Superparamagnetic iron oxide nanoparticle attachment on array of micro test tubes and microbeakers formed on p-type silicon substrate for biosensor applications
- Sarmishtha Ghoshal†1,
- Abul AM Ansar1,
- Sufi O Raja2,
- Arpita Jana1,
- Nil R Bandyopadhyay1,
- Anjan K Dasgupta2 and
- Mallar Ray†1Email author
© Ghoshal et al; licensee Springer. 2011
Received: 17 July 2011
Accepted: 4 October 2011
Published: 4 October 2011
A uniformly distributed array of micro test tubes and microbeakers is formed on a p-type silicon substrate with tunable cross-section and distance of separation by anodic etching of the silicon wafer in N, N-dimethylformamide and hydrofluoric acid, which essentially leads to the formation of macroporous silicon templates. A reasonable control over the dimensions of the structures could be achieved by tailoring the formation parameters, primarily the wafer resistivity. For a micro test tube, the cross-section (i.e., the pore size) as well as the distance of separation between two adjacent test tubes (i.e., inter-pore distance) is typically approximately 1 μm, whereas, for a microbeaker the pore size exceeds 1.5 μm and the inter-pore distance could be less than 100 nm. We successfully synthesized superparamagnetic iron oxide nanoparticles (SPIONs), with average particle size approximately 20 nm and attached them on the porous silicon chip surface as well as on the pore walls. Such SPION-coated arrays of micro test tubes and microbeakers are potential candidates for biosensors because of the biocompatibility of both silicon and SPIONs. As acquisition of data via microarray is an essential attribute of high throughput bio-sensing, the proposed nanostructured array may be a promising step in this direction.
The promotion of silicon (Si) from being the key substrate material for microelectronic devices to a potential light emitter emerged as a consequence of the possibility to reduce its dimension by different techniques [1–3]. Extensive research in this field was triggered after the discovery of light emission from electrochemically etched porous Si . Research on porous Si has so far been primarily focused on microporous Si which have average pore diameter ≤2 nm , exhibit room temperature photoluminescence (PL) and consequently hold immense promise for potential light sources in opto-electronic devices. However, macroporous Si with typical pore diameters > 50 nm , do not exhibit PL but has found niche applications in the field of photonics , sensor technology and biomedicine [6, 7]. Macroporous Si can potentially be used as a sensitive transducer material for detection of various biological and non-biological samples as its conductivity, capacitance, and/or refractive index changes upon adsorption of molecules on its surface [8, 9]. Porous Si can also be permeated by different molecules leading to specific properties depending on the deposited substance and their morphology [10, 11]. Because of its non-invasive and non-radioactive nature, porous Si promises versatile applications in medical diagnostics, pathogen detection, gene identification, and DNA sequencing [11, 12]. The non-toxic behavior of porous Si makes it particularly suitable for biosensor applications including drug delivery platform for in vivo applications [10, 13]. Extensive reviews on the scope of porous Si in nanobiotechnology have been reported in the literature [6, 11, 14].
For biological applications, porous Si structures with ordered arrangement of pores having diameters approximately 1 μm are desirable for loading molecules and drugs within the pores. Uniform macropore formation and its dependence on the formation parameters have been well reported [15, 16]. Fewer Fabry-Perot fringes were observed for porous Si sensors fabricated at higher current densities because of greater porosity leading to matte surface . Thus, engineering a uniform structure of macropores (approximately 1 μm in diameter), each of which appears as a micro test tube is very desirable for building porous Si-based biochips or biosensors. In addition, porous Si is known to be a suitable material for implementing an efficient and reliable surface-enhanced Raman scattering (SERS) substrate that can be used to detect the presence of chemical and biological molecules [18, 19]. However, to make an SERS substrate, complete filling of the pores is undesirable as the exposed surface area is reduced and thus the target molecule may simply attach on the top surface. Nano-sized Si pillars (< 100 nm in width) with comparatively larger pores (> 1.5 μm in diameter), appear as microbeakers on porous Si, which provide a very convenient platform for SERS substrate. These microbeakers can be coated completely without filling the pores for various bio-sensing applications.
In first part of this work, we report fabrication of arrays of micro test tubes and microbeakers formed on p-type Si substrate with varying pore and particle sizes. For the micro test tubes, the pore size as well as the inter-pore distance is typically 1 μm (approximately), whereas, for a microbeaker the pore size exceeds 1.5 μm and the inter-pore distance could be less than 100 nm. Even with very thin Si walls, the microbeakers were found to be quite stable under ambient conditions. In the next part of this work, we successfully synthesized and attached superparamagnetic iron oxide nanoparticles (SPIONs) on the porous Si surface as well as on the pore walls using a simple and cost-effective technique. SPIONs have demonstrated their utility as non-invasive molecular probes to monitor biological processes, particularly by enhancing magnetic resonance (MR) contrast in MR imaging which allows monitoring of anatomical changes as well as physiological and molecular changes [20, 21]. Therefore, such robust micro test tubes and microbeakers formed on Si substrates with SPION attachment promises to have immense applications in biomedicine and biomedical sensing due to biocompatible nature of both the materials [22, 23].
Macroporous Si were formed on (100) orientation, p-type Si wafers in a specially designed teflon bath by anodic etching in hydrofluoric acid (HF) and N, N-dimethylformamide (DMF) solution. To obtain porous Si with different morphology, wafers of varying resistivity (ρ) ranging from 0.01 to 100 Ω-cm were used. The concentration ratios of HF/DMF, formation current density (J), etching time (t) were also varied to obtain porous layers having different porosity. SPIONs were synthesized by chemical co-precipitation of ferrous and ferric ion. Briefly, ferric and ferrous chlorides were dissolved in 2 M HCl in 2:1 (w/w) ratio and bare iron oxide was obtained by addition of 1.5 M NaOH. All steps were performed under nitrogen environment. The formed black precipitate was washed several times by de-ionized (DI) water through magnetic decantation to remove excess ions. Then the precipitate was re-dispersed in citrate buffer of pH 4 and finally pH was adjusted to 7 to form aqueous stable colloidal SPION solution. The as-synthesized SPIONs were loaded onto the desired porous Si chips by placing the porous template in a dense aqueous solution of SPIONs under magnetic incubation for 24 h. An external magnetic field of 70 Gauss was applied so as to drive the SPIONs inside the pores. This was repeated twice, first without disturbing the system and secondly, by spraying DI water on the chip at certain intervals during magnetic incubation so that the particles can penetrate inside the pores without adhering on the surface only, due to drying up of the aqueous SPION solution.
Macroporous Si samples (with and without SPION attachment) were investigated with the scanning electron microscope (SEM). The SEM used in the present study is a Hitachi S-3400N. The variable pressure mode of the instrument allowed investigation of the semiconducting samples in their natural state without the need of conventional sample preparation and coating. The microscope was operated at 20 to 30 kV and 10 to 5 mm working distance under variable pressure. Elemental analyses (qualitative) were done from the energy dispersive X-ray (EDX) spectra. Dynamic light scattering (DLS) and laser Doppler velocimetry (LDV), for determining the hydrodynamic size and the zeta potential respectively of the as-synthesized SPIONs in solution, were performed on a Malvern Instruments Zetasizer (5 mW HeNe laser, λ = 632 nm). The operating procedure was programmed such that there were averages of 25 runs, each run being averaged for 15 s, with an equilibration time of 3 min at 25°C. The magnetic properties of the SPIONs were investigated using a superconducting quantum interference device magnetometer (Model: MPMS-Quantum Design7).
Results and discussions
Formation of micro test tubes and microbeakers
Several models regarding the mechanism of formation of macropores on p-type Si has so far been reported. The depletion and field effects model proposed by Lehmann and Rönnebeck , the chemical passivation model , the current burst model , etc. have been widely used, but a real consensus in this matter is still awaited. However, before commenting on the probable mechanism governing pore formation, we first note the major observations generated in this study with respect to the effect of wafer resistivity on pore morphology, which is partly reflected in the images shown in Figure 1: (1) the thickness of the macropore walls are greatly reduced with decrease in resistivity of the starting substrate; (2) for given current density and HF/DMF ratio, inter-pore spacing increases but the pore density decreases with increase in resistivity of the substrate; (3) the pore diameter also decreases with decreasing resistivity (though on comparing Figure 1a with either c or d this might seem contradictory, one has to note that the voids seen in Figure 1a are due to more than one interconnected pores); (4) there is probably some critical threshold resistivity (approximately 0.1 to 0.2 Ω-cm in our case) below which no macropore can be obtained; and (5) the geometry of the cross-section of the pore (roughly circular or hexagonal or rectangular) can be tailored by choosing different resistivity wafers. In addition, we also observed, in agreement with previous reports [5, 15, 16] that for a wafer of given resistivity, the pore diameter increases almost linearly with formation current density, whereas etching time primarily governs the pore-depth. The effect of HF concentration and HF/DMF ratio is relatively complex and is discussed elsewhere . The presence of DMF in the electrolyte plays an important role in the formation process as it is a very good solvent for positive charge carriers . The high concentration of DMF increases hole current at the pore walls causing widening of the pores. Therefore, for the low resistivity (ρ = 0.1 to 0.5 and 2 to 5 Ω-cm) samples, porous structure could be obtained only when both the current density and HF/DMF ratio were maintained at lower values.
Since the purpose of this work is to synthesize array of micro test tubes and microbeakers of Si for biological applications, and not on investigating the pore formation mechanism in p-Si, we refrain from making any assertive comments on this controversial issue. However, from the above observations, it seems likely that charge-transfer mechanisms similar to that of a Schottky diode in case of anodic etching of p-Si, in which case the holes migrate through the wafer towards the electrolyte/Si interface where the space charge region is formed, as suggested by the model of Lehmann and Rönnebeck , is in all possibility the dominant mechanism. The more-or-less square-root dependence of pore wall thickness on resistivity provides initial support to this model, whereas the variation of geometry of cross-section of the pore is suggestive of non-linear dissolution kinetics. A detailed analysis of the mechanism would no doubt depend on the systematic investigation of the role of each formation parameter and their interdependence, which warrants a separate investigation. Therefore, we focus only on the samples shown in Figure 1c, d for synthesis of microbeakers and micro test tubes.
From the SEM image shown in Figure 2a, it is clear that microbeakers are formed on p-Si with distinct large pores having diameter around 1.5 μm along with very narrow inter-pore Si walls (approximately 100 nm). Whereas, Figure 2b reveals that a regular array of micro test tubes with length exceeding 45 μm and inter-pore distances around 1 μm is also obtainable on p-Si substrate. From the discussion presented before, it is obvious that the length of the pores in both cases can be controlled primarily by tailoring the etching time while the pore diameter, pore density, and consequently the inter-pore distances are easily controlled by varying the formation current density and HF/DMF ratio. This allows us to synthesize arrays of microbeakers and micro test tubes on p-Si substrate with desired lengths and cross-sections by suitably tuning the formation parameters.
Superparamagnetic iron oxide nanoparticles
SPION attachment on macroporous silicon
In summary, we have demonstrated successful fabrication of a uniformly distributed array of micro test tubes and microbeakers on p-type Si substrates with tunable dimensions. Iron oxide nanoparticles, with average particle size approximately 20 nm, synthesized using chemical co-precipitation and exhibiting superparamagnetic characteristics, were attached to the surface and to the walls of these micro test tubes and microbeakers without completely filling the pores. Such robust and cost-effective SPION attached micro test tubes and microbeakers formed on Si substrates have immense applications in biomedical sensing due to biocompatible nature of both the materials. By loading such SPIONs with designed sequences of DNA at specific ensemble of the nanopores may upgrade the system to a nano-designed array, the specific details of which is presently under progress.
SG acknowledges Department of Science and Technology (DST), India for financial support under WOS-A scheme. NRB and MR thank DST, India, Australia-India Strategic Research Fund for providing financial support. The authors would also like to thank ICMR (35/24/2010/BMS-NANO dated 3/11/2010) for partial support of the research.
- Canham LT: Silicon quantum wire array fabrication by electrochemical and chemical dissolution of wafers. Appl Phys Lett 1990, 57: 1046–1048. 10.1063/1.103561View ArticleGoogle Scholar
- Cullis G, Canham LT: Visible light emission due to quantum size effects in highly porous crystalline silicon. Nature 1991, 353: 335–338. 10.1038/353335a0View ArticleGoogle Scholar
- Wilson WL, Szajowski PF, Brus LE: Quantum confinement in size-selected, surface-oxidized silicon nanocrystals. Science 1993, 262: 1242–1244.View ArticleGoogle Scholar
- Rouquerol J, Avnir D, Fairbridge CW, Everett DH, Haynes JH, Pernicore N, Ramsey JDF, Sing KSW, Unger KK: Recommendations for the characterization of porous solids. Pure Appl Chem 1994, 66: 1739–1758. 10.1351/pac199466081739View ArticleGoogle Scholar
- Lehmann V: Trends in fabrication and applications of macroporous silicon. Phys Stat Solidi (a) 2003, 197: 13–15. 10.1002/pssa.200306513View ArticleGoogle Scholar
- Batty CA: Porous silicon: a resourceful material for nanotechnology. Recent Patents on Nanotechnology 2008, 2: 128–136. 10.2174/187221008784534514View ArticleGoogle Scholar
- Saha H, Dey S, Pramanik C, Das J, Islam T: Porous silicon-based smart sensors. In Encyclopedia of Sensors. Volume 8. Edited by: Grimes CA, Dickey EC, Pisako MV. American Scientific Publishers; 2006:163–196.Google Scholar
- Lin VSY, Motesharei K, Dancil KPS, Sailor MJ, Ghadiri MR: Porous silicon-based optical interferometric biosensor. Science 1997, 278: 840–843. 10.1126/science.278.5339.840View ArticleGoogle Scholar
- Reddy RRK, Chadha A, Bhattacharya E: Porous silicon based potentiometric triglyceride biosensor. Biosens Bioelectron 2001, 16: 313–317. 10.1016/S0956-5663(01)00129-4View ArticleGoogle Scholar
- Anglin EJ, Cheng L, Freeman WR, Sailor MJ: Porous silicon in drug delivery devices and materials. Adv Drug Deliv Rev 2008, 60: 1266–1277. 10.1016/j.addr.2008.03.017View ArticleGoogle Scholar
- Granitzer P, Rumpf K: Porous Si - a versatile host material. Materials 2010, 3: 943–998. 10.3390/ma3020943View ArticleGoogle Scholar
- Stewart MP, Buriak JM: Chemical and biological applications of porous silicon technology. Adv Mater 2000, 12: 859–869. 10.1002/1521-4095(200006)12:12<859::AID-ADMA859>3.0.CO;2-0View ArticleGoogle Scholar
- Salonen J, Kaukonen AM, Hirvonen J, Lehto VP: Mesoporous silicon in drug delivery applications. J Pharmaceutical Sci 2008, 97: 632–653. 10.1002/jps.20999View ArticleGoogle Scholar
- Ghoshal S, Mitra D, Roy S, Majumder DD: Biosensors and biochips for nanomedical applications: a review. Sensors and Transducers 2010, 113: 1–17.Google Scholar
- Vyatkin A, Starkov V, Tzeitlin V, Presting H, Konle J, Konig U: Random and ordered macropore formation in p-type silicon. J Electrochemical Soc 2002, 149: G70-G76. 10.1149/1.1424898View ArticleGoogle Scholar
- Harraz FA, Kamada K, Kobayashi K, Sakka T, Ogata YH: Random macropore formation in p-type Silicon in HF-containing organic solutions: host matrix for metal deposition. J Electrochemical Soc 2005, 152: C213–220. 10.1149/1.1864292View ArticleGoogle Scholar
- Janshoff A, Dancil KPS, Steinem CDP, Greiner DP, Lin VSY, Gurtner C, Motesharei K, Sailor MJ, Ghadiri MR: Macroporous p-type silicon Fabry-Perot layers, fabrication, characterization, and applications in biosensing. J Am Chem Soc 1998, 120: 12108–12116. 10.1021/ja9826237View ArticleGoogle Scholar
- Chan S, Kwon S, Koo TW, Lee LP, Berlin AA: Surface-enhanced Raman scattering of small molecules from silver coated silicon nanopores. Adv Mater 2003, 15: 1595–1598. 10.1002/adma.200305149View ArticleGoogle Scholar
- Jiao Y, Koktysh DS, Phambu N, Weiss SM: Dual-mode sensing platform based on colloidal gold functionalized porous silicon. Appl Phys Lett 2010, 97: 153125–153127. 10.1063/1.3503608View ArticleGoogle Scholar
- Thorek DLJ, Chen AK, Czupryna J, Tsourkas A: Superparamagnetic iron oxide nanoparticle probes for molecular imaging. Ann Biomed Eng 2006, 34: 23–38. 10.1007/s10439-005-9002-7View ArticleGoogle Scholar
- Kim DK, Zhang Y, Voit W, Rao KV, Kehr J, Bjelke B, Muhammed M: Superparamagnetic iron oxide nanoparticles for bio-medical applications. Scripta Mater 2001, 44: 1713–1717. 10.1016/S1359-6462(01)00870-3View ArticleGoogle Scholar
- Granitzer P, Rumpf K, Roca AG, Morales MP, Poelt P: Porous silicon/Fe 3 O 4 -nanoparticle composite and its magnetic behavior. ECS Transactions 2008, 16: 91–99.View ArticleGoogle Scholar
- Canham LT: Biomedical applications of porous silicon. In Properties of porous silicon. Edited by: Canham LT. London: IEE Press; 1997.Google Scholar
- Lehmann V, Rönnebeck S: The physics of macropore formation in low-doped p-type silicon. J Electrochem Soc 1999, 146: 2968–2975. 10.1149/1.1392037View ArticleGoogle Scholar
- Ponomarev EA, Lévy-Clément C: Macropore formation on p-type Si in fluoride containing organic electrolytes. Electrochem Solid-State Lett 1998, 1: 42–45.View ArticleGoogle Scholar
- Christophersen M, Carstensen J, Feuerhake A, Föll H: Crystal orientation and electrolyte dependence for macropore nucleation and stable growth on p-type Si. Mater Sci Eng B 2000, 69–70: 194–198.View ArticleGoogle Scholar
- Bettotti P, Gaburro Z, Negro LD, Pavesi L: New progress on p-type macroporous silicon electrodissolution. Mat Res Soc Symp Proc 2002, 722: L6.7.1-L6.7.6.Google Scholar
- Park JY, Choi ES, Baek MJ, Lee GH: Colloidal stability of amino acid coated magnetite nanoparticles in physiological fluid. Mater Lett 2009, 63: 379–381. 10.1016/j.matlet.2008.10.057View ArticleGoogle Scholar
- Bean CP, Livingston JD: Superparamagnetism. J Appl Phys 1959, 30: S120-S129.View ArticleGoogle Scholar
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