HIV-1 infection is a major health threat in both developed and developing countries. The integration of mobile health approaches and bioengineered catalytic motors can allow the development of sensitive and portable technologies for HIV-1 management. Here, we report a platform that integrates cellphone-based optical sensing, loop-mediated isothermal DNA amplification and micromotor motion for molecular detection of HIV-1. The presence of HIV-1 RNA in a sample results in the formation of large-sized amplicons that reduce the motion of motors. The change in the motors motion can be accurately measured using a cellphone system as the biomarker for target nucleic acid detection. The presented platform allows the qualitative detection of HIV-1 (n = 54) with 99.1% specificity and 94.6% sensitivity at a clinically relevant threshold value of 1000 virus particles/ml. The cellphone system has the potential to enable the development of rapid and low-cost diagnostics for viruses and other infectious diseases.
The timely management of infectious diseases especially in the developing countries where there are limited laboratory infrastructure and trained staff is a major global health-care challenge1,2,3. Diagnostic platforms that meet the World Health Organization’s ASSURED criteria (Affordable, Sensitive, Specific, User friendly, Rapid, Equipment-free, and Delivered) with the ability to be seamlessly integrated with appropriate and effective surveillance mechanisms can shift the paradigm in outbreak control and the prevention of new epidemics3,4,5. Of particular interest is early human immunodeficiency virus (HIV) detection, timely initiation of antiretroviral therapy (ART), and monitoring ART for efficient management of HIV infection particularly in resource-poor settings where >70% of the infected individuals live6.
The rapid advances in consumer electronics and portable communication systems particularly cellphones have led to faster and cheaper approaches of data acquisition and significant growth of cellphone subscribers worldwide particularly in the developing countries7,8,9,10. The global cellphone adoption and cellphone adoption in just Africa has jumped to almost 4.8 billion and 0.5 billion, respectively in 2016 and will reach to 5.7 billion and 0.725 billion by 2020, respectively8,9,10. Such significant cellphone adoption particularly in resource-poor settings combined with its powerful computing ability and built-in sensors present a promising potential in developing mobile health (mhealth) tools and surveillance diagnostics that can help us in closing the gap in infectious disease management through providing appropriate diagnostic solutions11,12,13. The advances in telecommunications combined with the recent changes in consumer behavior on wearable sensors and self-testing have led to the development of a series of mhealth diagnostic and surveillance technologies for disease detection and infection management14,15,16,17,18,19,20,21.
Recent progress in material synthesis and engineering can allow seamless integration with cellphone systems to develop advanced digital health tools and technologies. Self-propelling nanoparticles (NPs)/microparticles are among the most exciting materials that possess unique properties and have a tremendous potential for disease diagnosis and treatment monitoring22,23,24. These materials are readily synthesized in different shapes (e.g., spherical, rod, wire, tube, and polymer aggregates) and catalytic, magnetic, and acoustic forces can power their motion. Catalytically powered motors are usually designed to harness specific catalytic reactions either through using enzymes or transition metals, such as platinum, silver, gold, copper, nickel, and iron. Simple integration with portable devices and stability over time especially compared to fluorescent-based sensing (i.e., resistant to photobleaching, temperature, and pH)25,26,27 are some of the advantages of catalytic motion-based sensing approaches. Furthermore, motion-based optical sensing does not require bulky optical components or expensive equipment usually used for fluorescent-based microscopy. It can also allow rapid testing compared to the conventional nucleic acid detection methods, such as polymerase chain reaction (PCR) and enzyme-linked immunosorbent assay (ELISA)25,27,28. So far, catalytic motor systems have been reported for DNA and protein sensing and diagnosis of different pathogens and diseases29,30,31,32,33,34,35,36,37,38.
Here, we present a cellphone-based assay for HIV-1 molecular detection using loop-mediated isothermal amplification (LAMP) and micromotors (CALM). The large stem-looped amplicons formed through LAMP amplification are uniquely adopted to change the motion of specifically DNA-engineered micromotors powered by metal NPs (i.e., platinum nanoparticles (PtNPs) and gold nanoparticles (AuNPs)) indicating the presence of the HIV-1 using the cellphone system (Fig. 1). The efficiency of the CALM system in qualitative detection of HIV-1 is evaluated using phosphate-buffered saline (PBS) and serum samples (n = 54) spiked with different concentrations of HIV-1 above and below a clinically relevant threshold value of 1000 virus particles/ml. The cellphone system is also tested using HIV-infected patient plasma samples (n = 6) by comparing the results of the motor-based sensing with the results obtained by a quantitative real-time PCR assay targeting a highly conserved region of integrase in the HIV-1 pol gene with single-copy sensitivity (iSCA).
Platinum motor preparation and characterization
The micromotors used in this study are PtNP-coated spherical polystyrene (PS) beads (with density of 1.04 g/cm³) indirectly engineered with short DNA probes through a middle piece of spherical AuNP (Fig. 2a). A detailed schematic for synthesis of Pt-motors is shown in Supplementary Fig. 1. The motor preparation reaction includes the direct coupling of AuNPs and PtNPs to the surface of amine-functionalized PS beads using a heterobifunctional crosslinker of succinimidyl 3-(2-pyridyldithio)propionate (SPDP). The beads were initially activated with SPDP-forming thiolated beads to allow the thiol–metal-based coupling with NPs (i.e., PtNPs and AuNPs). Prior to coupling reaction, AuNPs were modified with thiolated DNA probes of 30-mer oligonucleotides that specifically target HIV-1 gag. The prepared AuNP-DNA conjugates were mixed with the SPDP-activated beads with a molar ratio of 1:10 to minimize the number of DNA probes on the surface of beads. The remaining surface of PS beads was coated by adding excess amount of PtNPs (Fig. 2a).
Transmission electron microscopy (TEM) of the synthesized NPs showed that both the synthesized AuNPs and PtNPs were spherical in shape with diameters of 57.721 ± 5.181 nm (data reported as mean ± standard deviation) and 3.43 ± 1.336 nm, respectively (Fig. 2b). Digital images and ultraviolet–visible (UV-vis) spectroscopic analysis results for AuNPs and PtNPs are shown in Fig. 2c and Supplementary Fig. 2. In addition, dynamic light scattering (DLS) analysis results confirmed the stability of the prepared AuNPs and PtNPs with polydispersity index values <0.45 (Supplementary Fig. 3, 4) and zeta potential values of −14 to −29 mV (Supplementary Fig. 5, 6). The conjugation of DNA to AuNPs was confirmed using UV-vis spectroscopy and Fourier-transform infrared spectroscopy (FT-IR) techniques. Figure 2d shows the FT-IR spectra of non-modified prepared AuNPs and AuNPs conjugated with DNA probes. The addition of DNA resulted into a group of peaks around 515.01, 852.56, 1004.0, 1300.0, 1518.8, 1718.6, and 2061.9/cm that are specific for NH2 and pyridine of DNA nucleotides39. In addition, the number of DNA capture probes per NP was quantified using UV-vis spectroscopy (Fig. 2e and Supplementary Methods). The results indicated that the average ratio of DNA/AuNPs was 12.1 ± 0.12 DNA probe molecule per each AuNP. The efficiency of AuNP–DNA conjugates coupling to the surface of PS beads was evaluated using silver staining technique. The presence of DNA–AuNPs on the surface of beads induced a rapid change of the silver staining reaction into a dense dark brown color compared with control samples where non-modified PS beads were added (no AuNPs) (Fig. 2f). The stability and reactivity of the fully structured motors (PtNP/AuNP–DNA-modified PS) were confirmed using inductive couple plasma–mass spectroscopy (ICP-MS) and gel electrophoresis techniques (Fig. 2g–i). ICP-MS analysis showed that each PS bead is modified with an average number of 1.335 ± 0.9161 and 386,044.1 ± 10.9161 of AuNPs and PtNPs, respectively (Supplementary Methods). In addition, the deposition of PtNPs with its characteristic intense brown color on the surface of PS beads was easily observed as a visible brown color when the prepared motor solution was dropcasted on a sheet of chromatography paper, confirming the heavy surface modification of beads with PtNPs (Fig. 2g). On the other hand, agarose gel electrophoresis technique was applied to test the efficiency of the fully structured motors (PtNP/AuNP–DNA-modified PS beads) in capturing synthetic target DNA (Fig. 2h). Synthetic target DNA was mixed and allowed to hybridize to DNA capture probes present on the surface of Pt-motor. The hybridization reaction products of motors and target DNA were then isolated by centrifugation, washed, and the captured synthetic target DNA molecules were released by incubation at 95 °C for 5 min The released target DNA was then tested using agarose gel electrophoresis technique. The results showed a clear band at 180 bp that is specific for the synthetic target DNA captured and isolated using the prepared Pt-motors (Fig. 2h). Furthermore, fluorescence spectroscopy indicated a 30% capture efficiency of LAMP amplicons on the surface of motors (Fig. 2i and Supplementary Methods).
Platinum motor motion testing and optimization
The velocity of Pt-motors prepared from 6-μm beads was tested in the presence and absence of H2O2. Figure 3a shows the effect of the concentration of H2O2 on the motion of 6-μm Pt-motors. In the absence of H2O2, motors were just vibrating due to the Brownian motion, and in the presence of H2O2, the average velocity of the motors increased at a rate of ~0.7 μm/s for 1% increase of H2O2 concentration (Supplementary Fig. 7 and Supplementary Movie 1). Our sensing protocol relies on monitoring the change in motor motion due to the LAMP amplicon reaction on the surface of motors using DNA capture probes through thermal hybridization. Thus it was necessary to test the effect of temperature and incubation time in H2O2 on the velocity of the prepared motors. We incubated aliquots of the prepared motors at 45, 80, and 100 °C for 10 min. The results indicated that the velocity of the prepared motors decreased with the increase in the temperature and there was a 10% loss of motion at 45 °C when compared to control (incubated at 25 °C as room temperature) (Fig. 3b, Supplementary Fig. 8). On the other hand, the prepared motors were stable in their motion with time of incubation in H2O2. Figure 3c presents the motion of motors for 120 s in 5% H2O2 solution. In the presence of H2O2, the motors autonomously move in a self-propelled fashion that is in principle due to the consumption of H2O2 and generation of gas bubbles. To investigate the motion of the prepared Pt-motors, their motion trajectories in the presence and absence of H2O2 were recorded under a bright-filed light microscope and then analyzed by plotting the mean squared displacement (MSD) against time (t). MSD is known to be proportional to tα for scaling exponent α40. We found that the MSD versus time had a near linear dependence (α = 0.9) when no H2O2 was added, as is the case for random diffusion (α = 1), while in the presence of 5% H2O2 solution, α = 1.8 indicating that the motor motion is caused by the catalytic activity of the surface PtNPs and differs from random diffusion (Fig. 3d, e). To further confirm the catalytic nature of the prepared motors (i.e., move due to the decomposition of H2O2 by PtNPs), samples with a mixture of 6-μm motor (coated with PtNPs) and non-modified 3-μm beads (no PtNPs) in 5% H2O2 solution were tested and their motion was analyzed using bright-field light microscopy and Image J software. The slope of MSD plot of the 3-µm beads and 6-µm Pt-motors suggests a fundamentally different mode of motion (Fig. 3f, g and Supplementary Movie 2).
Development of Pt-motor tracking cellphone system
The cellphone system used in visualizing and tracking the motion of micromotors comprises an android terminal (XT1575, Motorola) modified with an optical attachment and a cellphone application on a single-channel microfluidic device (Fig. 4a). The microchip used to test the motion of motors was prepared of poly(methyl methacrylate) (PMMA) substrate and a glass slide attached to each other using a 80-μm double-sided adhesive (DSA) machined with a laser cutter to fabricate a single microchannel with 2 mm width (Supplementary Fig. 9). The cellphone attachment was designed in Solidworks and three-dimensional (3D) printed with low-cost polylactic acid (PLA) material. The 3D printed enclosure housed a broadband white light-emitting diode (LED), a 3.3-V battery, a switch, and inexpensive optical lenses. The 3D construct also includes a sample holder to focus the sample between the two lenses and the cellphone camera (Fig. 4b). The optical attachment and sample holder were custom-designed to facilitate chip insertion and positioning on the attachment through a simple slide-on mechanism and in a way that the chip remains in optimal focus without the need for manual focusing. The software on the cellphone was developed in Android Studio using OpenCV (ver. 3.1.0) libraries with a user-friendly interface to guide the user through the testing process (Fig. 4c). The cellphone application records videos of samples, enumerates motors, automatically calculates the velocity of motors, and reports the results in <1 min. The developed application was able to record sample videos at a rate of 30 frames per second (fps) with a maximum effective field of view of 320 × 240 pixels for the cellphone used in this study (Motorola MotoX). The developed cellphone system was first calibrated using a micrometer scale shown in Supplementary Fig. 10. The performance of the developed system in visualizing, counting, and tracking the motion of Pt-motors was tested and correlated to the manual counts using bright-field microscopy. The results indicated a correlation coefficient of 0.9413 with a standard error of 0.3592 and a correlation coefficient of 0.9028 with a standard error of 0.3121 for motor velocity and enumeration, respectively. Furthermore, there was no statistical difference between the measurements (n = 50) from the motion tracking application and the manual count performed by bright-field microscopy (P > 0.05, paired t test) and with 95% confidence interval (CI) of −0.1564 to 0.04814 and −0.1491 to 0.02913 for motor velocity and enumeration, respectively (Fig. 4d, Supplementary Fig. 11 and Supplementary Table 1).
LAMP reaction and validation of the CALM system
Reverse transcription-loop mediated isothermal amplification (RT-LAMP) was performed using a set of four primers that target gag gene of HIV-1 (Table 1 and Supplementary Fig. 12) following the standard protocol41,42. Different concentrations of HIV-1 RNA template were prepared and used as a target in LAMP reaction. The amplification product was characterized using agarose gel electrophoresis (Fig. 5a). The results indicated the formation of large-sized DNA amplicons appeared as ladder-like patterns with many bands (>320 bp in size) and the amount of these amplicons was proportional to the concentration of HIV-1 RNA.
To detect the motion of motors in the presence and absence of HIV-1 LAMP amplicons, the motors were mixed with LAMP amplicons and allowed to hybridize at 80 °C (Supplementary Methods). The formed motor–LAMP DNA assemblies were tested in 5% H2O2 solution. In the presence of HIV-1 LAMP amplicons, the velocity of the motors (n = 30) was significantly (P < 0.0001, unpaired t test) decreased by 95.26% compared to control where no HIV-1 LAMP amplicons were added (only Pt-motors) (Fig. 5b, Supplementary Fig. 13 and Supplementary Movie 3, 4). Subsequently, different dilutions of the target LAMP amplicons were allowed to hybridize with motors and the motion of the formed motor–DNA amplicon assemblies was tested in 5% H2O2 solution using the developed cellphone motion tracking system (Fig. 5c and Supplementary Movies 5 to 8). The results indicated that the presence of LAMP amplicons, even at a very low concentration of 3.394 ± 0.245 ng/µl, reduced the velocity of motors compared to control (no LAMP amplicons), considering signal-to-noise ratio = 3. We further tested the recovery of motor motion after releasing the target LAMP amplicons by incubating the formed LAMP DNA–motor assemblies at 90 °C for 30 s. The released amplicons were separated from the motors by centrifugation at 6000 × g for 5 min and tested in 5% H2O2 solution. There was a 75.52% recovery for the velocity of the tested motors (Supplementary Fig. 14). In addition, the response of the CALM system to non-target viruses was tested using different sexually transmitted RNA and DNA viruses commonly exist with HIV infection including hepatitis C virus (HCV), hepatitis B virus (HBV), herpes simplex virus type 1 (HSV-1), and human papillomavirus type 16 (HPV-16)43. The results of LAMP reaction confirmed that the DNA amplicons are only formed in the presence of the target HIV-1 and no visible amplification was observed with other tested viruses on agarose gel (Fig. 5d). Furthermore, the average velocity of motors in the presence of the amplification products of non-target viruses (i.e., LAMP reaction products generated with HCV, HBV, and HSV-1) was not significantly (P > 0.05, unpaired t test) different than control (no amplicons) samples and was at least three-folds higher than the average velocity of HIV-1 samples (Fig. 5e, f and Supplementary Fig. 15, 16). To further confirm the specificity of our system in the presence of the non-target amplicons or contamination, the motors were challenged with non-target LAMP amplicons generated from HPV-16 using specifically designed primers against envelop (E)-1 gene (Supplementary Table 2) and at amplification temperature of 60 °C for 30 min44. There was no significant change (P > 0.05, unpaired t- test) in the velocity of motors (n = 25) compared to control (no amplicons) in the presence of non-target amplicons confirming the high specificity of the developed CALM system for HIV-1 testing (Fig. 5e, f and Supplementary Figs. 15, 16).
HIV-1 detection using the CALM system
We evaluated the efficiency and reliability of the developed CALM system in HIV-1 detection using PBS (1× PBS, pH 7.4) and serum samples spiked with HIV-1 and patient plasma samples (Fig. 6 and Table 2). The developed system can qualitatively differentiate between samples with viral loads below (i.e., negative sample) and above (i.e., positive sample) a clinically relevant threshold value of 1000 copies/ml as recommended by the World Health Organization (WHO)45. To establish the motor velocity that corresponds to the threshold virus concentration of 1000 particles/ml, the system was first calibrated using 1× PBS samples (n = 48) spiked with different concentrations of stabilized synthetic HIV-1 RNA (0–107 copies/ml). The prepared samples were amplified using LAMP and the generated amplicons were allowed to interact with motors for target capture and detection using the CALM system. The results demonstrated an average velocity of 0.705 ± 0.082 μm/s for samples with 1000 copies/ml and there was a significant difference (P < 0.0001, unpaired t test) between the average velocity of samples spiked with target RNA concentrations below and above the threshold value of 1000 copies/ml (Fig. 6a, b). Accordingly, the cellphone system was calibrated using this velocity value of 0.705 ± 0.082 μm/s to allow qualitative testing of PBS and serum samples spiked with virus particles (n = 54) (Fig. 6c–f, Supplementary Fig. 17 and Supplementary Movies 9–12). The qualitative results obtained by the CALM system compared to the standard quantitative real-time PCR (RT-PCR) technique are presented as heatmap in Fig. 6c. In addition, the receiver operating characteristic analysis (n = 54) showed that the CALM system has a sensitivity of 94.6% with a CI of 81.8–99.3% and a specificity of 99.1% with a CI of 80.5–100% at the threshold concentration of 1000 particles/ml. The area under the curve (AUC) was 0.984 with a binomial exact CI ranging from 0.905 to 1.00 and significance level P (area = 0.5) < 0.0001 (Fig. 6d). The vertical scatter plot analysis showed that the accuracy of the CALM system in correctly classifying PBS (n = 34) and serum (n = 20) samples spiked with HIV as positive and negative were 100% and 90%, respectively (Fig. 6e). The specificity and reliability of the developed CALM system was evaluated using serum samples spiked with HIV-1 and non-target viruses of HCV, HBV, and HSV-1. The results showed that the velocity of motors (n = 30) significantly (P < 0.01, unpaired t test) decreased in the presence of the HIV-1, while in the presence of non-target viruses the velocity of motors was not statistically different (P > 0.05, unpaired t test) than HIV-free control samples (Supplementary Fig. 18, 19). In addition, we evaluated the performance of the CALM system in identifying HIV-infected patient plasma samples compared to the results obtained by iSCA assay, which is a quantitative real-time PCR assay with single-copy sensitivity targeting a highly conserved region of integrase in the HIV-1 pol gene widely used in clinical diagnosis of HIV infection and ART monitoring (Table 2, Supplementary Fig. 20, 21 and Supplementary Movies 13, 14)46. We observed 100% accordance between the CALM system and iSCA assay in classifying patient plasma samples as positive (≥1000 virus particles/ml) and negative (<1000 virus particles/ml).
Early diagnosis of acute HIV infection is crucial since viral replication and shedding occur in this stage before detectable HIV antibodies appear47. Individuals with acute HIV infection who are unaware of their disease can contribute to HIV transmission. Most of the point-of care (POC) HIV diagnostics such as lateral flow assays, including dipsticks or enzyme immunoassays (ELISA), and OraQuick HIV test kit target the detection of antibodies against HIV and thus lack the capability to detect acute HIV infection even at high viral load of HIV48,49. In addition, the widespread implementation of ART has been highly effective in reducing mortality in HIV-infected individuals but the number of AIDS-related deaths is still >1.1 million every year. The recent treat-all policy of the WHO recommends earlier ART initiation regardless of CD4 count. Expanding access to ART in developing countries has cumulatively averted 5.5 million HIV-related deaths in low- and middle-income countries50,51. The updated guidelines will significantly increase the number of individuals eligible for ART52. Nucleic acid testing (NAT) for HIV viral load represents the most important method for the diagnosis of acute HIV infection and ART failure monitoring, but current NAT-based technologies cannot be implemented at the POC due to the need for specialized laboratory facilities and technicians. The limitations of current HIV viral load assays also represent barriers for the monitoring and detection of treatment failure in resource-limited settings. Thus there is an immediate need for an easy-to-use, portable, and inexpensive diagnostic tool for detecting acute HIV and early failure of ART. The presented cellphone-based motion sensing platform allows HIV detection by uniquely combining three technologies: (i) LAMP-based NA amplification, (ii) simple optical signal generation using micromotors (PS beads functionalized with AuNPs and PtNPs conjugated with antibodies), and (iii) cellphone-based optical sensing. Such system does not require bulky, expensive fluorescent-based optical components usually used in other commercially available NAT-based methods. This platform allows specific qualitative HIV detection with a threshold of 1000 virus particles/ml and thus can be implemented to detect acute infection and reduce the risk of virus transmission in the window period and to detect early treatment failure. We attribute the specificity and sensitivity of the developed system to the nature of LAMP technique used in nucleic acid amplification and the design of catalytic motors. We optimized LAMP amplification conditions (increasing target concentration and amplification reaction time) to amplify the target nucleic acid down to 1000 virus particles/ml using a set of four specific primers, which is directly contributing to the selectivity and specificity for the detection of HIV-143,44. Engineering the surface of Pt-motors with 30-mer DNA capture probe that specifically recognize the target amplicon in a postamplification-capture step limits the binding of any non-specific amplicons and further improves the detection specificity and reliability. In addition, the CALM system takes the advantage of the highly efficient and rapid amplification of LAMP with a sensitivity limit down to single copy of the target. Together with the unique large-sized looped DNA amplicons characteristic to LAMP, the generated amplicons can effectively reduce the velocity of Pt-motors, allowing a rapid and sensitive detection of HIV-1 RNA41,53.
In our system, Pt-motors were prepared using PS beads with density of 1.1 g/cm3 to minimize the effect of gravity forces on motors facilitating their use as a motion sensor. Compared to bulk materials, NPs are known to possess higher surface-to-volume ratio and thus higher surface activity54,55. For this reason, PtNPs with average size <4 nm were used in the preparation of the motors to allow efficient catalytic activity55,56. In addition, the use of PtNPs allows better-controlled coverage ratio of the total surface of beads using thiol–metal chemistry compared to the commonly used metal sputtering technique that requires specific equipment and tedious control procedures over beads during the modification step. With ~4% surface coverage, the prepared Pt-motors were moving with an average velocity of 4.96 ± 0.281 μm/s in 10% H2O2 solution. Considering that our system relies on the payload effect of LAMP amplicon to change the velocity of motors, the control of the surface coverage of beads with PtNPs was critical to control the motor motion, allowing sensitive detection of the amplicon. It is worth mentioning that controlling the beads surface coverage with PtNPs helped to limit the accumulation of O2 bubbles generated during the catalytic-based motion of motors and allowed better imaging and motion tracking using the cellphone. The use of AuNPs to indirectly engineer motors with DNA capture probes allows efficient control on the number and position of the added DNA probes to the surface of Pt-motors. The number of DNA capture probe was optimized to be ~15 DNA molecules per motor particle to control the loaded number of the target amplicons and in turn the detection sensitivity of the developed system. Furthermore, this strategy of indirect modification of the motors with DNA allows spatial control over DNA probes to act as amplicon-binding spot that induces the accumulation of amplicons in one side of the motors to allow more directional and uniform motion of the motors. This is critical to allow easy motion tracking by cellphone and enhanced and reliable sensing performance of the developed CALM system.
The presented work has demonstrated the development of a cellphone-based technology for HIV-1 RNA detection based on monitoring the change in the velocity of catalytic micromotors in H2O2 solution when they interact with DNA amplicons. LAMP technique allows target amplification under isothermal condition and the used micromotors are simple in design and can easily be prepared using commercially available PS beads and metal NPs. The material cost of the hardware cellphone accessory, microchip, and reagents per test is <$5 (Supplementary Table 3). We showed that the developed system can rapidly (<1h) and qualitatively classify HIV-infected samples based on a threshold of 1000 copies/ml with 90–100% accuracy as compared to RT-PCR. In addition, this system is affordable, sensitive, specific, rapid, and user-friendly, which are the major components of ASSURED criteria. Thus it has significant advantages in addressing an unmet clinical need in HIV detection and treatment monitoring and can potentially prevent unintended infection transmission. However, the presented system is a platform technology and will need additional modifications to allow sample processing and amplification. Further testing using the standard laboratory-based methods will be needed to confirm positive results generated by the presented cellphone system before initiating any treatment. The developed platform can be used in molecular assays that require simple, low-cost, and rapid testing of viruses. The proposed system has a great potential for broad applications in infectious diseases control and management.
HIV-1 propagation and nucleic acid isolation
HIV-infected peripheral blood monoclonal cells (PBMCs) were first isolated from patient blood samples using Ficoll-Hypaque density gradient cell centrifugation. PBMCs were then stimulated by phytohemagglutinin and co-cultured with irradiated PBMCs at 37 °C and 5% of CO2. The virus titer in the co-culture supernatant was tested using HIV-1 p24 antigen ELISA (PerkinElmer Life Science, Inc., NEK050b). The co-culture process was continued till the concentration of p24 became 20 ng/ml. The cell culture supernatant was collected, and the virus concentration was tested using Roche-COBAS AmpliPrep TaqMan HIV-1 v2.0 system at Brigham and Women’s Hospital (BWH). For sample testing with the cellphone system, HIV-1 RNA was isolated from each sample using the AllPrep DNA/RNA Mini Kit (Qiagen, CA, USA) following the manufacturer's protocol.
A single-channel microchip consists of three layers: (1) PMMA (3.175 mm; McMaster-Carr Inc., 8560K239) that contains the inlets and outlets of microchannels, (2) DSA sheet (80 μm; 3M Inc., 82603) that includes the microfluidic channel, and (3) glass slide (25 ×75 mm2; Globe Scientific Inc., 1358A). The microchip design was initially prepared using the vector graphics editor CorelDraw X7 software. Then the DSA and PMMA were machined using the VLS 2.30 CO2 Laser cutter (Universal Laser systems AZ). The DSA was used to assemble PMMA and glass slide and the prepared chips were cleaned and tested for leakage using de-ionized water.
Pt-motor preparation and characterization
Platinum micromotors were prepared of spherical 6-μm PS beads coated with PtNPs and AuNPs and modified with DNA capture probe that recognizes HIV-1 LAMP amplicons. The detailed protocol includes three main steps: (1) PtNPs and AuNPs synthesis, (2) DNA conjugation to AuNPs, and (3) PS beads surface activation and sequential coating with NPs. The synthesis of PtNPs and AuNPs was performed following the common protocol of metal salt reduction with sodium borohydride57,58,59. For PtNPs synthesis, 100 ml of ultrapure water was heated in a 250-ml Erlenmeyer flask and brought to boiling and 7.2 ml of a 0.2% chloroplatinic acid hexahydrate solution was added and mixed by magnetic stirring. Then 2.2 ml of 1% sodium citrate freshly prepared in 0.05% citric acid was injected in the flask and the solution was mixed for 1 min. In all, 1.1 ml of 0.08% sodium borohydrate solution freshly prepared in 1% sodium citrate–0.05% citric acid solution was added while boiling and the reaction continued till the formation of the PtNPs. For AuNP synthesis, a seed solution of ~15 nm-AuNPs was first prepared by adding 900 μl of 1% sodium citrate trihydrate solution to 300 μl of 1% HAuCl4 diluted in 30 ml of H2O. The growth reaction of AuNPs was then initiated by adding 391 μl NP seed solution to 100 μl of 1% (W/V) HAuCl4 diluted in 9.5 ml of H2O under rapid stirring at room temperature followed by the addition of 22 μl of 1% sodium citrate solution and 100 μl of 0.03 M hydroquinone. The reduction is completed within 10 min. One milliliter of the synthesized AuNPs was mixed with freshly reduced thiolated-DNA probe deigned against HIV-1 gag gene (50 μM) and the mixture was incubated at room temperature for 12 h. The solution was then brought to 0.1 M NaCl and allowed to stand for 40 h and washed twice by centrifugation at 12,000 × g for 30 min using 10 mM phosphate buffer (pH 7.2)60. To prepare thiolated beads, 0.14 pM amine-functionalized PS beads (Spherotech, Inc., AP-60–10) were mixed with 1.6 mM SPDP crosslinker (Thermo Fisher Scientific Inc., 21857) in phosphate buffer (pH 7.2) and incubated for 3 h at room temperature. Then the thiolated beads were first coupled with the prepared DNA–AuNP conjugates using the well-known thiol–gold chemistry followed by adding excess of PtNPs to coat the remaining surface of beads. The prepared Pt-motors were characterized using TEM, UV-vis spectroscopy, FT-IR, Zeta potential (ζ), DLS, and ICP-MS59.
RT-LAMP amplification of the target HIV-1 RNA was performed using a set of four specific primers (Table 1). The reaction was performed as follows: a mixture of the 4 sets of DNA primers (50 µM) was first prepared by mixing 0.8 µl of FIP, 0.8 µl of BIP, 0.1 µl of F3, and 0.1 µl of B3 and then added to the reaction mixture prepared of 2.5 µl isothermal amplification buffer (New England Biolabs Inc., BO537S), 1.5 µl MgSO4 (100 mM), 1.4 µl dNTP (25 mM), and 2.5 µl Betaine (5 M). Then 2–4 µl of the target and non-target RNA was added followed by adding of 6 unit of AMV reverse transcription enzyme (New England Biolabs Inc., M0277L) and 8-unit Bst. 2.0 DNA Polymerase (New England Biolabs Inc., M0537L). The reaction volume was brought to 25 µl by UltraPure™ DNase/RNase-Free Distilled Water (Thermo Fisher Scientific Inc., 10977023) and mixed thoroughly before incubation for 40–50 min at 65 °C and termination at 85 °C for 5 min42.
LAMP amplicon capture and motion assay
Our assay relies on reducing the motion of the Pt-motors when specifically coupled with the large-sized LAMP amplicons. The prepared LAMP amplicons are hybridized with Pt-motor at 80 °C for 2 min and cooled to 4 °C61. Then 10 µl of the formed assemblies were mixed with H2O2 solution and loaded on the microchip. The reduction of the beads motion in the presence of HIV-1 LAMP amplicons was tested using either the developed cellphone system or the bright-field light microscopy (Carl Zeiss AG Axio Observer D1) using Snagit v11.4.3 (Build 280) video recording software. The recorded videos were analyzed using ImageJ and MtrackJ plug-in to manually calculate the velocities of beads in the tested sample.
Motor tracking cellphone system
The cellphone attachment was designed using the Solidworks 2015 software and 3D printed using Ultimaker Extended II 3D printer and Ultimaker PLA as printing material. The cellphone attachment was designed to record the videos using the cellphone rear camera of a Moto X smartphone (Motorola, XT1575). The optical cellphone attachment has an LED, electronics, and switches and two acrylic lenses extracted from TS-H492 discarded optical drives with focal lengths of 4 and 27 mm and numerical apertures of 0.43 and 0.1662. The cellphone application was designed using Android Studio to record a video of the sample for 30 s at 30 frames/s. The detection algorithm identifies the motors and tracks its motion to calculate its average velocities. The presence of the target virus is then determined based on the change in bead motion in the tested sample.
Evaluation of the CALM system in HIV-1 detection
We evaluated the effect of the presence of different concentrations of HIV-1 LAMP amplicons prepared by diluting the final amplification product in PB (pH 7.2) into the following percentages 100, 50, 10, 1, 0.5, 0.1, 0.01, and 0.0%. The total DNA concentration in each dilution was first measured using a NanoDrop One-C spectrophotometer (Thermo Fisher Scientific Inc.) and 10 µl of each concentration was mixed with Pt-motors and tested using the CALM system. We evaluated the performance of the CALM system using HIV-1 and non-target viruses, including HCV, HBV, HSV-1, and HPV-16. The cellphone system was calibrated with PBS samples spiked with synthetic HIV-1 RNA standard (0–1 × 107 copies/ml) purchased from ATCC (VR-3245SD) and then compared to the standard RT-PCR using 1× PBS (pH 7.4) and serum samples spiked with HIV-1 particles at concentrations between 0 and 1.5 × 104 virus particles/ml. In addition, the developed CALM system was tested using HIV-infected patient serum samples (n = 4) and fresh whole blood from HIV-negative subjects (n = 2) purchased from Research Blood Components Inc. HIV-1 plasma samples were prepared from whole blood obtained from patients enrolled in the HIV-1 Eradication and Latency (HEAL) Cohort and ART treated and followed up at BWH and Massachusetts General Hospital. This study was approved by the Partners Human Research Committee. Participants of the HEAL cohort represented a convenient sample of participants meeting the HEAL inclusion criteria. Samples obtained were based on participant flow and no other sample selection criterion was in place for the study. All patients (HIV positive and negative) provided informed consent for blood samples to be collected.
Statistical analyses were performed using OriginPro 2015 (OriginLab Corporation, Northampton, USA), GraphPad Prism software version 5.01 (GraphPad Software, Inc. La Jolla, CA, USA), and MedCalc 14.8.1 (MedCalc Software bvba, Ostend, Belgium). Correlation between the motion tracking cellphone application and the bright-field microscopy was performed using linear regression analysis, and paired t test analysis was used to compare the motor motion analyzed by both techniques. All data for system performance were analyzed using unpaired t test. Differences between groups were considered significant when P values were not >0.05, and levels of significance were assigned as *P ≤ 0.05, **P ≤ 0.01, ***P ≤ 0.001, and ****P < 0.0001. Each data point represents the average of a total of three independent measurements.
The computer code used for motion tracking in the developed cellphone system reported in this study is available upon request from the authors.
All relevant data are included within the article and Supplementary Information files and available upon reasonable request from the authors.
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We would like to thank Jonathan Li, Behzad Etemad, Sambeeta Das, Raymond Chung, Wenyu Lin, Wenting Li, Francoise Giguel, Sanchana Krishnakumar, Prudhvi Thirumalaraju, Akash Srivaths, Anugna Addula, Siddarth Swaminathan, and Yudong Li. Research reported in this publication was partially supported by the National Institute of Health under award numbers R01AI118502, R21HD092828, and P30ES000002; Harvard T.H. Chan School of Public Health, Harvard Center for Environmental Health through Harvard NIEHS Grant; and American Board of Obstetrics and Gynecology, American College of Obstetricians and Gynecologists, American Society for Reproductive Medicine, Society for Reproductive Endocrinology and Infertility through ASRM Award, and Harvard University Center for AIDS Research (CFAR) under award number 5P30AI060354–14.
M.S.D. and H.S. have filed a patent application around the reported technology through Brigham and Women’s Hospital and Partners Healthcare. The other authors declare no competing interests.
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Draz, M.S., Kochehbyoki, K.M., Vasan, A. et al. DNA engineered micromotors powered by metal nanoparticles for motion based cellphone diagnostics. Nat Commun 9, 4282 (2018). https://doi.org/10.1038/s41467-018-06727-8
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