Abstract
A full derivation of the recently introduced technique of Harmonic Optical Tomography (HOT), which is based on a sequence of nonlinear harmonic holographic field measurements, is presented. The rigorous theory of harmonic holography is developed and the image transfer theory used for HOT is demonstrated. A novel treatment of phase matching of homogeneous and in-homogeneous samples is presented. This approach provides a simple and intuitive interpretation of coherent nonlinear scattering. This detailed derivation is aimed at an introductory level to allow anyone with an optics background to be able to understand the details of coherent imaging of linear and nonlinear scattered fields, holographic image transfer models, and harmonic optical tomography.
Keywords
- nonlinear optics
- tomography
- computational imaging
- nonlinear scattering
- nonlinear holography
- optical holography
- optical tomography
- phasematching
1. Introduction
Optical microscopy permits the noninvasive acquisition of information that is revealed through light-matter interactions. These light-matter interactions are generally referred to as contrast mechanisms and come in many forms. The information carried by an optical contrast mechanism depends on the properties of the illumination light, the properties of the light produced by the contrast mechanism, and the details of the light detection. Most optical imaging systems rely on light that can be described approximately as classical, although there is a steadily growing body of work describing microscopy methods that exploit quantum correlations to enable the extraction of new information from objects.
The coherence properties of the light used for illumination and detection are also critical drivers of the properties of an optical imaging system. The classical theory of optical coherence is concerned with the statistical properties of classical fields that are treated as random variables. Although light is, in general, partially coherent, it is often suitable to describe light in the limiting case of either fully coherent or fully incoherent. Heuristically, we can describe coherent light as a field that is statistically similar across either temporal or spatial points on the field, whereas fully incoherent light lacks any correlation either along temporal or spatial displacements. Consideration of optical coherence is critical for understanding the broader context of optical microscopy and optical tomographic imaging.
While light propagation is not directly modified by optical coherence, field coherence strongly impacts the observed signal from a detector. For our purposes, a semiclassical model of light detection is suitable, where we consider generated photocurrents in a photodiode or photo-generated electrons detected by a camera chip. In all instances treated herein, we assume detector integration times are longer than the temporal coherence times of the light fluctuations. As such, detected light intensities are inferred from a long-time average of the incident optical field’s instantaneous intensity. To provide a consistent framework for our discussion of coherent tomographic imaging, we briefly review optical imaging theory to ensure that the reader is familiar with the notation used in this treatment.
In this chapter, we focus on imaging systems that can be described in a classical optical formalism that uses coherent nonlinear scattering as a contrast mechanism. Coherent nonlinear scattering exploits the microscopic properties of materials that exhibit a nonlinear dipole in response to a sufficiently strong incident field [1, 2, 3, 4, 5]. While materials can produce higher-order responses than a nonlinear dipole, the high field strength required generally precludes the use of higher-order terms to prevent damage to the object under study. It is suitable to describe the sensitivity of the nonlinear response as a nonlinear susceptibility tensor that is obtained from a Taylor expansion of the dipole response to the applied electric field. While the tensorial nature of nonlinear response depends on the incident fields and the distribution, we will suppress the vectorial dependence of both the coherent nonlinear light-matter interactions and the light scattering [3]. Within this approximation, coherent nonlinear scattering is described by a scalar field. For the purposes of imaging and tomography, we must then build a model for the propagation of the scattered scalar field through an imaging system, the detection of that light, and the processing required to obtain a microscopic or tomographic image.
This chapter is organized as follows. Coherent imaging theory is outlined and the application to tomographic imaging using coherent scattering is described. This section will show that while the imaging system permits spatial magnification of the field to enable the observation of small features, this magnification comes at the cost of low-pass filtering of the spatial frequency span of the collected coherent scattered light. Next, the scalar model of the nonlinear scattered field is developed to produce the working equations for the contrast signal that is collected by the imaging system. Then, the physical implications of the scattering and image formation models are discussed. Finally, the implications of the image transfer model for holographic optical tomography (HOT) and the tomographic reconstruction algorithm for both second harmonic generation (SHG) and third harmonic generation (THG) are discussed. We conclude by discussing prospects for widefield HOT imaging.
2. Optical holography
Optical detectors respond to the incident optical intensity rather than the field. As a result, all phase information is lost when making any direct optical measurement of a field. However, we know that when the measured light has suitable coherence, we may convert phase differences into intensity modulations through optical interference. Generally, we may have the desired signal field,
Holography was first described as a linear scattering model where the scattering object is much smaller than the extent of the incident wave [6]. In this in-line Gabor holography, the unscattered (ballistic) part of the incident wave is treated as the reference wave. The interference between the scattered and unscattered portions of the field constitutes the hologram. In-line holography generated limited excitement initially because the desired scattered field was contaminated by an unwanted conjugate (twin-image) field. This contamination significantly degraded the utility of early holograms. Around the same time that Gabor was working on in-line holography, Leith and co-workers were working in a secret US government program to process synthetic aperture radar films optically. Leith and Upatnieks independently discovered holography, but with a communications theory perspective that employed a spatial frequency carrier for off-axis holography [7, 8, 9]. In off-axis holography, with a suitably large incident reference beam angle, the complete complex signal field may be recovered, thus solving the twin-image problem. In 1997, Yamaguchi demonstrated another elegant solution to the twin-image problem by taking a sequence of holograms where the relative phase of the signal and reference field was shifted, allowing for unique extraction of the complex signal field from a series of in-line holograms [10]. While early holographic work made use of photographic plates, modern holography makes use of digital cameras and numerical processing algorithms [11, 12].
Off-axis holography is hailed as a 3D imaging technique. Indeed, when a hologram produced from an exposed photographic plate is illuminated by a duplicate of the reference wave, one will observe the signal wave as if the object were still present. An observer will see a 3D image of the object. Off-axis holography was first revealed in dramatic fashion with holograms of trains produced in Leith’s laboratory. However, it must be remembered that human visual perception is stereoscopic and not truly 3D. Thus, an observer
Emil Wolf analyzed optical holography from the perspective of linear scattering in the first Born approximation. He developed what is now referred to as the Fourier diffraction theorem, which shows that while a holographic field can be propagated or refocused,
The focus of this chapter is on nonlinear holographic imaging. In nonlinear microscopy, signals are recorded from coherent nonlinear scattering, which arises from a distortion of the induced oscillating dipole response of an atom or molecule subjected to a suitably strong illumination (fundamental) field. This nonlinear response can scatter light to new frequencies at harmonics of the incident fundamental field frequency,
Due to the weak strength of the nonlinear optical susceptibility, coherent nonlinear holography had to await the development of more powerful ultrafast sources. Roughly 60 years after the first reports of linear holographic imaging, Demetri Psaltis’ group described SHG holography of SHG-active nanoparticles using a 10 Hz laser amplifier system [23] in a special issue of applied optics that was dedicated to the memory of Emmett Leith [24]. Subsequently, Psaltis demonstrated focusing and imaging of point scatterers in biological tissues and phase conjugation to improve image quality [25, 26, 27, 28]. Shortly after this initial demonstration of SHG holography, imaging in biological systems with oscillators was demonstrated [29, 30, 31, 32, 33, 34]. By optimizing the experimental configuration, quasi-3D imaging at rates of nearly 1500 volumes per second was demonstrated [34]. This early holography work was still limited in the ability to produce detailed 3D imaging and this problem was only recently solved with the introduction of harmonic optical tomography (HOT) [35].
3. Optical diffraction tomography
A measured optical field that has scattered from an object because of a spatial inhomogeneity in either the linear or nonlinear optical susceptibility reveals information about the spatial distribution of the susceptibility. The goal of any coherent imaging system is to uncover quantitative data on the spatial distribution of susceptibility variations,
The concept of diffraction tomography was introduced by Emil Wolf in his seminal optics communications paper analyzing optical holography for the case of linear scattering [13]. Wolf’s treatment is reproduced in this chapter and the extension to coherent nonlinear scattering [35] is developed.
In classic holography [7, 8, 9, 11, 12, 36], we consider the illumination of the object by a spatially coherent, monochromatic plane wave with a particular incident propagation wavevector
The opposite extreme of spatially coherent illumination is the case of spatially incoherent illumination [41, 42]. We may still assume a long coherence time for the case of quasi-monochromatic light. However, the temporally random variations of the illumination field sample the full range of possible incident spatial frequency that is supported by the numerical aperture of the condenser lens. The image transfer model for incoherent illumination exhibits a finite thickness at intermediate spatial frequencies, yet still exhibits no spatial frequency support near zero transverse spatial frequencies [43]. As a result, spatially incoherent imaging also lacks optical sectioning capabilities. However, when an object is placed within the depth of focus of a microscope with spatially incoherent illumination, an absorption tomographic image can be reconstructed [41] with only a slight modification to the standard computed tomography filtered back projection algorithm from a sequence of transillumination intensity images taken over a full rotation of the object [40]. This imaging modality is referred to as optical projection tomography.
Partially coherent illumination fits somewhere in between fully spatially coherent and incoherent imaging. The image transfer model was derived by Streibl for linear scattering under quasi-monochromatic, partially coherent illumination [43]. This transfer function falls between that found for fully coherent and fully incoherent illumination. While in the case of fully spatially coherent light, scattering is accumulated from all depths, the image transfer function of partially coherent light acts as a low-pass filter that rejects the defocused contributions [44]. Streibl showed that by acquiring a stack of images in axial steps of the depth of focus, the set of data can be deconvolved to obtain a three-dimensional image [45, 46, 47]. This same strategy—that of a 3D deconvolution of a stack of images—is a productive approach for 3D imaging of incoherent fluorescent emission [48, 49].
In recent years, Streibl’s approach has been expanded to other partially coherent illumination sources. A method called white light diffraction tomography makes use of spatially coherent light with very broad bandwidth, and thus short temporal coherence [50]. When this very broad bandwidth light is used to illuminate a specimen with a very high NA objective, measurement of the complex field produced by linear scattering through a variant of holography broadens the imaging transverse function axially to permit optical sectioning. Three-dimensional images of the inhomogeneity of the linear susceptibility are then obtained through a 3D deconvolution from a sequence of images taken as the object is displaced in the in the axial direction.
Another strategy that avoids the use of interferometry for extracting the complex field is the use of asymmetric illumination apertures with partially coherent light [51]. When this illumination strategy is coupled with a rigorous model of the imaging transfer function, again a 3D deconvolution can be applied to an axial image stack to obtain a 3D image of the spatial variations in linear optical susceptibility.
The forms of tomography that we have discussed so far are primarily based on optical scattering. As we discuss in detail in the later section, the reliance on scattering with spatially coherent illumination allows for the measured field to relate the input and output scattering directions, which pinpoints the spatial frequency component of the object spatial susceptibility perturbation distribution. However, the short duration of the excited state lifetime and rapid dephasing of fluorescent emitters renders them spatially incoherent. While one might expect this spatial coherence to prevent interference, an individual fluorescent emitter will interfere with itself even though the lack of spatial coherence prevents interference between emitters. As a result, diffractive optical structures can be designed to enable depth-dependent interference intensity structures that allow for holography of incoherent emitters [52, 53]. An alternate strategy can be deployed for mimicking coherent scatting and holographic imaging with incoherent emitters based on the interference of spatially coherent illumination light, either between a plane wave and a point focus [54, 55] or with a pair of plane waves [56, 57, 58, 59, 60, 61]. By using the interference between two spatially coherent illuminating plane waves, one may perform tomographic imaging with fluorescent emitters that exactly mimics ODT [62, 63, 64, 65].
Widefield coherent nonlinear scattering enables the ability to form holograms when a coherent reference beam is directed to interfere with the light produced from the nonlinear scattering process [23, 29]. In the case of illumination with a plane wave fundamental beam, the scattering picture for nonlinear scattering is nearly equivalent to that of linear scattering, with a few modifications. These similarities and differences in the scattering picture will be discussed in later sections of this chapter. The key observation is that we will not obtain any optical sectioning with strictly plane wave illumination. However, due to the weak interaction strength for nonlinear scattering, the fundamental excitation beam is generally weakly focused to provide a balance between field of view activated in the nonlinear scattering process and signal strength that is driven by suitably large field strengths. In such a weak excitation case, moderate 3D imaging resolution is observed [34].
The fact that nonlinear scattering is driven by multiple input fields allows for a completely new form of optical tomography that we called holographic optical tomography (HOT) [35]. In HOT, we employ a high NA condenser to illuminate the object with a broad range of input fundamental spatial frequencies. To ensure widefield illumination, the object is illuminated at defocused plane where the beam is spread out spatially. Because the nonlinear scattering process draws from a broad distribution of illumination spatial frequencies from the full transverse spatial frequency support of the condenser NA, the coherent transfer function for this widefield coherent nonlinear scattering imaging process gains axial spatial frequency support, and thus allows for optical sectioning. Now the strategy first demonstrated by Streibl may be deployed so that 3D tomographic imaging can be obtained from the deconvolution of an axial image stack using a model of the HOT coherent transfer function.
4. Description of optical imaging systems
Optical microscopy can be modeled as a two-dimensional or three-dimensional image collection system. As our focus here is the treatment of tomographic imaging with coherently scattered light, we will provide a discussion of the imaging of spatially coherent light. In the case of coherent nonlinear scattering, however, the weak nonlinear light-matter interaction strength necessitates the use of pulsed light fields. Because the light propagation [66, 67] is linear and shift-invariant, after the coherent nonlinear scatter has occurred (as described in the following section), we may treat the light propagation for each temporal and spatial frequency independently, so that the total field may be obtained from the superposition of the imaged fields. A schematic of the optical imaging system is shown in Figure 1.
The spatio-temporal variation of the scalar field is denoted by
Here,
When imaging a coherent field from an object plane to an imaging plane, we can use a simple shift-invariant model for each optical frequency component. The imaging system will be described by an ideal telecentric 4-F imaging system as shown in Figure 1 [66, 68]. Green’s function for a coherent 4-F imaging system is referred to as the amplitude (or coherent) spread function (CSF),
Here,
The coherent transfer function (CTF) is the Fourier transform of the CSF,
As the propagation of coherent fields through a source-free region can be readily described using the angular spectral propagator, the object field can thus, be propagated from any reference plane to the conjugate object plane of the imaging system. Similarly, the field in the imaging region can also be propagated from one plane to another. The angular spectral propagator for fields propagating in the positive
where the axial spatial frequency,
Within the theory of semiclassical light detection, we may describe the signal recorded by a camera of an incident optical field as the time average of the zero-delay field autocorrelation,
The angle brackets,
The intensity for spatially coherent fields, as we assume here, is defined as:
Coherent tomographic imaging requires access to the field directly. This field can be approximately retrieved experimentally through holography that relies on interference with a reference field, which we denote as
for the case of a unity amplitude reference field. In the transverse spatial frequency domain, we may write this expression as:
Here, we note that the image of the scattered field,
With a model of coherent imaging of the scattered field, we now need a description of the scattered field to proceed. In the following section, we derive the scattered coherent nonlinear field the the
5. Coherent nonlinear scattering of scalar field
Our goal is to understand the imaging properties, capabilities, and limitations of coherent nonlinear optical holography and tomography. While a full description of coherent nonlinear scattering requires a vector treatment [17, 32, 34], we will restrict our discussion to scalar fields. Such a treatment may provide an understanding of holographic and imaging properties without loss of generality, as the measurement at the camera always involves a projection of the nonlinear scattered field polarization onto the reference field polarization [34]. Thus, we post-select a particular polarization component that can then be regarded as a scalar nonlinear field.
In the scalar description that follows, we begin with the wave equation, where we have made the usual assumptions for optical propagation. Explicitly, these assumptions are that we consider a region devoid of free charges and associated free-charge current densities. Moreover, we assume nonmagnetic media, so the magnetic permeability used is simply that of free space. To simplify the wave equation, we assume that both the linear,
5.1 Scattering model of scalar field
Making explicit use of the assumptions stated above, we may combine two of Maxwell’s equations to obtain the optical wave equation:
Here,
For isotropic media that can, to the first approximation, be treated as spatially homogeneous, in the absence of free charges, Gauss’ law,
Now, Eq. (10) becomes
Our interest lies in the nonlinear response, which is encapsulated in the real displacement field, which is written as
The total real polarization density of the form of a superposition of the linear and the nonlinear response is given by
The linear polarization density follows a convolution of the linear optical response of the medium
The linear, causal optical response function of the medium is
For nonresonant interactions, the nonlinear polarization density may generally be expanded as a power series of the form
Details of the nonlinear polarization density will be deferred to a later section. These nonlinear polarization density terms drive a wide range of nonlinear optical processes. For our purposes, we will focus on
Combining all of these expressions, we arrive at our wave equation for coherent nonlinear scattering that reads the equation:
5.2 Wave equation in the frequency domain
The time-domain equation may easily be represented in the frequency domain by noting that the fields can be represented through an inverse Fourier transform as
Applying the second-order temporal partial derivatives to the inverse Fourier transform in Eq. (17) produces the frequency-domain wave equation:
Making use of the time-domain linear response function in Eq. (15), we may write the equation:
Defining the refractive index in the usual way as
This equation is now a forced Helmholtz equation, where the LHS describes linear scattering and the RHS is the nonlinear forcing function.
5.3 Slowly varying envelope approximation
The wave equation in Eq. (20) contains the spectrum of the real fields and polarization densities, which includes the complex conjugate of the positive frequencies in the negative frequency region. In addition, these spectra include all optical frequencies, including the fundamental and the nonlinear scattered fields. To simplify these expressions, we assume that each spectral region can be written as a separate spectral envelope, so that we consider, in general, a set of optical pulses (or cw fields) with frequencies centered at
with the distinct spectral bands centered about
where
We assume that we have pulses well described by a slowly varying envelope in time relative to the rapid oscillations of a carrier (center) frequency,
The wavenumber at frequency
For the convenience of notation, by defining
5.4 Harmonic generation
The nonlinear polarization density, e.g., for SHG scattering with
We have explicitly ignored spectral dispersion of the second-order nonlinear coefficient in this expression, and as such we do not need the second-order time response integral nor the second-order response function. Physically, these assumptions equate to assuming that the second-order polarization density responds instantly. Note also that the field and polarization density are described by real quantities in this expression. While many nonlinear interactions can occur, we focus our discussion on coherent nonlinear scattering where we scatter to new frequencies at
The many interaction terms are considered by taking the m
This term drives coherent nonlinear scattering from the fundamental optical frequency centered at
In an imaging scenario, we may assume that very little coherent linearly scattered power is generated. Thus, we may assume that
As a specific example, consider SHG, where the time-domain polarization density for the SHG source term reads
The polarization density for SHG oscillates with a center frequency of
5.5 Coupled wave equations
Making use of the nonlinear scattering assumptions noted in the previous section we are now in a position to write the coupled wave equations for the coherent nonlinear scattering process.
and where the nonlinear polarization density reads
The first equation describes linear scattering, while the second is the nonlinear scattering at the m
By defining the m
we may write the forced equation governing linear and coherent nonlinear scattering as:
This form of the equations admits the construction of solutions from the free space Green’s functions. Here, we have assumed that spectral width is sufficiently narrow than the multiplicative
The equations above allow for a general spectrally-varying treatment of coherent nonlinear holography and tomography. However, the effects of the spectral variation on propagation and on the interpretation of scattering are not strongly dependant on the pulse spectrum. In order to simplify the following interpretation of the imaging transfer function, we will assume that we have a narrow enough spectrum so we may make a continuous wave (cw) approximation, where
for the fundamental and
for the nonlinear harmonic field (Figure 2).
5.6 Holography with a linear scattering
Inspection of the coupled wave equations in Eqs. (36) and (37) makes it clear that within the undepleted pump approximation the fundamental field solution is independent of the nonlinear scattering. Thus, it is fruitful to first obtain a solution to the linear field propagation, and we will consider the general case where the linear susceptibility varies in space. We may rewrite Eq. (36) in the form of the equation:
Our goal is to solve for
Solutions to Eq. (38) in the first Born approximation may be constructed using Green’s theorem with the formula as follows:
Such solutions in the domain outside of the compactly supported susceptibility perturbation, i.e.,
where
Making use of a three-dimensional spatial frequency decomposition, where
Making use of this expansion in Eq. (39) produces the spatial frequency spectrum of the free space Green’s function as:
Here, we have defined the transverse spatial frequency vector
Computation of the inverse Fourier transform along the
By defining the source term in the RHS of Eq. (38) as
Here, the spectrum of the source term reads
The forward and backward scattered fields are obtained by applying contour integration and selecting the suitable residue from the simple roots of Eq. (42). In the forward direction (
In the backward direction,
We will restrict our discussion to the forward-propagating wave collected by the imaging system with a coherent transfer function given by
Here, we have dropped the unscattered portion of the incident field to focus on the scattered field and simplify the discussion that follows.
In the process of recording a hologram, we multiply by a reference field,
The operator
To simplify our analysis of the hologram, we will first consider the special case of the fundamental incident wave as a plane wave incident along the direction
For the plane illumination case, we may specifically write out our source term convolution integral as follows:
as
Now the imaged scattered field hologram for a single incident fundamental plane wave illumination reads as:
Note that
Making a coordinate transform into the spatial frequency space of the object by defining the scattering vector
Now, we may take the Fourier transform along z, giving us
The Dirac delta function has selected the portions of the Ewald sphere that are supported by the illumination and collection optical system transfer functions given as
By inspection of Eq. (54), we may identify the transfer function for a single illumination plane wave, which is given by:
When using a non-negligible illumination condenser optic NA, then the super-position of all of the illumination k-vectors must be considered so that we can get:
Here, we have suppressed the explicit optical frequency dependence. For a short pulsed illumination, we would make use of an effective transfer function weighted by the cross-spectral density of the scattered and reference waves:
Notice that only the terms
5.7 Coherent nonlinear scattering, holography, and tomography
The linear scattering case can be easily extended to nonlinear scattering. For m
Consider Eq. (37), which is a driven Helmholtz equation analogous to Eq. (38), but where we make the substitutions
where
Defining a generalized nonlinear scattering vector
Here, the transfer function for the harmonic holography reads:
And where the integrand is given by:
A similar extension to illumination with a short optical pulse can be applied to this transfer function as was applied in the linear scattering case (Figure 3).
5.8 Example: second harmonic generation holography
Coherent nonlinear holography offers new possibilities for expanded spatial frequency support due to the effect of noncollinear mixing of fundamental spatial frequencies in the nonlinear mixing process [35]. The key difference lies in the source term, which for SHG reads:
The spectrum of the square of the field is the autoconvolution of the spectrum,
The autoconvolution of the fundamental field spectrum also appears in the problem of modeling reflectance confocal microscopy [69] and for an illumination objective with a half-opening angle
Here, we use the parameters
Now, we consider the case where we have two input fundamental plane waves
which simplifies to
So that now the source term evaluates to read
The imaged SHG field reads
The SHG hologram reads
For the case with a pair of fundamental plane waves, the SHG hologram term
We have defined in incident SHG vector as the sum of the two incident fundamental k-vectors,
Defining a new SHG scattering vector
Now we may take the Fourier transform along z, giving us (Figure 4)
The SHG hologram field may now be written as a simple linear shift invariant model with
The transfer function for a pair of fundamental illumination plane waves, is given by
When using a non-negligible illumination condenser optic NA, then the super-position of all of the illumination k-vectors must be considered, so that
6. Harmonic optical tomography (HOT) conclusions
The conventional approach to harmonic holography, that is imaging of nonlinear scattering with holographic detection using a coherent harmonic reference beam, cannot provide depth information, known as optical sectioning. While one can rotate the illumination beam or the object, neither of these strategies are very practical. In the case of object rotation, the mechanical positioning errors introduced by the translation and rotation stages make high-resolution imaging all but impossible. While illumination beam scanning is easier, one is left with the classic missing cone problem, and thus estimation of the object is a difficult inverse problem that is prone to distortion.
A few years ago, we introduced a completely new strategy that takes advantage of the fact that coherent nonlinear scattering mixes all possible pairs of incident fundamental plane waves to produce a vast array of scattering directions. The result is that with a suitably large condenser NA for focusing the fundamental light, optical sectioning is admitted into the imaging process. Clearly, point scanning nonlinear scattering takes advantage of this very feature, but in that case, the total power of the scattered harmonic field is detected. As a result, one cannot obtain direct access to the desired nonlinear susceptibility,
However, HOT is able to exploit cameras, which provides several advantages. First, we have increased speed because we capture a widefield holographic image from which the mHG field is extracted. Second, we benefit from heterodyne amplification of the field because we can bring a strong reference field to detect a weak harmonic field and push to very high imaging speeds [31]. Third, because the CTF exhibits broadening along the direction of propagation (
This chapter focused on the background to introduce the uninitiated to the topics of coherent holography and tomography. We provided a full and rigorous scalar treatment of coherent nonlinear scattering for holographic and nonlinear imaging and tomography. Because most readers will be more familiar with linear scattering, we reviewed linear scattering and then demonstrated the homology to coherent nonlinear scattering through variable substitution to convert from the linear to the nonlinear scattering formulae. The critical difference between linear and nonlinear cases is that the source term in the nonlinear case provides vastly increased spatial frequency support. We demonstrated that this spatial frequency support could be related to a linear shift-invariant imaging model for coherent nonlinear scattering when holographic detection is used. As a result, the entire imaging process can be characterized by a coherent transfer function (e.g., Figure 5). Expressions for computing the CTFs for coherent nonlinear holographic imaging and tomography are derived. We hope that the theory introduced here will inspire new researchers to investigate the use of powerful coherent nonlinear holographic imaging and tomography tools.
Acknowledgments
We gratefully acknowledge funding from the Chan Zuckerberg Initiative’s Deep Tissue Imaging Program.
Dedication
We dedicate this chapter to the memory of Gabriel (‘Gabi’) Poposecu with whom we collaborated on the original HOT paper. Gabi is a dear friend and colleague and he is sorely missed.
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