Modeling of Low Coherence Interferometry Using Broadband Multi-Gaussian Light Sources

Using a low coherence interferometry (LCI) model, a comparison of broadband single-Gaussian and multi-Gaussian light sources has been undertaken. For single-Gaussian sources, the axial resolution improves with the source bandwidth, confirming the coherence length relation that the resolution for single Gaussian sources improves with increasing spectral bandwidth. However, narrow bandwidth light sources result in interferograms with overlapping strata peaks and the loss of individual strata information. For multiple-Gaussian sources with the same bandwidth, spectral side lobes increase, reducing A-scan reliability to show accurate layer information without eliminating the side lobes. The simulations show the conditions needed for the resolution of strata information for broadband light sources using both single and multiple Gaussian models. The potential to use the model to study optical coherence tomography (OCT) light sources including super luminescent diodes (SLDs), as reviewed in this paper, as well as optical delay lines and sample structures could better characterize these LCI and OCT elements. Forecasting misinformation in the interferogram may allow preliminary corrections. With improvement to the LCI-OCT model, more applications are envisaged.


Introduction
Optical coherence tomography (OCT) is a medical imaging technique that is fundamentally an application of low coherence interferometry [1][2][3].
In previous research [4], an OCT model was used to compare different optical delay lines (ODLs) in order to verify the functionality of a proposed stationary ODL [5]. To further investigate OCT operation characteristics, the OCT model has been used to characterize one to four combined Gaussian broadband light sources which mimic the spectral characteristic of super luminescent diodes (SLDs), a typical OCT light source.

Optical coherence tomography
In this section, we provide a brief overview of the processes and method of OCT, as well as providing an introductory review of the super luminescent diode OCT light source that is relevant to, and predictive of, appropriate applications of the OCT model simulator in this paper and in future research. This research considers combinations of SLD-like sources and their resulting interferograms.

OCT method
In LCI and OCT, a low coherent/broadband light source is used to generate a reflection intensity map of a material's (LCI) or tissue's (OCT) cross section.
In vivo (OCT), the sources penetration depth can vary from 1 mm to 3 mm or more. This depends on the tissue type as well as an increase in the longer wavelength and optical power [6]. The axial resolution can be 1 μm to 10 μm depending on the light source spectral shape [7][8]; decreasing in the value with the bandwidth and increasing in the value with the central wavelength [3].
Four key elements impact on the OCT detector signal: the light source, the ODL of the reference arm, the type of the interferometer used, and the sample characteristics.
The light source is low-coherent in that it has a broad frequency bandwidth. All the light frequencies interfere with each other, resulting in a self modulated light source where the width of the individual peak in the time domain is proportional to the image axial resolution, measured by the coherence length (L C ) of the source [see (1)] divided by the average tissue refractive index. The L C can be determined from the spectral characteristics of the source using 2 0 C ln 4 L        (1) where  0 is the source central wavelength, and  is the spectral full width at the half maximum (FWHM) of the power spectrum, assuming it has a Gaussian spectral profile. Typical OCT sources have  0 at 840 nm and 1320 nm, with  equal to 60 nm. From (1), these values give coherence lengths of 5.2 μm and 12.8 μm, respectively.
Since the inverse Fourier transform of a perfectly Gaussian spectrum in the frequency domain is itself a Gaussian in the time domain, a Gaussian spectrum will have one peak and no repeated peaks, ideal for stratified samples. The less Gaussian that the source spectrum is in the frequency domain, the more frequently that peaks appear in the time domain. An interferometer can then be used to manipulate the introduced light to acquire an interference pattern of the multi-layered sample's reflected beam and the reflected reference ODL beam at the detector (Fig. 1). Fig. 1 Operating principle of a Michelson interferometer type OCT system.

OCT light source characteristics
The suitability of the optical source is governed by its bandwidth, optical power, spectral shape, ripple, and cost. Figure 2 shows the relationship between the L C (axial resolution), FWHM bandwidth (λ), and central wavelength (λ 0 ).
The longer the source wavelength (λ 0 ) is, the wider the bandwidth (λ) is needs to be to achieve equivalent axial resolution. The wider the bandwidth is, the better the axial resolution (R axial ) is, which can be determined from the L C at the average tissue refractive index (n ave ): The larger the optical powerm is, the greater the sensitivity (limited by the biological safety irradiation limit) is. This is especially true for full field OCT where the source power is spread over a large illumination area.
The shape of the coherence function and the level of the side lobes are determined by the spectral shape. A perfect Gaussian spectrum has no side lobes in the autocorrelation function and is the preferred source spectrum. Due to their affordability and Gaussian spectral shape, OCT sources are typically SLDs. To increase the bandwidth, thus improving the axial resolution, it is common to combine two or more SLDs. This often leads to non-Gaussian spectra with multiple spectral peaks degrading the A-scan with the addition of the spurious smaller "side lobe" peaks [8].

Super luminescent diode
Since this paper considers the simulation of OCT interferograms using simulated single and tandem SLD (Gaussian) light sources, an introductory review of the SLD as an OCT source is appropriate. This review outlines the various techniques used to broaden the SLD spectra, so that the OCT axial resolution can be improved.
SLDs work like a forward biased PN junction for which a large forward bias produces a large density of electron-hole recombination and resulting light emission. The structure and operation of SLDs are similar to an edge emitting laser diode without the feedback or cavity so that lasing is prevented. Due to this high injection current, the spontaneous emission is amplified, resulting in super-luminescence. However, the higher the gain is, the narrower the spectral width is, until radiation amplification exceeds the loss, resulting in lasing, with loss of the spectral bandwidth [9]. For this reason, the current needs to be kept at a maximum value at which super-luminescence, not lasing, is generated [10]. Therefore, the SLD spectral width is between that of a light emitting diode (LED) and a laser diode.
The SLD wavelength and bandwidth are determined by the type of semiconductor materials and their layering in the waveguide structure of the diode [9]. The narrow emission angle of SLDs allows optimum coupling into the single-mode fiber for optical fiber based OCT [11]. SLDs can be manufactured to illuminate within and beyond the "therapeutic window", which is between 800 nm and 1350 nm [9].
In the earliest OCT systems, LEDs were also popular. These gave broader bandwidths than SLDs but with orders of magnitude less power in the single spatial mode, though the edge-emitting LED had higher intensity [12]. An edge emitting LED, used for high-resolution reflectometry in the biological tissue at the wavelength of 1300 nm, bandwidth of 60 nm , and L C of 12.4 μm, produced an optical power of only 1 W [13]. Combined LED sources, at 1240 nm and 1300 nm, improved the L C from 10.8 μm to 7.2 μm [14]. Though the power increased 100 fold from [13], it was still only 100 μW [9].
Interest in SLDs was initiated due to their application to fiber-optic gyroscopes in the early 1980s [15] and other fiber-optic-based sensors used in navigation [16]. This development led to their use in other sensing systems including Faraday-effect electric current sensors and distributed Bragg-grating sensor systems [7]. This was soon followed in the 1990s with their application to the testing of telecommunications wavelength division multiplexing systems [17] and various low coherence interferometry systems including OCT due to their small size, ease of use, low cost, and ten-fold improvement (10 mW) in the output power at that time [7].

SLD spectral broadening
SLDs would be the OCT light source of choice for application to making OCT affordable to medical general practice if their bandwidth could increase without significant loss to their Gaussian spectral shape. The spectrum of an SLD is determined by its optical gain spectrum.
The first SLDs were based on bulk semiconductor hetero-structures with thick active layers. Their optical spectrum width varied from 15 nm-20 nm for 800-nm AlGaAs emitters to 30 nm-40 nm for 1300-nm-1550-nm InGaAsP SLDs. Broadening the spectrum was attempted for these bulk active layer SLDs by including a "stacked-layer-SLD" with two active layers of different materials [7].
The most significant progress in spectral broadening was made with the demonstration of quantum-well SLDs.

Quantum Well SLDs
In a quantum well (QW) SLD, the active region of the device is so narrow that quantum confinement occurs. The wavelength of the light emitted by a quantum well source is determined by the width of the active region rather than just the bandgap of the material from which it is constructed. This means that the wavelength emitted can be tailored to a particular value. The physical form can be achieved using epitaxial growth techniques (molecular beam epitaxy) to grow a sequence of direct band-gap semiconductor layers so that the narrower bandgap material is sandwiched between the larger bandgap materials. A quantum "well" is then formed in both the valence and conduction bands. Harmonic-like, sub energy bands exist in these wells [18]. These extra energy levels can broaden the emission spectrum. The efficiency of a quantum well SLD is also greater than a conventional SLD source due to the stepwise form of its density of states function caused by introducing the well.
QW SLD spectral broadening can be achieved in two ways. Firstly, the optical gain of these SLDs is broadened by their higher density of states, compared to bulk SLDs. Secondly, transition from different sub-bands in quantum-well active layers, can be used to broaden the SLD spectrum [7]. This broadening is dependent on the magnitude of the drive current. However, as broadening increases, the spectrum can become bi-lobed [16], resulting in expected spurious side lobes appearing in the interferogram.

Multiple QW SLDs
An extension of the QW SLD, that increases spectral bandwidth, is the multiple QW (MQW) SLD in which quantum wells of various depths are created thereby broadening the emission spectrum. For example, a double QW separate confinement double hetero-structure SLD, has been demonstrated [(InGa)As/(GaAl)As/GaAs]. The combined spectra has a central wavelength of 1029.6 nm, a bandwidth of 108.5 nm (L C =4.3 μm), and a single mode power of 18.3 mW [19].
Compositionally modulated MQW SLDs have also broadened the SLD spectrum. Here, the depth of the well systematically decreases by varying the percentage compositions of the paired III-V direct bandgap semiconductor constituting each well. A bandwidth of 91 nm at 1300 nm and output power of 2 mW has been demonstrated [20].

Quantum dots-in-well SLDs
SLDs have been demonstrated, which are based on multiple layer "dots-in-the-wells" (DWELL) separate confinement double hetero-structures. These SLDs have a median wavelength of 1160 nm and bandwidth of over 100 nm (L C < 5.9 μm). However, the spectrum has multiple peaks resulting in side lobes in the coherence spectrum [19].
An addition to the MQW structure that broadens the emission spectrum of the SLD is the use of chirped quantum dot (QD) multilayers. The broadening is controlled by a change in the matrix surrounding the QD; that is, when the QDs are covered by an InGaAs strain-reducing layer. Depending on the thickness and composition of the strain-reducing layer, an emission red shift occurs [21]. The combination of the ground state and excited state emissions results in a bandwidth of 121 nm, centered at 1290 nm (L C = 6.1 μm). An increasing in the injection current will increase ground state emissions and blue-shift the spectrum [21]. Similar SLDs at a wavelength of 1144 nm with a bandwidth of 110 nm (L C = 5.2 μm) and a power of 58 mW, and at a wavelength of 1050 nm with a bandwidth of 70 nm (L C = 6.9 μm) and a power of 2 mW [23], have been demonstrated.
A broadening of the emission for a 1.3-μm QD well SLD can also be achieved by incorporating the InAs QDs in InGaAs QWs of the chirped indium composition. This dots in a compositionally modulated well (DCMWELL) SLD generates a broader and flatter emission compared to the DWELL SLD, which have wells of the identical indium composition and present multiple Gaussian peak spectra. This flatter emission is due to the overlapping of excited and ground state transitions from different DWELLs that have different indium well compositions [24]. An improved 3  2 chirped DCMWELL SLD with a bandwidth of 95 nm at the same wavelength of 1270 nm and power of 8 mW, and the possibility of the output power being increased to 42 mW has also been demonstrated [25].

Quantum dash SLDs
A variation in the QD is the quantum dash (QDash), which is a finite-length wire-like structure with the height and width similar to a QD and the length much longer than that of the QD. Bandwidths up to 300 nm [26] and near-Gaussian emission have been reported, though only above the "therapeutic window" at around 1600 nm. Broadening of QDash laser emission can be achieved monolithically by spatial bandgap engineering techniques employing regrowth, selective area epitaxy, or quantum heterostructure intermixing [27]. It may be possible, by using suitable combinations of larger direct bandgap semiconductor materials, to fabricate a QDash SLD that blue shifts the amplified stimulated emission spectrum into the therapeutic window while still keeping the bandwidth and other advantages of the QDash SLDs.

Tandem SLDs
Though the previous SLD spectra can be simulated using the present OCT model, this introductory paper considers the following method of increasing spectral bandwidth. Here, SLDs are optically combined so that their spectra overlap. This can be achieved by physically connecting multiple SLDs with their outputs coupled optically.
An early example of tandem SLDs had two SLDs at 830 nm (26-nm bandwidth) and 855 nm (25-nm bandwidth), optically combined with a beam splitting cube. This resulted in a reduction in the coherence length from 12 μm to 8 μm [28]. Wang [29] showed another multi-SLD example, which was a combination of four SLDs with central wavelength/bandwidth combinations of 1265 nm/30 nm, 1320 nm/70 nm, 1355 nm/53 nm, and 1380 nm/47 nm. The combined bandwidth produced was 145 nm centered at 1330 nm, having an output power of 10 mW and a coherence length of 5.4 m. Other novel tandem-SLD sources are the BroadLighter D-890 (2 SLDs), Q-940, and Q-1350 (4 SLDs) with bandwidth of 150 nm, 300 nm, and 280 nm, respectively [19], resulting in coherence lengths of 2.3 μm, 1.3 μm, and 2.9 μm, respectively. An example of a quantum-well double SLD was the DenseLight DL-BD9-CS31159A, a 25-mW SLD with a bandwidth of 170 nm at 1310 nm, and with the L C of 4.4 μm [30]. All of these SLDs can be generated by this model to investigate their A-scans.

Characterizing SLD OCT interferograms
This research considers the latter spectral broadening techniques. It compares the effect of combining multiple broadband Gaussian sources on their total spectrum, as well as characterizing the effect on the resultant simulated interferogram, and the corresponding limitations for practical implementations. Importantly, this is for the same five-layer 1D virtual sample structure, enabling the direct comparison between SLD combinations and individual broad and narrow spectra.
Multiple SLD bandwidth broadening is not only the broadening technique. While other techniques produce wider bandwidths, multiple spectral peaks typically occur. This initial investigation demonstrates the relation between the bandwidth (λ) and axial resolution (R axial ) for a given central wavelength (λ 0 ). It further compares the effects of bandwidth on the spectrum and autocorrelation function for combined Gaussian sources, corroborating current knowledge, as well as demonstrating the effect of the bandwidth and the number of Gaussian sources used.

Theory
The OCT circuit modeled is a Michelson interferometer, e.g. Fig. 1. The light source is a low coherent virtual source that can model either an SLD Gaussian spectral shape, a predefined combined spectra, or the ability to simulate A-scans using spectral curves generated by real light sources.
The sample is a stratified 1D virtual model with the definable layer depth and refractive indices. From these defined refractive indices, the layer reflectivities are calculated by the model and used to generate the complex sample reflections.
The optical delay line is a moving mirror on a linear scanner, where its travel length is defined over the total depth of the virtual sample. Other ODL can be tested, including the stationary stepped mirror ODL as well as other quasi-stationary alternatives.

Light source
The light source is modelled as a spectrum of continuous wavelengths, with a Gaussian spectral shape defined by the peak amplitude (A 0 ), the peak wavelength (λ 0 ), and the spectral bandwidth FWHM (λ), as

Light in the interferometer
In the interferometer, light is split by a beam splitter (Fig. 1); 50% is reflected (R) to the ODL, and 50% is transmitted (T) to the sample. The light amplitude after the split is The amplitudes after reflection from the sample interfaces are given by where i = 1,…,n is the index over the semi-reflector interfaces of the sample, and r i denotes the reflectivity of the ith interface. The total distance from the laser source to the ith reflecting sample interface and then back to the detector is denoted by d i . The model does not consider multiple reflection, due to the small reflection coefficients. However, this consideration can be included in future versions. The ODL is a moving reference reflector, assumed to be moving slow enough to neglect the Doppler effect. The distance from the laser source to the ODL reflector and back to the beam-splitter and then to the detector is denoted by d n+1 . If the ODL reflector moves an amount d, then d n+1 increases by an amount of 2d.

Light at the detector -wave interference
The square of the amplitude of the auto-correlated wave is Therefore, the total intensity is The integral in (9) is approximated numerically.

Method
In this section, the tissue model is defined, and the application of the OCT model simulator is outlined.

Tissue model parameters
The layered virtual sample employed in the simulation consisted of five layers with equal thickness, being 100 μm and 95 μm in Sections 5.1 and 5.2, respectively. This thickness is analogous to that of tissue lamina in vivo [31]. The refractive index assigned to the medium above the uppermost stratum was 1.35. The assigned refractive indices of the five sample layers, the uppermost layer first, were 1.45, 1.49, 1.45, 1.49, and 1.45, respectively. Even though these values are within biological tissue ranges, 1.37-1.5 [31], the model may be used to explore any virtual multi-strata reflecting material.

OCT model simulator 3.0
The flexibility of this version (3.0) of the OCT simulation model to allow, at this stage, choice of two sample layer characteristics -thickness and refractive index -enables approximate definition of real axial tissue characteristics. This then generates an autocorrelation function with twice the layer separation. For a user defined light source spectrum and ODL, the effects of OCT sources, ODLs [4], and sample types on OCT operation, can be studied to a degree remembering that a real system presents imperfections at every point in the interferometric circuit.

Results and discussion
In this section, we present results for OCT interferograms using (1) a single SLD Gaussian source with the varying bandwidth and (2) multiple SLD Gaussian sources with the constant bandwidth. Figure 3 shows the effect of Gaussian source bandwidth on the layer resolution. As the bandwidth increases, resolution increases. Note that side lobes are absent from the interferograms in Fig3. 3(b), 3(c), and 3(d). It is not possible to resolve individual layers in Fig. 3(a) because the L C is 106 μm , and the layer thickness is only 100 μm, which is 0.94L C . In contrast, the broadest source has the best resolution because the L C is ten times less for the same 100-μm interface separation, which is 9.4L C . Even with Figs. 3(b) and 3(c), the layers can be resolved, their separations being 1.9L C and 4.7L C , respectively. The hidden peak information in Fig. 3(a) can lead to loss of layer information in the A-scans. Figures 4,5, and 6 show the interferograms for two, three, and four combined Gaussian sources, respectively. Each spectral band width is 100 nm.

Multiple source with constant bandwidth
If the resolution is a function of the coherence length, Figs. 4, 5, and 6 should be as equally resolved as Fig. 3(d), as they have the same coherence lengths (10.6 m). This is, of course, not the case, as non-Gaussian sources generate the classic side lobe artefact. The greater the peak separation in the spectrum is, the greater the number of side lobes and their secondary, and tertiary daughter satellites are. Increasing the number of SLDs in the source will increase the number of side lobes in the A-scan. The graphs (a) and (c) in Figs. 4, 5, and 6 demonstrate the issue of non-Gaussian sources. Namely, the side lobes of a strongly reflective layer will appear equal to or greater than the real layer peaks of other layers in the A-scan. How can the detecting software distinguish the real peaks from the artefacts?
The graphs (b) and (d) in Figs. 4, 5, and 6 demonstrate one-layer-sample interferograms, which are effectively inverse Fourier transforms of their associated multi-SLD spectra -the latter inserted in each of the (a) and (c) graphs of Fig. 4, 5 and 6. These (b) and (d) graphs show the extent of side lobe artefacts not present in the 5-layer interferograms of (a) and (c). The (b) and (d) graphs also imply that the 5-layer A-scans are not just showing the contributions of each layer alone. Rather they represent a contribution from the interference signal from the adjacent layer as well. For example, Fig. 6 (b) has 6 detectable side lobes that extend down to the next layer, as will all the other SLD combinations if the layers are close enough. This is in marked contrast to the single SLD source with the similar bandwidth and central wavelength [ Fig. 3(d)] as mentioned above. Here, the layers can be as close as a coherence length (10.6 m) and still be distinguishable in the A-scan. Figures 4-6 show that the number of side lobes increases with the number of tandem SLDs and decreases with the center of each SLD spectrum converge. There is one to two generations of side lobes for the dual-SLD sources (Fig. 4), two to four for the triple-SLD sources (Fig. 5) and three to six for the quad-SLD sources (Fig. 6). Also, the larger the reflection is, the larger the side lobe and satellite magnitudes are.
These complex interferogram results indicate that the side lobes would interact with each other to a greater extent as the layers narrow below 9L C . As has already been mentioned, the result of this is that the phantom layers would appear as strong as the real layers. For example, in Fig. 4(a), if the corresponding secondary peaks of two strata were to be in phase, and collocated, then the sum of this would be equal in magnitude to the primary peak. This phantom layer would appear to be located exactly between the two strata. The complex interaction is also seen in Fig. 6(a), where the secondary peak of the front surface is identical to the main peak of the other layers. The result for the multiple layers shows that this effect is reduced as the separation between the central wavelengths of the sources converge.

Future work
Future research with this simulation model will explore: (1) modulating the strata thicknesses and their effect on the interferograms and (2) the effect of real OCT light source spectra on their OCT interferogram characteristics. Already the Matlab model's simulation software has presented fresh insights from its capability to generating interferogram "movies". In particular, it can capture a sequence of interferograms as the layer thickness stepwise increases or decreases, showing the change in the layer peak and, where relevant, side lobe peak magnitude and morphology.
The current version of the OCT model is one dimensional. It considers ballistic sample reflections dependent on the refractive index and interface separation. The potential to study the effect of real OCT light source spectra on interferograms is now possible with the next version of the OCT model. The potential to improve the model to study the effect of light sources and ODLs, using realistic virtual samples with additional tissue characteristics, such as absorption, scattering, dispersion, and polarization, is envisaged. This will provide a more realistic understanding of the OCT light source functionality for specific tissue types and conditions. Due to the ongoing extrinsic evolution of the OCT simulation software, more applications are envisaged. It will be able to forecast misinformation, for which corrections may be able to be made. It may also be able to provide insight into choosing the best real OCT light source for a given tissue application. Studying the effect of modulating layer thickness on the interferogram may help in the understanding of new OCT modalities. Its use in physics, biomedical optics, imaging, and photonics education may also be possible.

Conclusions
We have shown a comparison of broadband single-Gaussian and multi-Gaussian light sources used for OCT. For single-Gaussian sources, the axial resolution improves with the source bandwidth, as expected. However, for narrow bandwidth light sources, their interferograms show overlapping strata peaks. This results in the loss of individual strata information. For an increasing number of multiple-Gaussian sources with the same bandwidth, spectral side lobes increases, reducing the reliability of the A-scan to show accurate layer information without eliminating the side lobes. The more Gaussian the light spectrum is, the more ideal the autocorrelation function is. The potential to use the model to study real OCT light sources such as the SLDs reviewed in this paper, as well as optical delay lines and sample structures, can improve our understanding of the effects that these OCT elements have on the resulting A-scan. With ongoing model development, many more applications are envisaged.
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