Page 38 - TD-2-1

Tumor Discovery Breast cancer optical differentiation

biological tissue [37,38] , sketching of the blood vessels in the • The investigation and patient criteria for breast tissue
arm to aid with Phlebotomy and tissue oxygen [39,40] , and samples selection and preparation
breast cancer investigation and malignancy detection [41-43] . • Capturing the HS image for the ex vivo breast samples
The expansion of optical systems in current medical • The measurement of the sample’s diffuse reflection (R )
d
sectors in therapeutic, diagnosis, and surgery regions for both the cancerous and the non-cancerous regions
has motivated the research on optical properties of • The measurements for sample T r
numerous biological tissues. At the same time, the • Calculating the sample absorption coefficient (µ )
a
effectiveness of laser therapy varies by photon propagation from the measured T r
and spreading fluence rate inside irradiated tissues . • The statistical analysis to select the optimum wavelength
[44]
Moreover, the ability to image a biological sample for the diagnostic and therapeutic applications
deeply is limited by light penetration depth inside the • Calculating the system efficiency (average reading
biological tissues, as distinguished by high turbidity . accuracy, sensitivity, and specificity).
[45]
Regarding the optical properties of the biological tissues 2.2. Design and implementation of the optical
(comprising blood, lymph, and other biological fluids), imaging system
it had been classified into two classes: (i) opaque tissues
(intensely scattering) such as the brain, skin, blood, and The principal structure of the proposed framework
vascular walls; and (ii) translucent tissues (inadequately is partitioned into two different configurations. The
scattering) such as the cornea and anterior eye chamber first configuration (reflection approach) utilizes a
lens . The light interaction (reflection, scattering, and polychromatic source light (Derungs, 20P SX -20 Watt,
[46]
absorption) with the investigated biological soft tissue Germany) with a spectral range (400 ~ 950 nm) to
varies concerning the optical properties variation of its measure the R of the investigated ex vivo breast samples,
d
fundamental characteristics, is presented in Figure S1 as illustrated in Figure 1A for the schematic diagram and
[47]
(Supplementary File). Figure 1B for the actual setup . The second configuration
(transmission approach) employs the same light source.
In this study, we designed an optical imaging system However, underneath the investigated samples for light T
r
incorporating the hyperspectral (HS) camera to acquire a measurement, these measurements yield the calculation of
fast and effective method for breast tissue characterization the µ , as presented in Figure 1C for the schematic diagram
a
by capturing the spectral signatures of the malignant and and Figure 1D for the actual setup.
normal breast tissues for both investigative and therapeutic
objectives. The exploited optical imaging had been divided Both configurations exploit the HS camera (Surface
into two separate setups (Reflection/Transmission) Optics, SOC710, USA) at 400 ~ 1000 nm, with a spectral
with spectral range of 380 – 1050 nm to measure the resolution of 4.69 nm and a bit depth of 12, which is
tissue’s diffuse reflectance (R ) and light transmission equipped with an objective lens (Schneider, 400 – 1000 nm,
d
(T), and then the sample absorption coefficient (µ ) was Germany). The employed HS camera is a push broom
a
r
calculated from T. Then, from the measurements of the imager with scanned cube 128 frames which has a built-in
r
previously stated parameters for both the normal and the translation sensor capable of directly collecting information
malignant breast tissues, we exploited the inverse adding for the entire spatial image of the whole object. The camera
doubling (IAD) method for breast tissue characterization. was settled at a height of 20 cm, and the light source was
Furthermore, the T-test was utilized to verify the significant 16 cm from the breast samples. The light was settled at
difference between the various types of breast tissues the same distance under the samples in the transmission
and select the optimum wavelength for diagnosis and configuration. The signal analysis measurements were
therapy applications. Finally, the proposed methods with analyzed with software (SOC’s Hyperscanner and
histopathological examination were compared to evaluate SRAnalysis, USA) accompanied by (DADiSP, SE 6.7, USA)
the system’s effectiveness in terms of sensitivity, specificity, on a personal laptop (DELL, INSPIRON 5584, Intel Core
and accuracy. I7, 16 GB RAM, Windows 10, USA) where the actual setup
with all of its components is displayed in Figure 1.
2. Materials and methods
2.3. Optical phantom preparation and system
2.1. Primary system interconnections calibration
The primary system interconnections include the following: Initially, we prepared liquid optical phantoms for system
• The design and implementation of the optical imaging calibration. Then, we used demineralized water as a matrix
system material and added milk (whole milk, lactose-free, and
• The optical phantoms and system calibration fat-free) as the scattering material with three different

Volume 2 Issue 1 (2023) 3 https://doi.org/10.36922/td.258