Transdermal Diagnosis of MalariaUsing Vapor NanobubblesEkaterina Lukianova-Hleb, Sarah Bezek, Reka Szigeti, Alexander Khodarev, Thomas Kelley,Andrew Hurrell, Michail Berba, Nirbhay Kumar, Umberto D’Alessandro, Dmitri LapotkoA fast, precise, noninvasive, high-throughput, and simpleapproach for detecting malaria in humans and mosquitoesis not possible with current techniques that depend on bloodsampling, reagents, facilities, tedious procedures, andtrained personnel. We designed a device for rapid (20-second)noninvasive diagnosis of Plasmodium falciparum infectionin a malaria patient without drawing blood or usingany reagent. This method uses transdermal optical excitationand acoustic detection of vapor nanobubbles aroundintraparasite hemozoin. The same device also identified individualmalaria parasite–infected Anopheles mosquitoes ina few seconds and can be realized as a low-cost universaltool for clinical and field diagnoses.Malaria control and elimination would benefit greatlyfrom an efficient and universal diagnostic tool thatis fast (provides results in seconds), noninvasive and safe(uses no blood sampling or reagents), simple to use (can beoperated by nonmedical personnel), sensitive and specific(detects low-level asymptomatic infections), and inexpensiveand that detects malarial infection in humans and inmosquitoes (1–21). We recently proposed a transdermalblood- and reagent-free approach based on hemozoin-generatedvapor nanobubbles (H-VNBs) (22) in which malariaparasite–specific endogenous nanocrystals of hemozoin areoptically excited in vivo with a safe and short laser pulse(delivered to blood vessels through the skin). The light isconverted into nonstationary localized heat that evaporatesthe adjacent nanovolume of liquid and thus generates anexpanding and collapsing vapor nanobubble inside the parasite.The nanosize and high optical absorbance of hemozoinprovide higher malaria infection specificity of theseAuthor affiliations: Rice University, Houston, Texas, USA(E. Lukianova-Hleb, D. Lapotko); Baylor College of Medicine,Houston (S. Bezek, R. Szigeti); Ben Taub General Hospital,Houston (S. Bezek, R. Szigeti); X Instruments LLC, Fremont,California, USA (A. Khodarev); Precision Acoustics Ltd, Dorset,UK (T. Kelley, A. Hurrell); Standa UAB, Vilnius, Lithuania(M. Berba); Tulane University, New Orleans, Louisiana, USA(N. Kumar); Medical Research Council, Banjul, The Gambia(U. D’Alessandro); London School of Hygiene and TropicalMedicine, London, UK (U. D’Alessandro)DOI: http://dx.doi.org/10.3201/eid2107.150089H-VNBs than does any normal blood and tissue components(23–26). Their transient expansion and collapse result in anoninvasive pressure pulse that is easily detected throughthe skin with an ultrasound sensor. In our preliminary studies(22), H-VNBs detected parasitemia as low as 0.0001%in vitro (human blood), and 0.00034% in vivo (transdermaldetection in animals), with no false-positive signals.Therefore, H-VNB might be able to detect extremely lowparasite densities provided the method can be applied tohumans or mosquitoes simply and inexpensively.To determine the technical and medical feasibility ofH-VNBs for malaria diagnosis and screening, we prototypeda diagnostic device and evaluated it in a patient withconfirmed malaria and in noninfected persons as controls.We also evaluated the device in Plasmodium falciparum–infected mosquitoes.Materials and MethodsPrototype Design and AlgorithmsThe laboratory prototype (Figure 1, panel A) comprisedthe newly designed compact low-cost pulsed laser (532nm, 10 μJ, 200 ps; Standa, Vilnius, Lithuania). The laserpulse is delivered to the skin by the combination probeat the fluence 36 mJ/cm 2 (Figure 1, panel B). The probewas developed for transdermal diagnostics and includesan optical fiber guide and a custom acoustic sensor witha preamplifier that is integrated in 1 compact hand-heldunit. In response to each laser pulse, the probe detects anacoustic pulse and generates an output electrical signal asan acoustic trace (Figure 1). Its output signals were collectedand analyzed with custom-designed software (NILabVIEW, Austin, TX, USA) by using a signal amplifier,digital oscilloscope (LeCroy 42X; Teledyne LeCroy, NY,USA), and computer. The peak-to-peak amplitude A of theacoustic trace obtained in response to each laser pulse wasmeasured and presented as a histogram for 400 sequentiallaser pulses. A malarial infection–negative trace histogramwas used to determine “the malaria threshold” T as themaximum amplitude for the malarial infection–negativesignal. Any trace with an amplitude above that thresholdwas considered to be hemozoin (malarial infection)–positive.To quantify the infection, we counted the incidencerate of malarial infection–positive traces IR (the probability1122 Emerging Infectious Diseases • www.cdc.gov/eid • Vol. 21, No. 7, July 2015
Transdermal Diagnostics of MalariaFigure 1. A) Experimentallaboratory prototype of a malariadiagnostic device with the pulsedlaser and the integrated probeshown being scanned acrossa human wrist. B) Functionaldiagram of the prototype and theprinciple of transdermal opticalexcitation and acoustic detectionof vapor nanobubbles aroundhemozoin in malaria-infectedcells exposed to the laserpulses (green arrows). H-VNB,hemozoin-generated vapornanobubble.of the trace incidence with an amplitude above the malariathreshold calculated for 400 laser pulses) and calculated theHemozoin Index (HI) (22): HI = IR(A – T).Monitoring of Transient Vapor NanobubblesThe direct monitoring of transient vapor nanobubbles inresponse to a single laser pulse uses our optical scatteringmethod (27,28). This method used time-resolved opticalscattering of a probe continuous laser beam of verylow power (633 nm, 0.1 mW). The probe laser beam wasfocused on the blood sample collinearly with the excitationlaser pulse. The axial intensity of the probe laser beamthat passed through the blood sample was monitored witha photodetector. The response to the laser pulse includedbulk heating and generation of a transient vapor nanobubble.The bulk heating of the exposed blood volume (withoutgeneration of a vapor nanobubble) was detected opticallyby using a thermal lensing effect that revealed the fastheating and gradual cooling of the exposed volume (Figure2, panel A, black line in inset). The generation of an expandingand collapsing vapor nanobubble created a stronglocalized scattering of the probe laser beam by the vapor–liquid boundary, and this effect reduced the probe beamintensity with the bubble diameter (Figure 2, panel A, redline in inset). A vapor nanobubble–specific signal typicallyis shaped like an inverted bell and represents the growthand collapse of the bubble.Patient with Confirmed MalariaThe patient was admitted to Ben Taub General Hospital,Harris Health System (Houston, TX, USA), with fever,myalgia, abdominal pain, nausea, and vomiting for theprevious 4 days and no history of malaria chemoprophylaxis.Malaria identification and speciation was done by microscopy(thin, Wright-Giemsa–stained, peripheral bloodsmears) and a rapid malaria antigen test (BinaxNow Malaria;Alere Scarborough, Inc., Scarborough, ME, USA). Bothtests confirmed a P. falciparum malaria infection. By thetime of the H-VNB test, the patient had already receivedantimalarial drugs (doxycycline, malarone, quinidine, andquinine) for 24 h. During hospitalization, the patient hadmild hemolytic anemia and thrombocytopenia, neither ofwhich required transfusion of blood products. In additionto the antimalarial medications and to provide symptomaticrelief, the patient received intravenous fluids, antiemetics,and antipyretics.Diagnostic LocationsWe found wrist and ear lobe veins to be the optimal locationfor the test. Fingertips were also explored but wereinadequate because some persons develop very thick andrigid skin patterns that prevent efficient transdermal deliveryof a laser pulse to the blood vessels.Influence of Skin ToneThe difference between the amplitudes of the in vitro backgroundtraces from intact blood (Figure 2, panel B, blackbars) and those in vivo from a malaria-negative volunteer(Figure 2, panel D, black bars) accounts for the additionalcontribution of the optical absorbance by melanin in darkskin. The increase in the bulk optical absorbance consequentlyincreased the bulk transient heating (without thegeneration of H-VNBs) and thus increased the averagetrace amplitude of the background trace from 10.7 ± 1.7mV in blood alone (in vitro) to 18.1 ± 5.4 mV in bloodand skin (in human) as can be seen by comparing the blackhistograms in Figure 2, panels B and D. We further studiedthe influence of skin tone on the background trace in5 healthy volunteers with different skin tones (Figure 2,panel F). For 532-nm wavelength light, the predictable increasein the background trace amplitude resulted from thehigher concentration of the skin pigment, melanin, whichdetermines skin darkness (tone). Therefore, in malaria diagnosis,reference malaria-negative data (histogram andthreshold) should be linked to the same level of skin toneas in the malaria patient. Although the optical absorbanceEmerging Infectious Diseases • www.cdc.gov/eid • Vol. 21, No. 7, July 2015 1123
- Page 3 and 4: July 2015SynopsisOn the CoverMarian
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