Despite significant advancements over the years, there remains an urgent need for low cost diagnostic approaches that allow for rapid, reliable and sensitive detection of malaria parasites in clinical samples. Our previous work has shown that magnetic resonance relaxometry (MRR) is a potentially highly sensitive tool for malaria diagnosis. A key challenge for making MRR based malaria diagnostics suitable for clinical testing is the fact that MRR baseline fluctuation exists between individuals, making it difficult to detect low level parasitemia. To overcome this problem, it is important to establish the MRR baseline of each individual while having the ability to reliably determine any changes that are caused by the infection of malaria parasite. Here we show that an approach that combines the use of microfluidic cell enrichment with a saponin lysis before MRR detection can overcome these challenges and provide the basis for a highly sensitive and reliable diagnostic approach of malaria parasites. Importantly, as little as 0.0005% of ring stage parasites can be detected reliably, making this ideally suited for the detection of malaria parasites in peripheral blood obtained from patients. The approaches used here are envisaged to provide a new malaria diagnosis solution in the near future.
Malaria is a mosquito-borne infectious disease that affects 3.4 billion people - about half of the world’s population1. According to the malaria report 2013, there were an estimated 207 million cases of malaria infections in year 2012, causing a toll of 627,000 deaths2. The disease is most prevalent in tropical and subtropical countries of Africa, South America and South-East Asia. Obligate intracellular parasites of the genus Plasmodium are the cause of malaria. During its complex life cycle the parasite infects red blood cells (erythrocytes) and replicates within. The parasite directly ingests hemoglobin from the infected erythrocyte as a source of essential metabolites and energy3. While there are more than 120 species of Plasmodium, only 5 species are known to infect humans; P. falciparum, P. vivax, P. ovale, P. malariae and P. knowlesi. P. falciparum is the most common and is responsible for more than 90% of malaria death1. During the maturation in the erythrocyte, three distinct morphological stages can be observed microscopically - the ring, trophozoite and schizont stage. The cyclical invasion and reinvasion of malaria parasites in red blood cells causes the number of infected red blood cells to increase exponentially, resulting in the symptoms such as fever, headache, rigors and nausea usually associated with malaria.
The major challenges in current clinical malaria diagnostics are in obtaining a sensitive, robust, fast and inexpensive measurement from patients’ blood samples. One of the leading causes of the high mortality rate in malaria is the delay in medical diagnosis and treatment4. Prompt diagnosis and timely treatment for malaria is often difficult to come by in poverty-stricken countries with limited medical resources, while developed countries, with very few cases, often lack experience and expertise in malaria diagnosis5. Most malaria deaths can be prevented if diagnosis and effective treatment were administered within 24 hour after the onset of first symptom6. Physicians need the information on the severity of infection, often expressed in parasitemia (the ratio of infected to the total number of red blood cells) to determine the treatment schedule for malaria patients. Furthermore, anti-malarial drugs, such as artemisinin - the current last line of defense against malaria, have become less effective in malaria treatment as malaria parasite have adapted and developed resistance to the drugs7,8.
Giemsa-stained microscopic examination of thick blood smear has remained the gold standard for laboratory diagnosis of malaria for more than a century5,9. The procedure is labor intensive, time consuming and requires well trained and highly experienced personnel. In recent years, rapid diagnostic tests (RDT) such as the dipsticks were developed to aid malaria detection in malaria endemic area. However, negative RDT test results cannot be accepted directly without confirmation by microscopic examination10,11. The polymerase chain reaction (PCR) method has a high detection sensitivity of 0.0001% or as few as five parasites μL−1 of blood11,12. However, the process takes up to six hour per sample and is costly to perform13. Factors that preclude PCR as a suitable method for diagnosis tool in rural areas or in routine clinical setting include limited financial resources, inadequate infrastructures and lack of well-trained technicians5,12. So, even to date, access to fast, sensitive and reliable diagnostic tool is still lacking.
The miniaturization of magnetic resonance relaxometry (MRR) systems has been attracting considerable interest in recent years due to the promising applications in disease biomarker detection, point-of-care diagnosis and cancer screening by measuring the transverse relaxation rate, R2 of proton present in the bio-samples14,15,16,17. There are two main benefits to the miniaturization of MRR systems; it offers higher mass sensitivity and requires smaller sample volume than conventional nuclear magnetic resonance systems, which require high-strength, spatially uniform magnetic field18,19. Furthermore, each R2 measurement only takes approximately 1 minute. Recently, we have demonstrated that the presence of paramagnetic malaria pigment or hemozoin crystallites in malaria infected red blood cells (iRBCs) serves as the natural biomarker for malaria detection20. The bulk magnetic susceptibility of the iRBCs (Table 1) is significantly higher than the healthy red blood cells (hRBCs), which in turn induces a substantial change in the transverse relaxation rate. Nonetheless, MRR detection has a major drawback in that it measures the absolute value of a blood sample instead of detecting a relative change in the R2 value.
On the other hand, the separation of malaria iRBCs was made possible with the development of lab on a chip (LOC) or micro total analysis systems (μTAS). Gascoyne et al. exploited the difference in the dielectric properties of iRBCs and hRBCs to perform dielectrophoretic (DEP) separation in a microfluidic chamber21. While the technique has the ability to trap iRBCs at a localized position, the application of relatively high electric field causes Joule heating and could dramatically increase the temperature of the suspending buffer22 and affect the erythrocytes for downstream measurements. Ribaut et al.23 and Zimmerman et al.24 concentrate and purify iRBCs through magnetic columns (MACS) and magnetic deposition microscopy (MDM), respectively. However, both techniques have a serious limitation in that they were unable to separate ring stage iRBCs, which is important for the human P. falciparum malaria diagnosis. Previously, we have presented a deformability based separation method known as margination, where the stiffer malaria iRBCs are segregated towards the sidewalls of microchannel25. In contrast to the DEP or MDM methods, microfluidic margination offers the convenience of not needing external electrical and magnetic fields for iRBCs separation.
In this work, we develop a malaria diagnosis protocol that combines the use of microfluidics for the separation of iRBCs and MRR system for the rapid, label-free detection of malaria parasites. We mitigate the R2 baseline restriction by separating the iRBCs from the hRBCs through margination and compare the relative change in the relaxation rates of the separated blood samples. The diagnostic method that we propose here has similar detection sensitivity to PCR based methods and, at the same time, is one order of magnitude more sensitive than the standard Giemsa microscopic method. We improved the throughput of the microfluidic margination device by employing a multiplex margination design with 7 parallel margination channels and demonstrated that the device could effectively separate the hRBCs from iRBCs of all infection stages (ring, trophozoite and schizont). Due to the margination effect, the stiffer iRBCs are segregated towards the side outlet of the microfluidic channel, while the blood sample collected at the middle outlet is depleted of iRBCs. Thus, the marginated blood sample collected at the middle outlet has a lower R2 value compared to the inlet. The ability to perform relative R2 measurements alleviated the need for establishing a universal R2 baseline for MRR malaria diagnosis.
Results and discussion
Characterization of margination efficiency
The efficient enrichment of iRBC would be of significant benefit for the subsequent diagnostic of malaria, particularly in cases of very low parasitemia levels. In our previous work25, we demonstrated the margination of malaria iRBCs with a single margination channel. To improve this further, we evaluated the margination efficiency of the multiplex margination design (Fig. 1(a) and Fig. 2) with 7 parallel margination channels. With the margination effect, the stiffer iRBCs are segregated towards the sidewall, while more deformable hRBCs migrate towards the axial center of the microchannel. Figure 3(a) shows the DAPI fluorescence imaging at one of the bifurcation exits at the end of a margination channel with a total flow rate of 14 μL min−1, or 2 μL min−1 per channel. As the margination channel width-height ratio is 5:1, the channel height of 10 μm is taken as the characteristic length for the Reynolds number, Re estimation. Hence, assuming the whole blood density as 1056 kg m−3 and viscosity26 as 3.5×10−3 Pa s, the Re for flow rate of 2 μL min−1 is approximately 0.2. For all experiments, the hematocrit of the blood sample at the inlet is kept at 45–50%. We can clearly observe that the fluorescently labeled iRBCs with ~5% parasitemia level (~20% ring, ~80% schizont) are marginated effectively toward the sidewalls of the microchannel.
Since clinical samples contain only circulating ring stage parasites, we further evaluated the margination efficiency to separate ~1% ring iRBCs at various margination flow rates. With the help of a fluorescence activated cell sorting (FACS) flow cytometer, we could characterize the margination efficiency by estimating the parasitemia level of the blood collected from the middle and side outlets accurately. Figure 3(b) shows the parasitemia enrichment factor, PEF, for single channel flow rate of 1–10 μL min−1 (Re ≈ 0.1–1) for ~1% ring iRBCs. The parasitemia enrichment factor, PEF is defined as the parasitemia ratio between the side and middle outlet. Thus, a higher PEF value would indicate a higher margination sorting efficiency. As the PEF value remains relatively constant throughout the flow rate range, we can infer that increasing the margination flow rate from 1 to 10 μL min−1 does not adversely affect the margination efficiency substantially. Therefore, the flow rate could be increased to improve the throughput of the margination system without compromising the margination performance. With multiplex margination, throughput of the microfluidic separation step is improved to a total flow rate of up to 70 μL min−1, which reduces the margination process time to approximately 15 minutes.
Figure 3(c–e) show the margination results for ring, trophozoite and schizont, respectively. With the margination effects (see Methods), the parasitemia levels of the iRBCs at the side outlets are higher than the middle outlets for all three infection stages. In other words, the middle outlet is depleted of iRBCs, while the side outlet is enriched with iRBCs. The comparison of parasitemia enrichment factor for ring, trophozoite and schizont is summarized in Fig. 3(f). Since the stiffness of iRBCs increases exponentially as the infection stage progresses from ring to trophozoite and schizont (Table 1)27, the margination efficiency also increases accordingly. The multiplex margination device could separate iRBCs for all three stages of infection - ring, trophozoite and schizont effectively from hRBCs with a parasitemia enrichment factor and standard deviation of 1.9 ± 0.2, 4.1 ± 0.8 and 32.1 ± 7.6, respectively.
Establishing healthy baseline
Recently, we have shown that micro magnetic resonance relaxometry can be used as a new approach for malaria diagnostics20. The malaria infected iRBCs have higher transverse relaxation rate, R2 than the healthy hRBCs due to the presence of paramagnetic hemozoin crystallites in the infected blood20. These paramagnetic crystallites increase the bulk magnetic susceptibility of the iRBCs and induce a considerable increase in the R2 relaxation rate. Hence, the detection of the subtle increase in the R2 due to the presence of malaria parasites forms the basis of MRR malaria detection. However, MRR detection method measures the absolute R2 value of the blood sample instead of a relative change in the R2 value. The healthy absolute R2 value varies from individual to individual depending on numerous factors such as age, diet, genetic variation and hematocrit number and methemoglobin content. Furthermore, the R2 value of hRBCs increases with the number of post storage days when stored under hypothermic condition at 4 °C (Fig. 4(a)). The R2 value of that healthy blood sample increased from 6.80 ± 0.04 s−1 on day two to 7.94 ± 0.13 s−1 on day 21, an increment of 16.7%. Since the R2 value of the hRBCs increases as the RBCs age, establishing a universal healthy baseline R2 value for all individuals is rather impractical. Therefore, the malaria detection method based on the measurement of absolute R2 value needs to overcome the problem of the variation in the healthy baseline to be fully effective.
In order to overcome the R2 baseline challenge, we separated iRBCs from the hRBCs through microfluidic margination and compared the relative change in the relaxation rates, ΔR2 of the separated blood samples. Figure 4(b) shows the normalized R2 values of hRBCs and iRBCs for the marginated blood samples collected at inlet, middle and side outlets, where the absolute R2 values of each sample are divided with the absolute R2 value of the inlet hRBCs. The blood collected at the inlet refers to the blood sample obtained by remixing the bloods collected from the middle and side outlets after passing through the microfluidic channel, thus ensuring a fair R2 comparison between the inlet with middle and side outlets. The R2 relaxation rates of the collected blood samples are measured using the spin-down method described in the sample preparation section (see Methods). Interestingly, for hRBCs, the side outlet R2 value is approximately 15% higher than the inlet, while the middle R2 is approximately 6% lower than the inlet R2. A similar trend is observed for iRBCs. When the hRBCs are spiked with 0.0005% iRBCs, the R2 value of the side outlet increased further by approximately 7% since the iRBCs are marginated towards the sidewalls.
The observed phenomenon, that the side outlet R2 value is always significantly higher than the inlet, while the middle R2 is lower than the inlet R2 for hRBCs, may indicate that the margination device also separates stiffer and older RBCs from more flexible, younger RBCs. As the average life span of RBCs in vivo is about 120 days28, the hRBCs circulating in the human blood stream is made up of a distribution of RBCs of various age and deformability. The stiffness of RBC increases substantially during the aging process and is up to 134% less deformable on day 3629. RBCs are naturally damaged by oxidation during aging30 and cross-links are formed between the hemoglobin (Hb) and membrane proteins in the RBC31. Aging of RBC is associated with numerous changes, which include a reduction of intracellular glutathione (GSH) predisposing the cell to oxidative damage32. With diminished reducing activity and a constant auto-oxidation rate of Hb, there is gradual accumulation of methemoglobin (metHb), a ferric (Fe3+) derivative of Hb, in the senescent RBC33. MetHb can be further oxidized to a ferryl (Fe4+) state under constant oxidative stress34. Such oxidative stress ultimately leads to Hb denaturation, band 3 clustering and autologous immunoglobulin G (IgG) binding and general stiffening which marks the RBC for splenic clearance32,35. RBCs in the ferric and ferryl states are paramagnetic and thus are responsible for the higher R2 relaxation rates of the marginated stiff aged RBCs collected at the side outlet.
Due to the margination of aged RBCs, there exists a substantial relative change in the relaxation rates, ΔR2 of the separated blood samples even for hRBCs (Fig. 4b). To overcome this challenge we lyse the RBC with saponin after margination but prior to the MRR measurement as this diminishes the relative difference in R2 relaxation rates between the blood samples collected at the inlet and middle, enabling us to establish a healthy baseline necessary for reliable diagnosis. Figure 5 shows the R2 values at the inlet, middle, side for three different healthy individuals using the saponin lysis method (see Methods). The box plots show the lower quartile, median and upper quartile of their respective sample distributions. For all three cases, we observed that, while the side R2 values remains significantly higher than the middle, the middle R2 values has become statistically non-distinguishable from the inlet R2 (two-tailed paired student t-test (n ≈ 10) P-values of 0.739, 0.905 and 0.636, respectively). Due to the variation in R2 values between measurements, it is necessary to take 5–10 measurements per sample to prevent false positives and false negatives, thus the MRR measurement time per sample is approximately 5–10 minutes. Lysing the iRBCs with saponin releases intact P. falciparum parasites from the membrane of erythrocytes and it would therefore be expected that these intact parasites would remain to provide a detectable increase in the R2 values during MRR measurements. If this is indeed correct, we expect that as iRBCs are marginated towards the sidewalls, the middle outlet is depleted of iRBCs. Hence, the middle R2 values would be expected to be significantly lower compared to the inlet while it would be statistically non-distinguishable if the sample contains only hRBCs.
Validation of the lysis method for reliable parasite detection
To establish whether the comparison of inlet vs middle outlet in combination with saponin lysis was able to reliably detect low level of parasites, we evaluated this approach using samples with different parasitemia. Figure 6(a–c) shows the R2 values of blood samples collected at inlet, middle and side for an iRBCs sample at parasitemia levels of 5%, 0.5% and 0.0005%. All these samples contained a mixed infection of 37% ring and 63% schizont. The box plots show the lower quartile, median and upper quartile of their respective sample distributions. For all three parasitemia levels, the R2 values of the middle is significantly lower than the inlet (t-test P-value < 0.05), while the side R2 is significantly higher than the middle. This confirms that the depletion of iRBC in the middle outlet can be directly measured using the saponin lysis approach even at parasitemia levels as low as 0.0005%, providing us with an important tool for malaria parasite detection. In contrast as shown in Fig. 6(d,e) FACS analysis of the different samples after margination but before saponin lysis is only able to provide data for the 5% and 0.5% sample as the 0.0005% sample is beyond its detection limit. The FACS data shows that as the iRBCs are marginated towards the side outlet and although the margination process does not remove all existing iRBCs from the middle channel (as shown in Fig. 6(d,e)), the parasitemia level at the middle outlet is significantly lower than both the inlet and side outlet.
Limit of detection for ring stage parasites
For any diagnostic approach it is crucial that it can detect solely circulating young ring stages as later stage iRBCs, trophozoites and schizonts, are usually sequestered in the deep tissues, leaving only early stage ring iRBCs in the human peripheral blood. We therefore evaluated the limit of detection using samples containing different proportions of ring (R), trophozoite (T) and schizont (S) stage parasites. Three samples at extremely low parasitemia level of 0.0005% parasitemia with a composition estimated by Giemsa microscopic observation and FACS of (a) (100% R, 0% T, 0% S); (b) (50% R, 50% T, 0% S); (c) (52% R, 0% T, 48% S) were tested. Fig. 7 shows the R2 values at the inlet, middle and side for the three samples of iRBCs. In all three cases, the R2 relaxation rates of the sample collected at the middle outlet are significantly lower (P-value < 0.05) compared to the inlet. As seen in Fig. 7(a), even for the 100% ring sample, statistically significant (P-value is 0.0444) differences between the inlet and middle outlet sample can be detected. This confirms that the malaria diagnostic technique that combines the use of microfluidic separation and MRR system is able to detect early malaria infection at the parasitemia level of 0.0005%, without prior determination of patient-specific healthy baseline.
We have successfully developed a malaria diagnosis technique that combines the use of microfluidics for the separation of iRBCs and MRR system for a rapid, label-free detection of malaria parasites. The iRBCs are separated from the hRBCs through margination - a naturally occurring hemodynamic phenomenon where more deformable hRBCs experience a lateral migration towards the axial centre of the microchannel, displacing stiffer iRBCs to the sidewalls of the margination channel. Crucially we have demonstrated that this approach is capable of reliably detecting ring stage parasites at parasitemia as low as 0.0005%. In the near future, a Lab-on-a-Chip solution with MRR functionality integrated is envisaged for malaria diagnosis in the clinical setting. Both margination-based microfluidic separation system and MRR detection system have a room for further optimization, which will bring about more sensitive diagnostics, and, potentially, earlier detection of malaria cases. While the cost of the miniaturized MRR system maybe still expensive (several thousand US dollar) for developing nations, the cost per assay (<50 cents) is affordable. Pushing the detection sensitivity of malaria parasite to the lowest level possible would have significant implication in the clinical management of malaria in endemic areas, especially in the light of the possibility of latent, extremely low level parasitemia in non-symptomatic populations.
Cell margination is a naturally occurring hemodynamic phenomenon36 in our microcirculatory system
Stiffer nucleated white blood cells (leukocytes) are segregated towards the vessel wall to initiate leukocyte rolling, adhesion and extravasation at the blood vessel wall’s endothelia cells of the injury inflammation site37. The same margination principle could also be applied to displace stiffer malaria iRBCs towards the sidewalls (inset of Fig. 1(a))25. The margination effect is primarily attributed to RBCs axial migration resulting from wall induced migration and shear-induced diffusion38. In a wall-bound Poiseuille shear flow, deformable RBCs undergo change in shape and experience an inwardly directed wall induced pressure gradient due to the velocity difference in the laminae of the sheared suspension25,39,40. These wall-induced migration pressure gradient tend to push the RBCs away from the channel wall towards the axial center of the microfluidic channel, leaving a cell depleted plasma layer near the channel wall - the Fahraeus effect38,41,42. The stiffer iRBCs are more spherical in shape and experience smaller wall induced lift velocities than the hRBCs41. On the other hand, the shear induced diffusion due to the hydrodynamic interactions and mechanical collisions between the RBCs in the shear flow displace the stiffer malaria iRBCs towards the sidewall41.
While hRBCs are highly deformable, the iRBCs stiffen upon invasion of the large non-deformable intracellular parasite and changes its morphological, mechanical and electrical properties43,44. Furthermore, the parasite releases proteins that trigger the cross-linking of the spectrin network in the iRBC’s phospholipid bilayer membrane, thus increases the rigidity of the iRBCs45. The elastic modulus of ring, trophozoite and schizont are approximately 2, 2.7 and 6.7 times higher than the hRBC, respectively (Table 1)27. Therefore, through the biomimetic margination microfluidic separation device, we could effectively segregate the stiffer iRBCs towards the side outlet of the channel, while the blood sample collected at the middle outlet is depleted of iRBCs (Fig. 1(a)). Subsequently, we perform the relative R2 measurements with a bench-top 0.5 T MRR system (Fig. 1(b)).
The microfluidic margination device comprises of two microfluidic components: a margination layer and a cover layer. Due to the narrow cross-section and relatively long nature of the margination channel, the fluidic resistance for the margination channel is high. Thus, the maximum achievable flow rate is limited and subsequently limits the ability for high throughput margination. In order to increase the throughput and reduce the processing time of the microfluidic separation step, we opt to perform multiplex margination. The margination layer consists of seven parallel margination channels, each with a width of 50 μm, a thickness of 10 μm and a length of 2 cm. Figure 2(a) shows the schematic diagram for the design of the microfluidics margination device. At the end of each margination channel, the blood streams are separated into a bifurcation channel configured in a 1:2:1 manner (Fig. 2(c)). The hRBCs tend to move to the axial center of the microfluidic channel and exit through the middle outlet, while the stiffer iRBCs are segregated to the channel sidewalls and exits through the side outlets. In addition, we have also implemented multiple microstructures and pillars with gaps ranging from 25 μm to 200 μm. Figure 2(b) shows the magnified view of the filtration units at the inlet. These microstructures and pillars act as the filtration unit at the inlet to effectively trap any coagulated blood or debris that might block the narrow margination channel should they be allowed to pass through the microchannel. The cover layer consists of two large microchannels (transparent rectangular channels shown in Fig. 2(a) and is then aligned and bonded on top of the margination layer. The purpose of cover layer is to eliminate the need of connecting 14 tubings for blood collection at the outlets. The bloods from the middle and side outlets are pooled and exits via two large microchannels of the cover layer. The yellow circles indicate the tubing ports’ location for the inlet, middle and side outlets of the margination device.
The microfluidic margination device was fabricated in polydimethylsiloxane (PDMS) using standard photolithography technique. An approximately 10 μm thick SU8-3005 (Micro-Chem Inc., USA) negative photoresist was spin-coated onto a 4” silicon wafers at 500 rpm for 10 s with an acceleration of 100 rpm s−1, followed by 750 rpm for 30 s with an acceleration of 300 rpm s−1. The substrate was then soft-baked at 65 °C for 1 minutes and 95 °C for 3 minutes. UV exposure was performed with a mask aligner (MJB-4, SussMicrotec, Germany) at 200 mJ cm−2 for 16 s. Subsequently, post exposure bake is carried out at 65 °C for 1 minutes and 95 °C for 2 minutes. The substrate is then developed for 2 minutes. PDMS with a 10:1 mixture ratio for base and curing agent (Sylgard 184, Dow Corning Inc., USA) was casted onto the SU8 master and cured at 80 °C for 8 hours. Inlet and outlets ports were punched with a 0.75 mm PDMS puncher (Harris-Unicore Inc., USA) on the cured PDMS device. Finally, the PDMS device was cleaned in an ultrasonic cleaner with ethanol and DI-water for 15 minutes, respectively. The entire process was repeated to fabricate the PDMS chip that contains the cover layer.
After fabricating the PDMS chips for both the margination layer and cover layer, the next step was to assemble the multilayer microfluidic separation device. First, the microfluidics chip that contain the margination layer was bonded onto a pre-cleaned microscope glass slide (75 mm × 50 mm, Corning Inc., USA) with a plasma bonder (Covance, Femto Science Inc., South Korea) for 90 s. Second, the PDMS chip that contains the cover layer was then visually aligned and bonded onto the top surface of the PDMS chip containing the margination layer. The assembled microfluidic device was then kept in an oven at 80 °C for 8 hours to improve the PDMS bonding strength. Lastly, a tubing with a G23 needle end was inserted into the inlet and sealed with epoxy glue (Selleys Araldite Inc., Australia) to enhance the sealing.
Healthy non-malarial immune adult volunteer blood donors were recruited and brought to the National University Hospital of Singapore Blood Bank for phlebotomy services. The protocol was approved by the Institutional Review Board of National University of Singapore (NUS-IRB 10-285). Informed consent was taken from all volunteers and the methods were carried out in accordance with the approved protocol and guidelines. Whole venous blood was collected in Citrate-Phosphate-Dextrose-Adenine-1 (CPDA-1, JMS). The white blood cells (leukocyte) were removed via centrifugation and the removal of the buffy coat layer. Malaria parasites, P. falciparum strain 3D7 (MR4, USA) was cultured at 2.5% haematocrit using human erythrocytes in malaria culture media (10.43 g RPMI 1640 powder (Gibco, USA), 25 mL 1 M HEPES (Gibco, USA), 2 g NaHCO3 (Sigma-Aldrich, USA), 5 g AlbuMAX® (Gibco, USA), 0.05 g of hypoxanthine (Sigma-Aldrich, USA) in 1 mL of 1 M NaOH and 25 mg gentamicin (Gibco, USA) in 1 L milli-Q water)46. Cultures were kept in a Heracell 150 incubator (Thermo Scientific, USA) at 37 °C in an atmosphere of 5% CO2, 3% O2 and 92% N2. Ring stage parasites were synchronized using 2.5% D-sorbitol, while schizont stage parasites were purified using differential Percoll gradient centrifugation46. The parasitemia of the parasite culture was quantified either by standard Giemsa-staining of blood smear or by flow cytometry. For flow cytometry analysis, infected erythrocytes were fixed in 4% formaldehyde, followed by permeabilization with 0.5% v/v saponin solution in flow buffer (0.2% bovine serum albumin (BSA), 0.05% sodium azide in 1 × phosphate buffer solution (PBS)). Thereafter, parasite’s DNA was stained using Hoechst 33342 at a concentration of 20 μg mL−1 (Thermo Scientific, USA).
When the parasitemia of the iRBCs reaches ~10%, the infected blood sample is washed with 1 × PBS three times to remove the culture media and resuspended in 1 × PBS at 10% hematocrit. Subsequently, we prepare an infected blood sample at 5% parasitemia by spiking the corresponding amount of iRBCs into hRBCs from a healthy donor. The 5% parasitemia blood sample is then serially diluted with hRBCs to obtain blood samples with lower parasitemia of 0.5%, 0.05%, 0.005% and 0.0005%. The hematocrit of the blood samples are then adjusted to 45–50% for the microfluidic margination process. The R2 relaxation rates of the blood samples can be measured by two methods: (a) “spin-down” and (b) “lysis” methods. In the “spin-down” method, the samples are loaded into heparinized microcapillary tubes (22–260–950, Fisher Scientific, USA) via capillary forces. The microcapillary tubes are then sealed with a vinyl-plastic compound (Critoseal, Krackeler Scientific,USA) and centrifuged (Sorvall Legend Micro 21, Thermo Scientific, USA) at 13,000 g for one minutes. A total spun down cell volume of 4 μL is required for each MRR measurement. On the other hand, the procedure for the “lysis” method is similar to the “spindown” method except that the blood cells are lysed before being transferred into the microcapillary tubes for MRR measurements. First, the total volume of blood cells suspended in 1 × PBS required for obtaining a spun down cell volume of 4 μL is determined. Subsequently, the blood sample is centrifuged at 3,000 g for one minute. A portion of the supernatant of the sample is removed such that the total sample volume is 15 μL. The blood sample is then lysed with 5 μL of 1% v/v saponin lysis buffer (Sigma-Aldrich, USA).
Prior to the experiment, the microfluidic margination device is primed with 1 × PBS supplemented with 0.5% v/v BSA. The blood sample is filled in a 1 mL glass syringe (Hamilton Inc., USA) and pumped into the margination device with a syringe pump (Fusion 400, Chemyx Inc., USA) at total flow rates ranging from 7 μL min−1 to 70 μL min−1 with flexible Tygon© tubing (0.02” × 0.06”, 06419-01, Cole-Parmer Inc., USA). The flow of the iRBCs and hRBCs are observed under an inverted epi-fluorescence microscope (Olympus IX71, Olympus Inc., Japan) equipped with a high speed CCD camera (Phantom v9, Vision Research Inc., USA). The marginated blood samples are then collected from the middle and side outlets in 1.5 mL microcentrifuge tubes. We evaluated the performance of the margination separation device by running FACS analysis with a BD™ LSR II flow cytometer (BD Biosciences, USA) on the collected blood samples. The data from the cytometer is then analyzed with FACS Diva (BD Biosciences, USA) and FlowJo (TreeStar Inc., USA).
The proton 1H transverse relaxation rate, R2 of the blood samples from the middle and side outlets are measured with a bench-top nuclear magnetic resonance spectrometer (Kea2, Magritek, New Zealand). The microcapillary tubes containing the blood samples are slotted into an impedance matched 1 mm rf-probe tuned at a resonance frequency of 21.57 MHz. The rf-probe is subsequently placed inside a ~0.5 T permanent magnet (Metrolab Instruments, Switzerland) and connected to the bench-top spectrometer for proton 1H MRR measurements (Fig. 1(b)). The R2 relaxation rates are measured using standard Carr-Purcell-Meiboom-Gill (CPMG) pulse sequence with 5000 echoes, 200 μs inter-echo time, transmitter power output of 6.25 mW and 6 μs 90°-pulse length. A total of 24 scans are acquired for signal averaging and the system is maintained at 26 °C via an external temperature controller. The R2 measurement of each blood sample is repeated 5–10 times with independent microcapillary tubes.
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This work is supported by Singapore - MIT Alliance for Research and Technology (SMART) Centre, BioSystems and Micromechanics (BioSyM) IRG and Infectious Disease (ID) IRG Singapore. T. F. K and W. Y. would like to thank the SMART graduate fellowship for the financial supports.
The authors declare no competing financial interests.
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Fook Kong, T., Ye, W., Peng, W. et al. Enhancing malaria diagnosis through microfluidic cell enrichment and magnetic resonance relaxometry detection. Sci Rep 5, 11425 (2015). https://doi.org/10.1038/srep11425
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