial extent of skin vibrations along the motion axis, defined as the length in which vibration amplitude was at least 10% of maximum.
Behavioral data were captured in an experiment on tactile motion perception in which participants reported the direction of scanning via a two-alternative forced choice task. The stimuli were identical to those used in the vibrometry experiment but included an additional low-speed stimulus, vl = 0.5 m/s, whose motion direction could be easily perceived. Scanning stimuli were block-randomized over scanning speed and direction. Each of 12 participants completed 120 trials (10 repetitions for each of 12 stimuli). Participants could elect to repeat the stimuli one or more times. We computed per-participant summary statistics of the response data (Fig. 7B) and performed statistical analyses using generalized linear mixed modeling with a logistic link function (n = 12; significance of fixed effect coefficients assessed using two-tailed tests). We analyzed combined data from the vibrometry and behavioral experiments to determine the relationship between perception accuracy and wake length (Fig. 7C).
Reardon G., Dandu B., Shao Y, & Visell Y. (2023). Shear shock waves mediate haptic holography via focused ultrasound. Science Advances, 9(9), eadf2037.
Publication 2023
Elastomers Epistropheus Fingernails Fingers Holography Homo sapiens Motion Perception Skin Touch Perception Ultrasonography Vibration

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More about "Holography"

Holography is a captivating optical technique that uses the interference patterns of light waves to create stunning three-dimensional (3D) images of objects.
This revolutionary technology involves recording the wavefronts of light reflected from an object and then reconstructing the image by illuminating the recorded pattern with a coherent light source, such as a laser.
Holography has a wide array of applications, spanning fields like imaging, data storage, and optical communication.
Researchers can leverage PubCompare.ai, an AI-driven platform, to easily locate relevant protocols from literature, preprints, and patents, and identify the best methods and products for their holography research needs.
This ensures seamless and efficient experimentation on this transformative technology.
Beyond holography, researchers may also find utility in exploring other advanced imaging and visualization tools, such as 3D Cell Explorer, MATLAB, and the EPR finger dewar.
Additionally, components like the IMX081 image sensor and the BX41 and BX40 microscopes can be valuable in holographic and related research.
The use of specialized light sources, such as the Kr ion laser, can also enhance holographic capabilities.
Cutting-edge holographic systems like Q-PHASE and MAX606 offer unique capabilities that can further advance holographic research and applications.
The NRS-3100, a versatile Raman spectrometer, may also prove useful in holographic studies.
By leveraging these complementary technologies and resources, researchers can unlock new frontiers in the captivating world of holography.