Honeycomb-Inspired SERS Nano-Bowls for Rapid Capture and Analysis of Extracellular Vesicles

Research Article

Austin J Biosens & Bioelectron. 2024; 9(1): 1049.

Honeycomb-Inspired SERS Nano-Bowls for Rapid Capture and Analysis of Extracellular Vesicles

Sathi Das1; Jean-Claude Tinguely2,/; Eduarda M Guerreiro3; Omri Snir3; Kanchan Saxena4; Balpreet Singh Ahluwalia2*; Dalip Singh Mehta1#

1Bio-photonics and Green Photonics Laboratory, Indian Institute of Technology Delhi, India

2Department of Physics and Technology, UiT the Arctic University of Norway, India

3Thrombosis Research Group (TREC), Institute of Clinical Medicine, UiT - The Arctic University of Norway, India

4Amity Institute of Renewable and Alternative Energy, Amity University Uttar Pradesh, India

*Corresponding author: Balpreet Singh Ahluwalia, Department of Physics and Technology, UiT The Arctic University of Norway, Tromsø, 9037, Norway, India. Email: balpreet.singh.ahluwalia@uit.no; mehtads@ physics.iitd.ac.in

Received: November 06, 2024; Accepted: November 29, 2024; Published: December 06, 2024

Abstract

Extracellular Vesicles (EVs) are produced by each cell for communication and carry molecular signatures of the host cell. Therefore, the analysis of EVs is essential for disease detection and prediction of the state of host cells. We employ an Ag-coated nano-bowl PDMS substrate for molecular analysis of distinct EVs isolated from different cell types using Surface Enhanced Raman spectroscopy (SERS). The local field enhancement of the optimized SERS substrate was evaluated using the 3D Finite Difference Time Domain (FDTD) simulation that exhibits a high local field due to the cavity geometry. Apart from Raman signal enhancement, the nano-bowl-based substrate having large curvature restricts the Brownian motion of EVs at suspension, facilitating reproducible signal enhancement. The overall study demonstrates the utilization of the SERS technique as a label-free, rapid and sensitive analysis of EVs.

Keywords: Plasmonic trap; Biomarker; Malignant leukemia cells; Raman spectra

Introduction

EVs are nanobodies confined by lipid bilayer membranes which are naturally produced by all kind of cells, and carry diverse biochemical loads of proteins, lipids, and nucleic acids (i.e., RNA and DNA) [1]. EVs display a biological complexity and diverse heterogeneity according to their origin. Adequate analysis of the composition and biochemical load of EVs may thus provide critical information towards their exploitation for personalized medicine, disease prediction and diagnosis [2]. These vesicles include a diverse range of biomolecules including proteins, nucleic acids, and lipids, which resemble the composition of their parent cells [3]. For instance, tumor-derived EVs are composed of tumor-specific chemicals, making them suitable candidates for use as biomarkers in tumor diagnosis. Furthermore, EVs in blood plasma show great potential as a liquid biopsy source and could provide valuable insights into the molecular properties of early-stage melanomas [4]. Therefore, the characterization of EVs is crucial for disease diagnostics. However, detection of circulating EVs is complex due to their very small size (~100 nm), and potential chance of mixing with other proteins and molecules of similar dimensions [5]. Several methodologies have been explored to characterize the biomarkers carried by EVs. These methodologies include ELISA, WB, NTA, to mention a few. However, they do not come without draw backs such as consumption of a considerable amount of sample, sample processing, to name a few [6]. Therefore, it is essential to develop a method that can accurately and simultaneously characterize numerous EVs in a highly sensitive manner and address the current obstacles as well as enable the utilization of EVs as reliable biomarkers for the early disease detection.Recently various advanced nanophotonic and nanoelectronics approaches have been proposed for the detection of biofluids and biomarkers corresponding to diseases. For instance, Liu et al detected hepatic cell fate marker albumin in vitro and living cell labeling with up conversion nanoparticles (UCNPs), which are conjugated with Antibody (Ab) and Rose Bengal Hexanoic Acid (RBHA) [7]. Xu et al reported single-crystal patterned graphenesheet into Graphene Field-Effect Transistor (G-FET) biosensor that detected imatinib at as low as 15.5 fM [8]. However, these techniques require addition instrumentation and does not give the information of molecular energy label. Raman spectroscopy offers molecular fingerprint of samples in terms of its vibrational energy level [9]. The technique requires a small amount of samples and does not require external tagging process. However, the biomolecules exhibit inherently low Raman signal intensity, requiring high laser power and long integration time, that could lead to potential damage of molecules [10]. Surface Enhanced Raman Spectroscopy (SERS) is a popular technique that enhances the low Raman signal intensity and enables detection of analytes at low concentrations. The enhancement in SERS occurs due to the light trapping activity of metallic (Ag or Au) nanostructures at nanoscale [11]. Briefly, the trapped electric field generates hotspot regions around the vicinity of the nanostructures at the Localized Surface Plasmon Resonance (LSPR) condition. In this way, the analyte molecule localized on hotspots exhibits enhanced Raman signal. SERS is already being employed for the detection of a diverse set of molecules for chemical, and biomedical applications [9,12]. For example, Das et al detected different species and strains of pathogenic bacteria using Si nanowire SERS chip and machine learning [13]. Li et al have reported a micro-extraction SERS membrane made of gold@silver nanoparticles (Au@AgNPs) and CuO Nanospikes (NSs) on polymethyl methacrylate (PMMA) and detected microcystin–LR up to 5 × 10–6 μg/L [14]. Wang et al detected the serum extracellular vesicles for detection of early melanomas [15]. Yang et al distinguished EVs from different biological sources based on the SERS signatures collected using a graphene-covered Au coated quasi-periodic array of pyramids [16]. However, most of the existing literature reports the spectra of dried EVs since the EVs in suspension exhibit high Brownian motion hindering reliable in-focal measurements. Drying of EVs can lead to membrane modification, change in protein content and is prone to supplying false spectral information due to membrane alteration [17,18]. Therefore, it is desirable to perform SERS measurements of EVs in suspension to capture their chemical morphology. A few attempts towards trapping of EVs have been described, making use of a plasmonic tweezer, microfluidic set up, surface topology assisted passive trapping etc [19-23]. Among these, surface topology assisted passive trapping methodology restricts the high Brownian motion of bioparticles and passively traps the particle facilitating in-focal measurements [21,24]. Different surface topologies such as curved surfaces using nanopore, nanocavity, nano-bowl have been explore for passive trapping [24]. Here, the surface barriers of the structured surface restrict the motion of particles in the lateral plane (XY plane) and the incident laser assists in restricting the motion along the axial plane (Z-plane). Another advantage of such structured surfaces it that it also provides a larger surface area for additional plasmonic enhancement.

In this work, we described the SERS activity of plasmonic nanobowl surface and demonstrated the utility of the SERS substrate for label-free characterization of EVs in suspension state. The nanobowl surface topology is fabricated using a monolayer Polystyrene (PS) beads template. The topology of the PDMS surface resembles a honeycomb which is suitable for SERS enhancement due to its larger surface area compared to a flat substrate. Apart from the enhanced hotspot regions, it exhibits high surface barriers that could provide potential trap-sites for bio-nanocarriers. In this context, distinct EVs derived from three different malignant leukemia cells (HAP1, HAP1- F3KO, and THP1), were analyzed using the developed method to explore molecular signatures of EVs and the associated cell of origin. The THP1 cell line is a monocytic cell line commonly used to model macrophage functions, intercellular communication, and signaling [25]. The HAP1 cell has one copy of the chromosome, making it a valuable model for genetic research. HAP1 F3KO cells are genetically engineered HAP1 cells without the tissue factor (F3) gene, which has an essential role in blood coagulation [26]. Thus, the EVs derived from the mentioned cell lines contain a variety of biomolecules from the host cell, which helps find out the role of intercellular communication and disease diagnosis.

Experimental

The honeycomb inspired PDMS nano-bowl was fabricated and optimized using nanosphere lithography technique, as previously described [24,27]. Briefly, a 2.5% Polystyrene (PS) bead suspension (size: 1 μm) was spin coated on a plasma treated glass plate. The coated glass plates were subsequently submerged at an oblique angle into 4% Sodium Dodecyl Sulfate (SDS) in DI water. The hydrophobic solution repelled PS beads and a controlled immersion process led to the formation of a monolayer at the air-water interface. The floating monolayer of PS beads was scooped using a clean Si wafer and kept on a hot plate at 1100C for 20 min for increased adhesion. The PS beads template was further spin coated with PDMS solution at 800 rpm for 20 s and subsequently cured at 700C for 2 hours. Finally, the cured PDMS was peeled off and washed with dichloromethane and DI water to remove any beads residue.

To coat with Ag, the structured PDMS was placed inside a sputter coater (Cressington 208HR) for an optimized coating of 40 nm.

Isolation and Characterization of Extracellular Vesicles

Three million cells, Haploid human cell line (HAP1) and its derivative TF-knock out cell line (HAP1-F3KO) both from Horizon Discovery Ltd., were seeded in T-175 flasks in 40 ml IMDM+10% FCS. Cells were incubated overnight at 37°C, 5%CO2 and cell culture media was replaced by 40 ml IMDM + 10% exosome free FBS. Cells were incubated for 24 hours at 37°C, 5%CO2. Next, the culture media was collected and EVs were isolated by sequential centrifugation. Briefly, cell culture media was centrifuged at 300xg for 5 min in a 5810 Eppendorf centrifuge, swing bucket rotor A-4-81. Supernatant was transferred to a fresh tube and centrifuged at 2.500xg for 10 min in a 5810R Eppendorf centrifuge, swing bucket rotor A-4-81. Pellet was discarded and the supernatant was loaded into 50 mL, Polycarbonate Bottle with Screw-On Cap (Beckman Coulter) and centrifuged for 20.000xg for 30 min, 4°C in an Avanti J-26 XP centrifuge (Beckman Coulter) equipped with JA-25.50 fixed angle rotor. EVs were resuspended in 900 μl of 20 mM HEPES, 150 mM NaCl buffer and stored at -80°C until use.

THP1 monocytic cell line (American Type Culture Collection, ATCC) were cultured in 20 ml of RPMI+5% exosome free FCS in T-75 flasks, 37°C, 5%CO2. Fifteen ml of cell suspension were collected and centrifuged 250gx for 5 min. Supernatant was transferred to a fresh tube and centrifuged at 2500xg for 10 min in a 5810 Eppendorf centrifuge, swing bucket rotor A-4-81 to remove cell debris. Next, 30 ml of cell culture supernatant were pooled and concentrated in an Amicon-Ultra 15 Centrifugal filter units (Ultracel-50, Merck Millipore) centrifuging at 4,000rpm for 10 min in a Megafuge 1.0 (Heraeus Sepatech) centrifuge equipped with a swing bucket rotor BS4402/A. The concentrated cell culture media was loaded into a pre-washed 10 ml Sepharose CL-2B (GE Healthcare Bio-Sciences) size exclusion chromatography column. Sample was allowed to enter the column matrix and PBS was added continuously. The eluate was collected in 15 sequential fractions of 0.5 ml each. Protein quantification was used to identify the EV-rich fractions, which were then pooled and stored at -80°C until use.

Enumeration and Characterization of Extracellular Vesicles

Isolated EVs were characterized for particle concentration and size distribution using a ZetaView® PMX110 nanoparticle tracking analyser (Particle Metrix GmbH) equipped with a 488nm laser. EVs were diluted in PBS to obtain a particle concentration within the range 106 – 108 particles/ml. Data analysis was carried out with ZetaView (version 8.05.14 SP7) software. The presence of classical EV markers was carried out by bead-based flow cytometry analysis using CD9, CD81, and CD63 capture beads. Detection was carried out using a tetraspanin antibody mix (labeled with PE. Signal was acquired by flow cytometry using a CytoFLEX flow cytometer (Beckman Coulter, Indianapolis, USA) and data was analyzed using CytExpert 2.0 (Beckman Coulter, Indianapolis, USA) software.

Determination of Plasmonic Enhancement using 3D FDTD Simulation

3D Finite Difference Time Domain (FDTD) simulations using Lumerical software were performed to investigate the distribution of hotspots with an enhanced electric field. The simulation model was constructed using a simplified model of the nano-bowl structure as an inverted hemisphere having a diameter of 550 nm, as characterized from FESEM images. The thickness of Ag coating was set to be 40 nm. The refractive index of PDMS was set to 1.43, and the refractive index of Ag taken from the Palik data set [11]. The simulation geometry was considered for a single bowl to restrict the simulation memory requirements. The incident laser profile was chosen to be Gaussian, with an excitation wavelength of 532 nm, a bandwidth of ±5 nm and propagating in the –Z direction. The simulation domain was set to Perfectly Matched Layer (PML) boundary conditions. The mesh size was kept auto-nonuniform, and the override region closing the entire nano-bowl was set to 3 nm for all dimensions. The frequency-domain field profile monitors were utilized to check the local electric field map at various planes of the nanostructure.

Spectra Acquisition Methodology

To acquire the Raman spectra in suspension state, the fabricated SERS film was plasma treated and a 1.5 μm thick rectangular PDMS chamber positioned on top of the SERS substrate. 5μL of the sample solution was cast inside the chamber and sealed using a glass coverslip from the top. The sealed solution was characterized with a Renishaw In-Via Micro Raman spectrometer (100X, 0.85 NA). A 532 nm excitation laser, 10 mW laser power, and 30 s integration period were used for each SERS measurement. To conduct additional analysis, the acquired spectra were background removed and baseline corrected. The SERS spectra of each sample was collected multiple times considering the same spot and different spots on the sample solution placed on a substrate.