gold nanoparticle-enabled biological and chemical detection and analysis
TRANSCRIPT
This article was published as part of the
Nanomedicine themed issue
Guest editors Frank Caruso, Taeghwan Hyeon and Vincent Rotello
Please take a look at the issue 7 2012 table of contents to
access other reviews in this themed issue
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This journal is c The Royal Society of Chemistry 2012 Chem. Soc. Rev., 2012, 41, 2849–2866 2849
Cite this: Chem. Soc. Rev., 2012, 41, 2849–2866
Gold nanoparticle-enabled biological and chemical detection and
analysisw
Hilde Jansaand Qun Huo*
b
Received 10th October 2011
DOI: 10.1039/c1cs15280g
Gold nanoparticles (AuNPs) are some of the most extensively studied nanomaterials. Because
of their unique optical, chemical, electrical, and catalytic properties, AuNPs have attracted
enormous amount of interest for applications in biological and chemical detection and analysis.
The purpose of this critical review is to provide the readers with an update on the recent
developments in the field of AuNPs for sensing applications based on their optical properties.
An overview of the optical properties of AuNPs is presented first, followed by a more detailed
literature survey. As the last part of this review, we compare the advantages and disadvantages
of each technique, briefly discuss their commercialization status, and some technical issues that
remain to be solved in order to move the technique forward (151 references).
1. Introduction
Gold nanoparticles (AuNPs) are some of the most extensively
studied nanomaterials. Because they have many unique
optical, chemical, electrical, and catalytic properties, AuNPs
have attracted enormous amount of interest for biological and
chemical sensing applications. A literature search of key words
‘‘gold nanoparticles’’ and ‘‘detection’’ using SciFinder Scholar
returned a list of more than 5000 entries (journal articles and
reviews only, in English) from the year 2005. This research area
continues to quickly evolve, with innovative new techniques
and methods reported frequently in recent years. Although
there have been many review articles published in the past on
this topic,1–11 we feel it is time to write another review to cover
some of the most recent developments in the field. The emphasis
of this review is on different detection methods. With the
significant progresses and successes made in this field, many
techniques derived from this research area have advanced to or
very close to commercialization. A critical review will help
potential users to understand the options available and to select
the appropriate techniques for different application purposes.
For techniques that are at an early stage or require further
a Imec, SSET/Functional Nanosystems, Kapeldreef 75,B-3001 Leuven, Belgium
bNanoScience Technology Center, University of Central Florida,12424 Research Parkway Suite 400, Orlando, FL 32826.E-mail: [email protected]; Tel: +1-407-882-2845
w Part of the nanomedicine themed issue.
Hilde Jans
Hilde Jans (PhD) graduated in2005 from the Catholic Univer-sity of Leuven (KULeuven) witha Master degree in Chemistry.After completing her thesiswork related to the synthesisand characterization of metalnanoparticles for nano-immunoassay applications,she obtained her PhD degreein 2010. During her PhDstudy, Hilde Jans was avisiting scholar in the Nano-Science Technology Center atUniversity of Central Florida(UCF). Dr Jans is now a
postdoctoral researcher at imec. She is currently involved inseveral European and national research projects aimed forbiosensing technology development using metal nanoparticles.
Qun Huo
Qun Huo (PhD) received herBSc degree in polymer sciencefrom University of Science andTechnology of China (1991),MSc degree in chemistry fromSun Yatsen University (1994),and PhD degree in Chemistryfrom University of Miami(1999). After spending twoyears as a postdoctoral fellowat University of Miami, shebecame an assistant professorat North Dakota State Univer-sity in 2001, and then joinedUniversity of Central Floridain 2005. She is now a tenured
associate professor in the NanoScience Technology Center atUniversity of Central Florida. Dr Huo’s primary research interestis gold nanoparticles for biomedical applications.
Chem Soc Rev Dynamic Article Links
www.rsc.org/csr CRITICAL REVIEW
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2850 Chem. Soc. Rev., 2012, 41, 2849–2866 This journal is c The Royal Society of Chemistry 2012
development, it is important to understand the major problems
that are remaining and need to be solved. This review also
serves the purpose of clarifying some confusing perceptions in
the field.
Many properties of AuNPs can be and have been used for
sensor and assay development. In this review, we will focus on
detection methods based on various optical properties and
surface chemistries of AuNPs. Optical methods are widely
used in the current analytical technologies and products.
Nanoparticle-enabled optical techniques can be readily developed
into commercial products and enter the marketplace. For detection
methods based on the electrical, catalytic, or other related
properties of AuNPs, there are a large number of comprehensive
reviews that have been written by the leading experts in this field to
which the reader may refer12–17 and therefore are not covered in
this review. One example we want to mention here in this review,
just as an illustration of the promising potentials of AuNPs as a
nanomaterial for sensing applications, is an electronic nose sensor
for cancer diagnosis based on the electrical conductivity change of
immobilized AuNP film upon detection of various cancer-related
volatile organic compounds (VOCs).18 This work has received
high profile publicity since it was first reported by the Haick
group. This group later reported that this new sensor technology is
able not only to detect cancer, but also to distinguish different
types of cancer.19–21
Although AuNPs have been used for both chemical and
biological detection and analysis, most of the effort has been
devoted to biological applications. In terms of chemical
detection, the main interest is more focused on applications
in environmental protection and homeland security, for example,
for the detection of toxic metal ions and explosive chemicals. For
biological and biomedical applications, the type of target analytes
spans a wide range from proteins, DNAs, small biomolecules, to
microorganisms including bacteria and viruses. Using AuNPs for
cancer-related detection and analysis has arisen as an extremely
active area in the last few years. A significant number of studies
discussed in this review are indeed aimed for cancer biomarker
research and applications. As one of the most challenging medical
problems, cancer causes economic burdens to society that
outweighs the effect of all other human disease. Innovative
technologies are needed to bring breakthrough advance to the
field. It is expected that the development of nanoparticle-based
technologies to improve cancer diagnosis and treatment will
continue to remain a hot topic in the future.
When biomolecular analysis is referred to, it is typically
perceived as concentration analysis of various biomolecules,
such as proteins, DNAs, and RNAs. But in fact, biomolecular
analysis is a much broader area than just a concentration
analysis. Biomolecular interaction study and biomolecular
complex detection comprise the major part of research effort
of biomolecular researchers. Although analytical techniques for
biomolecule concentration analysis are widely available, techniques
for protein–protein interaction and other biomacromolecule
complex study are rather limited.Many techniques such asWestern
blot analysis, co-immunoprecipitation, immunochromatography
that are used routinely in biomolecular research laboratories have
been around and have not been improved for decades. These
techniques are often labor intensive, time-consuming, and require
the use of large sample volumes. New technology that can improve
existing bioanalytical tools or reveal new molecular information
that cannot be observed using current techniques should bring
significant benefit to biomolecular and medical research.
Finally, we feel compelled to clarify one important concept in
the bioanalytical field: the classification of labeled and label-free
techniques. Label-free techniques, as the definition implies, have
advantages over techniques that require labeling. Labeled
techniques refer to techniques that require the labeling of the
capturing molecule or ligand (such as antibody or single strand
DNA probes that will capture the target analytes) or the
labeling of the target molecules. The immobilization of a
capturing molecule or target analyte on an optical substrate is
generally, in a less strict sense, not regarded as labeling. For
example, the surface plasmon resonance technique is a widely
known label-free technique, while ELISA, an immunoassay
that requires not only the immobilization of one antibody
on a substrate, but also a second antibody that carries a
signaling probe (the label), is a labeled technique. Most
fluorescence-based techniques are labeled techniques, because
they require the labeling of target molecules, and sometimes
both capturing molecules and target molecules. According to
the above definition, if a detection method is based on the
optical property change of the AuNP metal core, then it is a
label-free technique. If an additional dye molecule is required
to label either the capturing molecule (ligand) or the target
analyte, then it is a labeled technique. If an additional dye
molecule is involved in the detection, however, the dye molecule
is part of the AuNP signal transducing system, and it is not
conjugated to a specific capturing molecule (ligand) or target
analyte, then this technique should still be considered as a label-
free technique. We will point out explicitly whether a technique
is a labeled or label-free technique when specific examples are
introduced.
2. Overview of the optical properties of AuNPs for
sensing applications
AuNP absorbs and scatters light intensely at its surface plasmon
resonance (SPR) wavelength region and such properties make
AuNPs as one of the most valuable optical probes for sensing
applications.22–35 The SPR wavelength of gold nanoparticles can
be tuned from the visible to the near IR region by changing the
size and shape of the gold nanoparticles. The strong absorption
or scattering of AuNPs at the visible light region makes them
easily observable by the naked eye or detectable by inexpensive
instruments. The possibility of tuning the SPR band of AuNPs
(including nanorods, shells, stars, and other shapes) to the near
IR region makes them promising materials for in vivo imaging
and analysis. The optical properties of AuNPs are further
dependent on the surface chemistry and the inter-particle
interactions. As a matter of fact, a vast majority of techniques
developed so far involving AuNPs as optical probes are based
on the target analyte-induced optical property change of
individual AuNPs, or AuNP cluster formation, as summarized
in Fig. 1. Upon target analyte binding, the surface plasmon
resonance of the AuNPs will change due to the surface
chemistry change, or inter-particle interactions. The surface
plasmon resonance change of AuNPs can be detected either by
light absorption (Fig. 1A) (Section 3.1) or light scattering
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This journal is c The Royal Society of Chemistry 2012 Chem. Soc. Rev., 2012, 41, 2849–2866 2851
techniques (Fig. 1B) (Section 3.2). For absorption based
techniques, the surface plasmon wavelength shift of AuNPs
caused by target analyte binding is used as the transducer
signal. For light scattering techniques, there are more options
available and they are discussed in detail in Section 3.2.
A typical AuNP contains two structural components: the
metal core and the surface coating. The detection methods as
mentioned above are mainly based on the property and
property change of the metal core. Because nanoparticles have
a large surface area/volume ratio and the surface chemistry
can be well controlled, the surface coating layer of AuNPs
provides additional opportunity for detection and sensing.
Two specific examples are related to this concept (Fig. 1C):
one is the DNA probe based bio-bar-code amplification
platform developed by Mirkin’s group, and another one is the
surface chemistry change-induced sensing method developed by
Rotello’s group. In the bio-bar-code method, multiple copies of
DNA probes are attached to AuNPs and due to the amplification
effect of the large number of DNA probes, a high sensitivity was
achieved for both DNA and protein detection. In the surface
chemistry-controlled sensing method, different functional ligand
molecules were attached to AuNPs to create surface layers that
Fig. 1 Illustration of six detection mechanisms using the optical properties of AuNPs. (A) LSPR concept: (1) Irradiation of the gold nanoparticles
gives rise to a collective oscillation of their conduction band electrons resulting in a plasmon absorption in the visible range of the electromagnetic
spectrum. (2) This plasmon resonance is sensitive to changes in the local environment, for example the binding of biomolecules. (B) (1) When
nanoparticles are irradiated with laser light, they will scatter the light elastically in all directions. By monitoring the change in the scatter pattern the
diameter of the solid nanoparticles can be deduced. (2) When biomolecules are attached on the nanoparticle surface the size increase can be
monitored. (C) Detection using the surface chemistry and ligands of AuNPs. (1) Signal amplification based on the large number of DNA
strands (bar-codes) released from the AuNPs. (2) Surface chemistry-controlled reversible biomolecular binding to AuNPs in a competitive assay.
(D) (1) Normal Raman scattering is inherently weak. (2) When biomolecules of interest are bound to nanoparticles, the Raman signal can be
enhanced due to the enhanced electromagnetic field which is excited or due to a charge transfer mechanism. When molecules are attached to
AuNPs their properties can change. (E) Metal enhanced fluorescence can occur when a fluorophore is placed at a fixed position from the metal
nanoparticle surface. (F) When the fluorophore is in short or direct contact with the metal nanoparticle surface quenching will occur. In this case, a
competitive assay format is often used for the target analyte detection.
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2852 Chem. Soc. Rev., 2012, 41, 2849–2866 This journal is c The Royal Society of Chemistry 2012
can bind with proteins, enzymes and fluorescent polymers
reversibly. This reversible binding process provides a new
sensing platform for a wide range of target analytes. These
two examples are discussed in Section 3.3.
The unique interactions between the metal core and the
surface ligands of AuNPs provide several widely known signal
transduction systems for chemical and biological sensing
purposes. Three techniques can be considered as examples of
this sensing mechanism: the surface enhanced Raman scattering
(SERS) (Fig. 1D), metal-enhanced fluorescence (MEF) (Fig. 1E),
and metal-induced fluorescence quenching (Fig. 1F). Although
SERS is a light-scattering based technique, this is different from
the other techniques mentioned above, where the light scattering
is detected from the metal core. In SERS, the scattered light is
detected from the Raman active dye molecules located on the
surface of AuNPs. The AuNP metal core enhances the Raman
scattering of the organic molecule. When a fluorophore is attached
to a metal nanoparticle, the fluorescence of the fluorophore can be
enhanced or quenched, largely depending on the distance from the
fluorophore to the nanoparticle core. Competitive assays are
often designed using the metal-induced fluorescence quenching
phenomenon, while direct assays are conducted based on
the metal-enhanced fluorescence effect. These three detection
mechanisms and examples are discussed in Section 3.4.
3. Literature survey
3.1 Detection based on the localized surface plasmon
resonance (LSPR) property
The optical properties of AuNPs are governed by their unique
localized surface plasmon resonance (LSPR), which is the
collective oscillation of the nanostructure’s conduction band
electrons in resonance with the incident electromagnetic field.
The LSPR spectrum is strongly dependent on the nanostructure’s
size, shape, dielectric constant, and on the dielectric constant of
the surrounding environment (Fig. 2).22–35 The contribution of
the different parameters to the total extinction of the metal
nanoparticles is described by the Mie theory. The recognition
that the LSPR is sensitive to changes in these parameters has
resulted in intense development of noble metal nanostructures
for various biomedical applications such as biosensors.
Depending on the origin of the LSPR change, a distinction
between two types of LSPR sensors can be made. The first one
is based on the aggregation of the colloid which results in an
apparent color change from red to blue due to inter-particle
coupling. When metal nanoparticles approach each other
closer than their particle diameter, a red-shift of the LSPR is
observed. An extensive review on aggregation based LSPR
sensing was written on this topic by Ghosh et al.34
The other sensor type is based on the sensitivity of the LSPR
to changes in the dielectric constant of the surrounding
medium or adsorbents. This relationship is expressed by the
following equation:35
DlLSPR ¼ mDn 1� exp�2dld
� �� �
where m is the bulk refractive index response of the nanoparticle,
Dn is the change in the refractive index induced by the adsorbents,
d is the effective adsorbent layer thickness, and ld is the
characteristic electromagnetic-field-decay length. As such,
when molecules bind to a AuNP the refractive index will
change giving rise to a shift of the LSPR. It can be deduced
from this equation that the enhanced electromagnetic field will
decay when further away from the nanoparticle surface. As such,
the sensitivity towards refractive index changes is distance
dependent. Only changes in the refractive index at close
proximity to the nanoparticle surface will give rise to a shift
of the LSPR wavelength. This makes the refractive index
based biosensor specific for interactions close to the nanoparticle
surface. The thickness of the adsorbate layer inversely affects the
sensitivity of the plasmon band position to changes in the
refractive index of the surrounding medium or interacting
molecules which is limiting for the detection.
In the following, some examples of both types of LSPR-based
sensors are given and their advantages and disadvantages are
discussed in greater detail. All LSPR-based sensors are label-free
techniques.
3.1.1 Aggregation based LSPR sensing. In the early 1990’s,
biosensor technologies based on the aggregation/agglutination
of gold nanoparticles were successfully implemented to probe
biomolecular interactions. The first reports focused on the
detection of ssDNA by using two types of gold nanoparticles,
both coated with a complementary strand to a part of the
target ssDNA. Upon hybridization, the gold colloid changed
color from red to blue. Mirkin et al. were the pioneers in this
field and were able to detect femtomole levels of ssDNA using
this technology.36 Not only was this technology applied for
DNA detection, but also it was used to study protein–protein
interactions in detail. A well-known application of this technology
is the development of a pregnancy test. In this sensor technology,
AuNPs and micro-latex beads are used, both coated with specific
antibodies to b-hCG, a hormone released by pregnant women.
Upon mixing these particles with urine, containing the hormone,
pink aggregates could be clearly observed.37 In the early 1990s
the first AuNP-based pregnancy testing kits were marketed
by Carter-Wallace and are nowadays still available through
consumer healthcare giant Church and Dwight. Thanh and
Fig. 2 The plasmon resonance of metal NP is dependent on the size,
shape and material. Silver nanoparticles exhibit a plasmon resonance
around 400 nm whereas spherical AuNPs have their resonance around
520 nm. Special shaped AuNPs exhibit plasmon resonance at longer
wavelength.
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Rosenzweig reported on a AuNP-based aggregation assay to
determine the level of anti-protein A in aqueous and serum
solutions.38 Their technique shows comparable sensitivity to
the traditional ELISA. Hirsch and coworkers reported on the
use of gold nanoshells in an immunoassay that is capable of
detecting subnanogram levels of analyte within whole blood.39
Because nanoshells absorb light at the near IR region where
blood does not absorb significantly, antibody-conjugated
nanoshells and their aggregate formation upon binding with
the target analytes can be detected from whole blood samples
using near-IR light.
The aggregates-based LSPR sensing has many advantages as
compared to other techniques. It is a label-free, homogeneous
solution assay and the detection can be done by low cost, simple
instruments (spectrometer) or even by the naked eye. However
this technology has some drawbacks since AuNPs tend to
aggregate under various external perturbations, e.g. changes
of ionic strength, pH or temperature. Further, the color change-
based detection is limited to mostly colorless samples, or at
least, the color of the sample matrices should not overlap with
the color and color change of the gold nanoparticles.
3.1.2 Refractive index based LSPR sensing. Since the
LSPR of metal nanoparticles is sensitive to changes in
the refractive index close to the metal surface, monitoring
the biomolecular interactions on the metal nanoparticle surface
is feasible.40 Englebienne et al. have demonstrated that this optical
property can be used in homogenous biosensor technologies.41
They developed AuNPs which remain in suspension during the
experiments. As such, they were able to determine affinity
parameters of binding proteins for their ligands. In addition,
they used antibody-coated AuNP probes to quantitatively
sense the analyte binding. Also, they can monitor changes in
protein conformation using this technology.42,43 Recently,
PharmaDiagnostics has commercialized this LSPR-based
biosensing. This technology is named SoPRanot and it has
the advantage of being fast, specific, simple to perform,
requires no separation or purification steps and uses common
laboratory equipment for detection. As such, SoPRanot
enables sensitive, robust and reproducible screening in high-
throughput mode.
As the examples above suggest, homogeneous biomolecular
assay formats offer several advantages over conventional
heterogeneous assays. For example, the biomolecular inter-
actions are no longer governed by planar diffusion but by faster
radial diffusion. The active surface area can be significantly
increased by the use of suspended nanoparticles.44 Despite the
potential of this sensing principle, the homogenous detection of
biomolecules has only scarcely been investigated. On the other
hand, refractive index based LSPR biosensing using a hetero-
geneous assay format has been widely developed. As an example,
Frederix et al. have applied this sensing principle in the
construction of a transmission plasmon biosensor, whereby
metal nanoparticles immobilized on a transparent substrate
served as a sensing platform.45 Huang et al. used this technology
to develop an on-chip LSPR-based biosensor for label-free
monitoring of protein–protein interactions.46 To increase the
performance and assay sensitivity of this sensor platform, other
materials and nanostructured patterns on transparent surfaces
have been developed. For example the plasmon wavelength of
silver nanotriangles,47 gold nanoholes, nanorings,48 nanocrosses,49
and nanoshells showed an enhanced sensitivity for refractive
index changes and proved potential in monitoring biomolecular
interactions. Extensive work on silver triangular substrates was
performed by the group of Van Duyne35,47,50,51 and Liz-Marzan.31
Extensive work related to different gold nanostructures was
conducted by the research group of Voros (ETH Zurich)52 and
our research group at imec. Active research is going on in
various research groups to eventually bring this technology to
the market. Some major challenges such as improving the
detection limit, sensitivity and multiplex capabilities need to
be addressed. Notwithstanding these issues, LamdaGen
Corporation has already launched a high throughput (4–8
channels) bench-top LightPatht instrument combined with
pre-functionalized LSPR-based sensorships and software for
data-analysis.
3.2 Detection based on the light scattering properties of
AuNPs
There are many types of electromagnetic scattering and they
can be generally grouped into the categories of elastic and
inelastic light scattering. Elastic scattering involves no energy
transfer while inelastic scattering involves energy transfer
during the scattering process. Rayleigh scattering and Mie
scattering are elastic scattering, while Raman scattering,
inelastic X-ray scattering and Compton scattering belong to
inelastic scattering.53 Depending on whether the scattered light
intensity is proportional or not to the irradiance of the incident
radiation, light scattering can be further divided into linear or
non-linear scattering. Hyper-Rayleigh and hyper-Raman
scattering are two examples of nonlinear light scattering. A
majority of work that has been published on using AuNP
probes for chemical and biological detection is based on elastic
and linear scattering. Inelastic surface-enhanced Raman
scattering is covered in Section 3.4, because it is based on
the scattering of the organic molecule attached to AuNPs, not
directly from the metal core as mentioned above. In regarding
to the nonlinear hyper-Rayleigh scattering of AuNPs, P. C.
Ray has recently published a comprehensive review on this
topic and its application in chemical and biological detection.54
Our current review will focus on two general types of methods
of elastic and linear light scattering: one is based on the
scattered light intensity or wavelength change, and the second
one is nanoparticle-enabled dynamic light scattering assay
(NanoDLSayt).
The theory of light scattering of AuNPs and its potential
applications in biology was first systematically studied by
Yguerabide and Yguerabide and more recently by El-Sayed
et al.22,23 The light scattering cross section of AuNPs increases
with increased particle size. When the diameter exceeds 80 nm,
the light scattering cross section increases substantially compared
to smaller particles (Fig. 3).55 The scattered light intensity of
AuNPs is about 105 times stronger than a fluorescein molecule
and 100–1000s times stronger than a polymer bead. The
exceptionally strong light scattering of AuNPs is enhanced
by the surface plasmon resonance effect. As an optical probe
for light scattering-based biomolecular detection and analysis,
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the scattered light intensity from AuNPs must be substantially
stronger than the scattered light from the biological samples to
avoid the background interference from the sample matrix.
AuNPs can be easily observed or detected in biological samples
and matrices including whole blood, serum, cells, and tissues.
This property is essential for applying AuNP probes for both
in vivo and in vitro applications. Finally, it needs to be mentioned
here that all of the light scattering-based detection techniques
that have been reported so far are label-free techniques.
3.2.1 Scattered light intensity or wavelength change-based
methods. The most known light scattering detection method is
perhaps to directly observe and measure the scattered light
intensity or wavelength change of AuNP probes upon
chemical or biomolecular binding using a microscope, a
spectrophotometer, or sometimes just by the naked eye. In
traditional solid phase ligand binding assays or immunoassays,
AuNPs can replace other optical or enzymatic probes to
conjugate with the detecting molecule. Upon binding of the
detecting molecule–AuNP conjugate with the analyte, the
AuNPs can be visualized using an optical microscope, a scanner
or a spectrophotometer, and the observed scattered light
intensity or wavelength is correlated to analyte concentration.
Sometimes, a silver or gold enhancement may be used to
further enhance the scattering light intensity from the plate.
The bio-bar-code method developed by Mirkin’s group initially
for DNA detection56 utilized this detection mechanism to
achieve a high sensitivity that is two orders of magnitude better
than the analogous fluorophore system.
Storhoff et al. reported the detection of unamplified genomic
DNA sequences based on colorimetric scattering of AuNP
probes using a slightly different assay format.57 In this assay,
the binding of nucleic acid targets with the DNA-modified
AuNP probes is performed in a homogeneous solution, i.e.
the binding between AuNPs probes and the target analyte
occurs in the free solution. The target DNA binding introduces
AuNP clustering. The assay solution is then spotted on a glass
slide and the scattering light from the AuNPs is detected by a
simple waveguide device (Fig. 4). While individual AuNPs
scatter a green light, the AuNP clusters scatter yellow to orange
light, due to a plasmon band red-shift. The scattering light
change was detected and correlated to the target DNA concen-
tration. This scattering light-based method enables detection of
zeptomole quantities of nucleic acid targets without target or
signal amplification, a sensitivity that is over four orders of
magnitude higher than the typical absorbance-based method.
The authors further successfully applied this method to the
rapid detection ofmecA in methicillion-resistant Staphylococcus
aureus genomic DNA samples.
It has been further reported that the detection can be done
by directly monitoring the light scattering change of the assay
solution. According to Mie or Rayleigh scattering theory, the
scattered light intensity increases with increased particle size. For
Rayleigh scattering, the scattering light intensity is proportional
to the 6th power of the radius of the particle.22 When AuNPs
form clusters in solution due to target analyte binding, the
scattered light intensity could increase dramatically. This is the
reason why light scattering based detection techniques are
generally far more sensitive than light absorption-based assays.
Zhang et al. reported the detection of a small biomolecule,
adenosine, from human urine samples using resonance light
scattering of a AuNP modified structure-switching aptamer.58
The reported detection limit was 1.8 nM, with a dynamic range
of 6–115 nM. Xiang et al. used this method to study glycogen
biomacromolecule interactions.59 Glycogen can cause AuNP
aggregation and upon interaction with biomacromolecules, such
aggregation is disrupted, leading to decreased scattered light
intensity. Du et al. demonstrated the detection of human IgG
and DNA using this technique.60,61 Using specially designed
microscopes, Rashke et al.62 and Cao and Sim63 demonstrated
that protein antigen–antibody interaction may be detected from
the light scattering of individual AuNPs.
3.2.2 Nanoparticle-enabled dynamic light scattering assay
(NanoDLSayt).Dynamic light scattering (DLS) is a well-known
Fig. 3 Calculations of the contributions of scattering and adsorption to
the total extinction cross-section of AuNPs of different sizes at their plasmon
band position. The calculations were performed using MiePlot v.3.4.12
(Philip Laven, Geneva, Switzerland). All calculations were performed for
spherical AuNPs in water (5 1C, density: 0.99996382 kg m�3).
Fig. 4 Colorimetric detection of nucleic acid sequences reported by
Storhoff et al. Step 1: DNA–gold nanoparticle probes (A and B) are
hybridized to a DNA target in solution. Step 2: The samples are spotted
onto a glass slide which is illuminated with white light in the plane of the
slide. The evanescent induced scatter from the gold nanoparticles is
visually observed. Individual 40- to 50-nm diameter gold probes scatter
green light, whereas complexed probes scatter yellow to orange light
because of a plasmon band red-shift (Reprinted by permission from
Macmillan Publishers Ltd: Nature Biotechnology, copyright 2005).
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analytical technique for particle size analysis, particularly for
particle sizes in the nanometre scale range.64 It has been used
routinely in polymer characterization, nanomaterial research
and the pharmaceutical industry to study drug formulation and
biopharmaceuticals. While DLS is occasionally used to monitor
the scattered light intensity change of a sample solution, most
frequently its purpose is to determine the average particle size
and size distribution of a nanoparticle solution. DLS measures
the particle size by monitoring the scattered light intensity
fluctuation caused by the Brownian motion of the particles in
solution. Because of the familiarity of DLS to most researchers
in the nanomaterial field, the background of this technique is
not explained here. Even though DLS is also a scattering light
detection technique, the technique we discuss at the following is
not based on scattered light intensity change like the examples
presented in the previous section. Instead, NanoDLSayt
technique detects target analytes based on the size change of
AuNPmolecular probes upon interaction with analyte molecules.
There were two principal assay formats developed (Fig. 5):
one is based on the analyte binding induced AuNP cluster or
aggregate formation; and a second one is based on the individual
AuNP size change upon analyte binding. The two assay formats
can be modified and adapted for different application purposes.
The aggregation assay format (Fig. 5A) can be applied to any
target analytes, small or large, including proteins and DNAs,
small chemicals, metal ions, etc. The individual particle size
change format is more suitable for the detection and analysis
of large biomacromolecules, mainly proteins (Fig. 5B).
(1) Aggregation-based average particle size change. In 2008,
Huo’s group reported a nanoparticle aggregation assay for
protein and DNA detection and analysis using AuNPs
coupled with dynamic light scattering.65–67 This assay is based
on the same principle that numerous other assays are based
upon: the AuNP cluster formation due to target analyte
binding. The nanoparticle cluster formation causes the average
particle size increase of the assay solution. Instead of detecting
the SPR wavelength shift (color change), or scattered light
intensity change, the average nanoparticle size change of the
assay solution is measured using DLS and the size information
is correlated to the target analyte concentration. This technique
has been applied for both protein and DNA detection. The
initial study demonstrated that the sensitivity of NanoDLSayt
is comparable to most other assay techniques: the sensitivity
for a cancer biomarker protein, PSA, could reach a low ng per
mL range, and the detection limit for DNA is in the pM range.
Later, Chun et al. reported that by using a gold-coated
magnetic nanoparticle, a detection limit of 0.01 ng mL�1 can
be achieved for a-fetoprotein.68
Other groups have reported the use of this concept for toxic
metal ions, small chemicals and biomolecules, DNA, and virus
detection. Ray’s group reported the detection of toxic metal ions
including arsenics and lead, and explosives TNT using small
ligand-modified AuNPs with extremely high sensitivity and
excellent selectivity.69–71 For arsenic or lead detection, metal ion
chelating ligands glutathione, dithiothreitol, or cysteine were
attached to the AuNP surface.69,70 For TNT detection, p-ATP-
functionalized AuNPs were used as the probe.71 The sensitivity of
this method for arsenic detection can reach 10 ppt, a concen-
tration that is three orders of magnitude lower than the WHO
guidelines. This sensitivity is two orders of magnitude more
sensitive than the colorimetric techniques. This assay has been
applied successfully to the analysis of environmental samples such
as contaminated well water and consumer products including
paints and toys. For TNT detection, the detection limit can reach
100 pM, which is 5 orders of magnitude more sensitive than the
typical colorimetric methods. The use of this technique is not
confined to only AuNPs, Zhang et al. reported the use of
aza-crown-ether-modified silver nanoparticles for lead(II) ion
detection in surface water with pM sensitivity.72
Miao et al. reported an equally sensitive detection of Pb2+
using Pb2+-specific DNAzyme controlled AuNP aggregation
coupled with DLS. This assay could also be used to detect
Cu2+ and UO42+.73 The same group recently also reported
the detection of double-stranded DNA with a detection limit
of 0.5 fM with excellent sequence specificity.74
Using a similar approach, Yang et al. reported an assay
for adenosine detection.75 Split aptamer fragments were
conjugated to AuNPs to form the probe. Again, the binding
of the aptamer-conjugated AuNPs causes AuNP aggregate
formation. The size change of the assay solution is detected by
DLS and correlated to the adenosine concentration. The
reported limit of detection (LOD) was around 7 nM, 5 orders
of magnitude lower than the colorimetric methods.
Fig. 5 The principle of NanoDLSayt. Two assay formats are illustrated here: A—analyte binding induced nanoparticle cluster formation; and
B—analyte binding induced individual nanoparticle size increase. In both cases, the particle size change of the assay solution can be measured by
DLS and correlated to the analyte information. While the first assay format can be applied to any type of target analytes, small or large, the second
assay format is primarily used for the detection of larger analytes, such as proteins, protein complexes, aggregates and viruses.
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More recently, the Han group developed an innovative
approach for DNA detection using true label-free citrate-
protected AuNPs coupled with DLS.76 Most prior work on
DNA detection involving the use of AuNP probes requires the
conjugation of a single strand DNA probe attached to AuNPs.
The assay developed by the Han group is based on the
different binding affinity of single strand DNA and double
stranded DNA to the citrate-protected AuNPs. Single strand
DNA can bind (or adsorb) to AuNPs through Au–N bonding
between AuNPs and the base moiety on DNA to form a
protective layer on the AuNP surface. Citrate-protected
AuNPs tend to aggregate at a salt concentration higher than
10 mM due to the disruption of the electrical double layer.
When the citrate-AuNPs are protected by a single strand DNA
layer, the AuNPs are stabilized and remain monodispersed in
high salt content solution. In contrast, when a single strand
DNA probe is hybridized with a target DNA to form a double
stranded DNA, the double stranded DNA lost its binding
affinity to citrate-AuNPs. Therefore, citrate-AuNPs are not pro-
tected by double strand DNA molecules against salt-induced
aggregate formation. Using this difference, the authors demon-
strated the detection of the sequence-specific nopaline synthase
(NOS) gene from transgenic plants. The detection limit can reach
the 10 fM range. This sensitivity is 5 orders of magnitude better
than the colorimetric method. A recent side-by-side comparison
study conducted by Pylaev et al. on DNA sequence detection also
confirmed that the dynamic light scattering detection is significantly
more sensitive than the colorimetric assay.77
Driskell et al. reported the detection of influenza virus using
specific anti-influenza virus antibody conjugated AuNPs and
DLS.78 After optimization, they demonstrated a detection
limit of o100 TCID50 per mL, which is 1–2 orders of
magnitude improved over commercial diagnostic kits. This
sensitivity increase is achieved without increasing the assay
time or complexity. Additionally, this assay was demonstrated
to perform equivalently for the influenza virus prepared in
different biological matrices.
As demonstrated by these published works, AuNPs coupled
with DLS detection is a highly promising new technique for
biological and chemical detection and analysis. The sensitivity
of this technique is on the average of 1–5 orders of magnitude
better than many of the other existing techniques. It is a single-
step homogeneous solution assay and it is extremely easy to
use. The target analytes that can be detected by this technique
range from ions, small chemicals and biomolecules, proteins,
DNAs to virus particles. Essentially, any target analytes that can
introduce AuNP cluster or aggregate formation can be detected
using this technique. As demonstrated from publications from
different groups on different target analytes, the reproducibility
of NanoDLSayt is excellent, and as a matter of fact, it is better
than many other existing techniques. Based on all the published
work, the CV% (coefficient variation) of NanoDLSayt is
generally below 10%, and with simple sample matrices such as
buffer solutions, it is often below 5%. As a comparison, the
CV% of a typical ELISA assay is 5–20%.
(2) Individual particle size change. Biological molecules
such as proteins and DNAs are macromolecules. For example,
bovine serum albumin, a protein with a molecular weight of
60–70 KDa has a hydrodynamic diameter around 5–7 nm, and
a typical IgG molecule (150 KDa) has a hydrodynamic
diameter around 7–10 nm. When a complete layer of proteins
is adsorbed or specifically bound to the AuNPs, the diameter
of the nanoparticle will increase by as much as twice of the
diameter of the protein molecule as illustrated in Fig. 6.
Because of the relative large size of the proteins, analyte
proteins may be detected by monitoring the individual particle
size increase without the need of introducing nanoparticle
aggregation by protein analytes. At a saturated binding level,
the size of a target protein may be deduced from the average
particle size increase of the assay solution. This unique feature
of NanoDLSayt to reveal the ‘‘size information’’ of a target
analyte brings new analytical capabilities in biomolecular
detection and analysis, as to be seen from the following
examples. It is important to be aware that in order to use this
assay format correctly, the assay needs to be designed to avoid
nanoparticle–nanoparticle interaction. This can be conveniently
done using a low concentration of AuNP probes. The strong
light scattering property of AuNPs is particularly important for
this application.
A. Label-free and real-time protein–protein interaction
study in solution. For this application, a capture protein or
binding ligand is immobilized or conjugated to AuNPs. Upon
mixing with a sample solution that contains the target binding
protein, the nanoparticle size will increase gradually and this
size increase can be monitored continuously in real time by
DLS to generate a binding curve as illustrated in Fig. 6. Huo’s
group first applied this technique on a model system, protein A
Fig. 6 Real-time monitoring of target analyte binding to the AuNPs
using NanoDLSayt. Assays can be designed so that a saturated
binding level is reached. At a saturated binding level, the size of the
target protein analyte can be estimated. The net particle size increase is
approximately twice of the diameter (D) of the analyte. Such information
can be used to deduce the complexing status of a protein analyte. Because
a protein complex is larger than an individual protein, the binding of a
protein complex to the AuNPs will cause a larger particle size increase at
the saturated binding level than a small individual protein. Protein
complexes and aggregates may further cause nanoparticle cluster
formation. These different scenarios can be distinguished according to
DLS analysis.
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(prA)–human IgG interaction.79 Protein A was immobilized
on AuNPs to form the molecular probe. The subsequent
binding of human IgG to the prA-conjugated AuNPs was
monitored directly by DLS according to the nanoparticle size
change. The different binding activities of the prA–AuNP
conjugate under different conditions (crosslinking versus
non-crosslinking of the prA layer, and pH effect) with human
IgGwere revealed from the assay. Later this assay was applied for
antibody isotyping and quality control analysis.80 Although this
application is not widely known among researchers, antibody
isotyping is a very important step in antibody production and
biopharmaceutical industry. In this study, NanoDLSayt analysis
of several antibody products purchased from commercial sources
led to the same results and conclusions as revealed by using
a commercially available test kit, however, at a substantially
lower cost.
B. Protein complex detection and binding partner analysis.
Protein–protein interactions play an essential role in almost all
cellular functions.81 Many intracellular biochemical processes
are triggered by the assembly of proteins into macromolecular
complexes, providing a means to control the myriad of
biochemical processes for the efficient management of vital
biological responses. A daily task for most biomolecular
researchers is to study various protein complexes and their
biological functions. While numerous methods and technologies
are available for protein concentration analysis, the number of
techniques for protein complex analysis and study is rather
limited and these techniques have not been improved for decades.
One of the most commonly used techniques in biomolecular
research laboratories for protein complex detection and binding
partner analysis is co-immunoprecipitation followed by immuno-
blotting. This technique is time-consuming (1–2 days), labor-
intensive (multiple assay steps) and requires substantially a large
amount of samples (typically 100s mL of sample solution at
reasonably high protein concentrations).
Using a two-step assay format and the assay principle as
outlined in Fig. 6, the Huo group developed a simple method
for protein complex detection and binding partner analysis.82
To conduct the assay, a specific monoclonal antibody for a
target protein is conjugated to AuNPs to form the immuno-
probe. The AuNP immunoprobe is then used to catch the
target protein or protein complexes from the sample solution.
When the binding reaches a saturated level (such a saturated
binding can be achieved by choosing an assay condition so
that the target protein concentration is substantially exceeding
the AuNP concentration), the average particle size increase
can be used to deduce whether the detected target protein is in
a monomer or the other complexed form. Typically, the size of
a target protein is known. If the protein is in a monomer state,
the maximum particle size increase that can be observed
should be approximately twice of the diameter of the protein.
If the observed particle size increase of the assay solution
exceeds substantially this value, the possible existence of
protein complex should be considered. In a second step of
the assay, an antibody that is specific to a suspected binding
partner of the complex is added to the assay solution. If the
suspected binding partner is part of the complex, further
increase of the average particle size should be observed; and
if the suspected protein is not part of the complex, then the
average particle size of the assay solution will remain unchanged.
Using this assay, we discovered for the first time a heteromeric
protein complex that contains EGFR, Stat3 and Src from a
pancreatic cancer cell line, Panc-1.82 Compared to co-immuno-
precipitation, NanoDLSayt requires only a minute amount of
samples (1–2 mL) and results are obtained in minutes instead of
hours or days.
In addition to the two applications discussed here, this
technique has also been applied for label-free protein aggregate
detection83 and cancer biomarker research.84,85 From these
studies, new molecular information on protein biomarkers that
had not been or cannot be revealed by other existing techniques
was discovered. Because of the complexity of the biological
problems addressed in these work, a separate review is being
prepared to examine these issues.
3.3 Detection based on the surface chemistry of AuNPs
Compared to many other nanoparticle materials, the surface
chemistry of AuNPs is significantlymore advanced and understood.
AuNPs form stable chemical bonds with S- and N-containing
groups. As to citrate-protected AuNPs, the presence of positively
charged Au+ ions attracts negatively charged proteins and DNA
molecules, a main force driving the adsorption of biomolecules
to AuNPs. Small organic ligands and polymers with a wide
variety of chemical functionalities may be conveniently attached
to AuNPs through thiol or N-containing linker molecules. The
unique ligand place exchange reaction of AuNPs allows one to
readily modify and switch the chemical functional groups on the
AuNPs.86–91 Furthermore, like other nanoparticle materials, the
large surface area of AuNPs allows one to use the surface ligands
as a way of amplification in chemical and biological detection.
3.3.1 DNA bio-bar-code technique. A most representative
example of using the surface chemistry of AuNPs to amplify
analytical signal transduction is the widely referred DNA
bio-bar-code method developed by the Mirkin group (Fig. 7).
Initially this method was reported for the detection of
protein analytes,92 but later was also applied for DNA target
detection.93 For protein detection, the AuNPs are conjugated
with a capturing molecule, which is an antibody for the specific
protein analyte, along with multiple copies of DNA strands.
The DNA strands are the bio-bar-codes. Another capturing
molecule, typically an antibody that binds to a different
epitope of the protein analyte, is conjugated to a magnetic
microparticle (MMP). The target protein analyte is first
captured by the MMPs, and then the AuNP probe is added
to form a sandwich structure with the captured target protein
and MMPs. By applying a magnetic field, the sandwiched
assay product can be isolated from the assay solution to
eliminate unbound AuNPs. The bio-bar-code DNA molecules
are then released from the AuNPs and analyzed by PCR
methods, or scanometric (PCR-less) methods amplified by
the enhanced light scattering of metal nanoparticles as the
authors reported previously.56
The DNA bio-bar-code technique combines two essential
elements to create ultra-high sensitivity of detection: (1) the
ability to attach a large number of DNA probes onto AuNPs;
and (2) the detection of DNAs with extremely high sensitivity
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using currently available techniques. Furthermore it is a
homogeneous solution assay. One has the option to add high
concentration of AuNPs and MMP probes to increase the
kinetics of the binding. The addition of more probe particles
(both AuNPs and MMPs) will push the equilibrium toward
the complex formation, increasing the detection limit. Without
PCR amplification, this method can achieve a 30 aM (attomolar)
detection limit for prostate specific antigen, a protein biomarker
for prostate cancer. If PCR is applied, the sensitivity can be
boosted to 3 aM. This bio-bar-code assay represents a six-order
of magnitude higher sensitivity than most conventional assays.
For target DNA detection, PCR-like sensitivity can be achieved.
Later this technique was reported for the detection of cyto-
kines at a 30 aM concentration range,94 a soluble pathogenic
biomarker for Alzheimer’s disease at a concentration around
100 aM,95 and more recently, used to detect trace amounts of
PSA from prostate cancer patients after radical prostatectomy
surgery.96
3.3.2 Controlled surface chemical functionality of AuNPs
for biological sensing and detection. Another approach that
uses the surface chemistry of AuNPs for sensing has been
developed by the Rotello group. Prior to sensing applications,
this group has conducted extensive studies to understand and
control the interactions between AuNPs and biomolecules,
primarily proteins, by controlling the surface chemical func-
tionality of AuNPs.97–103 The surface chemistry of AuNPs can
be conveniently modified using different synthetic methods.
Small chemical ligands or polymers may be attached to
AuNPs through Au–S or Au–N bonding. The AuNP surface
can thus be made to contain positive, negative, mixed charges,
or to be neutral. Different proteins, with different amino acid
residues and charges on the surface, tend to bind with
these surface-modified AuNPs with different affinities through
non-covalent interactions.
In 2007, the Rotello group made an important finding that a
fluorescent polymer (or green fluorescent protein) may reversely
bind and dissociate from the functionalized AuNPs through
controlled non-covalent chemical interactions between the
polymer and AuNPs.104 When the fluorescent polymer is
bound to the AuNPs, its fluorescence is quenched; and once
it is dissociated from the AuNPs, the fluorescence property is
restored. Based on the different binding affinity of this fluorescent
polymer and proteins with AuNPs, a competitive assay was
developed for protein detection (Fig. 8). The target protein is
detected according to their different binding patterns to variously
functionalized AuNPs. By using an array of surface-modified
AuNPs, a target protein will cause different fluorescence
responses upon binding with the AuNPs, therefore, a fluores-
cence response pattern is generated. By analyzing the fluores-
cence response pattern of the assay solution using a suite
of statistical analysis tools, different molecular targets or
biological species may be detected and distinguished from
one to another. This approach is based on a ‘‘chemical nose’’
sensing mechanism. The most unique and exciting aspect of
chemical nose sensing is that one does not need to know the
true identity or nature of the target analyte in order to detect
this analyte. There is also no need to generate a specific
antibody for the detection.
Initially, this method was reported for the detection and sensing
of proteins. Later, it was further successfully applied for the
detection and sensing of bacteria and cancer cells.105–109 More
recently, the Rotello group further reported the use of an enzyme,
b-galactosidase (b-Gal), to replace the fluorescent polymer as the
signal transducing molecule and to enhance the sensitivity of
the technique.110 Because of the amplifying capability of the
enzyme through catalytic reactions, the sensitivity is improved
substantially. For example, a detection limit of 1 � 102
bacteria per mL in solution and 1 � 104 bacteria per mL in
a test strip format was reported using this method based on a
simple color change of the assay solution.
Fig. 7 The DNA bio-bar-code method for protein detection developed by the Mirkin group. (A) An AuNP probe is functionalized with antibody
and bar-code DNAs, while a magnetic microparticle (MMP) probe is conjugated with a capture antibody for the target protein. The MMP probe is
first used to capture the target protein analyte and then the AuNP probes are added to form a sandwich-structure with the captured target proteins.
The AuNP–MMP clusters are then separated from the assay solution by applying a magnetic field. The bar-code DNAs are then released from the
AuNP–MMP clusters, and analyzed. The quantity of the DNA bar-code is correlated to the target protein concentration (Science by American
Association for the Advancement of Science. Reproduced with permission of American Association for the Advancement of Science in the format
Journal via Copyright Clearance Center).
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3.4 Detection based on the metal core–surface ligand
interaction of AuNPs
Colloidal AuNPs exhibit strong enhancement of Raman scattering
and fluorescence emission from molecules adsorbed on their
surface. As already outlined in the Introduction, the enhance-
ment mechanisms that are relevant to SERS are also present in
surface-enhanced fluorescence (SEF). Many applications as a
method to enhance existing fluorescence based techniques are
also relevant to SERS and vice versa. For example, many
SERS probes are, indeed, fluorescent dyes.
3.4.1 Surface-enhanced Raman scattering (SERS). Mole-
cular vibrations can be probed by infrared absorption spectro-
scopy or by inelastic scattering of photons from vibrational
quantum states, called Raman scattering. The frequency shift
between incoming and Raman scattered light is determined by
the energy of molecular vibrations. In general, Raman scattered
light is inherently weak. However, the intensity of Raman scattering
can be enhanced dramatically when the inelastic scattering process
takes place in very close vicinity of metal nanostructures. This effect
of surface-enhanced Raman scattering (SERS) elevates vibrational
spectroscopy to new limits in sensitivity and molecular structure
selectivity.
Surface-enhanced Raman scattering (SERS) was discovered in
the early 1970’s. Since then, this field developed explosively, reflected
by the enormous amount of research papers, reviews and analytical
books that have appeared in the literature. The interest in SERS
shifted from fundamental research to applications governed by the
ability to reliably control the size, shape and surface properties of
nanostructured materials, making SERS a recognized analytical
technique for the sensitive and selective detection of molecules in
close vicinity to metal nanostructures.111,112
Although the SERS effect has been studied extensively, the
mechanism leading to the surface enhancement is still not
Fig. 8 Protein detection using a nanoparticle–fluorescent polymer ‘‘chemical nose’’ sensor developed by the Rotello group. (A) Illustration of the
sensing mechanism. An anionic, fluorescent polymer is first adsorbed to the cationic gold nanoparticles through electrostatic interactions. This
adsorption causes fluorescence quenching of the polymer. Displacement of the quenched fluorescent polymer by a target protein restores the fluorescence
of the polymer. By using different types of gold nanoparticles, a protein sensor array is generated. Different target proteins will show different binding
affinity towards the nanoparticle array. (B) The chemical structure of the cationic gold nanoparticles and anionic fluorescence polymer. (C) The response
profile (expressed as a canonical score plot) of different target proteins to the nanoparticle–fluorescent polymer sensor (Nature Nanotechnology by Nature
Publishing Group. Reproduced with permission of Nature Publishing Group in the format Journal via Copyright Clearance Center).
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completely understood. It is generally believed that there are
two main contributions to the SERS effect:111–113 the electro-
magnetic mechanism or chemical enhancement. The electro-
magnetic mechanism arises from the optical excitation of
surface plasmon resonances in the metal nanoparticles, which
leads to significant increase in the electromagnetic field
strength at the metal nanoparticle surface. In the chemical
enhancement, molecules adsorbed onto the metal nanoparticle
surface are believed to couple electronically with the surface
leading to an enhancement effect similar to resonance-Raman
scattering or via resonant charge-transfer. The extent of the
relative contribution to SERS from electromagnetic and
chemical effects remains a subject of discussion. Independent
research in several groups has shown that Raman scattering
can be enhanced up to 1014 relative to normal Raman scattering.
As such, SERS opens up opportunities for monitoring biologically
relevant molecules even at the single molecule level. SERS also
offers several other advantages for the detection of biomolecules.
First of all it is a rapid non-destructive tool and it yields
compound-specific information. Furthermore it has the potential
for multi-component analysis. Additionally, SERS spectroscopy
can be performed in the presence of water, and as such this
technique can be applied for the investigation of organic and
biochemical substances in their natural environment.
Different roughened or nanostructured metals such as coinage,
transition and alkali metals have been evaluated as SERS
substrates. The commonly used substrates for SERS are the
coinage metals Ag, Au, Cu. These metals support plasmons in
the visible region.114 Transition metals are generally not
considered as SERS-active, because it is more difficult to excite
the plasmon in the visible region. The lack of attention to
alkali metals, although they have tunable plasmon resonances
in the visible region, is due to their high chemical reactivity,
which makes their exposure to air impossible.115 The SERS
effect using Cu, Ag, Au, Li, Na, K substrates is more intense
compared to that of transition metals. The typical enhance-
ment achieved using these substrates can be as high as 104–106
whereas transition metal substrates (Fe, Co, Ni Rh, Pd and Pt)
only show enhancement up to 101–104.116 Despite their lower
SERS enhancement, transition metals do have potential in
modern industries and technologies such as electrochemistry,
corrosion and catalysis and may as such not be neglected.
There are a few comprehensive reviews that have been written
by the leading experts in this field to which the reader may
refer.117–119
Towards biological applications and chemical inertness
roughened or nanostructured Au and Ag substrates are favor-
able. Several researchers have reported on the use of AuNP
immobilized substrates for efficient biomarker detection by
SERS and others use colloidal AuNPs as SERS labels for
analysis.120,121 The research group of Van Duyne developed
gold or silver coated polystyrene nanosphere substrates func-
tionalized with a self-assembled monolayer for glucose detec-
tion (Fig. 9).122,123 The potential of AuNP array substrates as
SERS substrates was also shown by Liu et al. in the develop-
ment of a sandwich assay using crystal violet as a reporter
molecule.124 On the other hand, AuNP-modified gold sub-
strates showed improved performance as SERS substrates as
demonstrated by Cheng et al. for the detection of dipicolinic
acid, a biomarker for bacterial spores.125 Very recently, Lee
et al. reported a highly reproducible SERS-based immunoassay
for cancer marker detection by the use of hollow AuNPs
combined with an AuNP-patterned surface in a sandwich
approach. Using their SERS-based approach, a three to four
orders of magnitude increase in detection sensitivity was
obtained compared to that of conventional ELISA.126,127
The Mirkin group mainly focused on using AuNPs function-
alized with various Raman dye-labeled oligonucleotides to
derive Raman spectroscopic fingerprints for the multiplex
detection of oligonucleotide targets. After Ag enhancement,
reproducible SERS responses were obtained.128 On the other
hand, Vo-Dinh and co-workers made use of the distance
dependency of SERS caused by the rapid decay of the field
enhancement around metal spheres. In their technology,
sentinel nanoprobes (Raman-labeled DNA hairpin probe immo-
bilized on colloidal AgNPs) are used to detect oligonucleotide
targets by SERS.129 In the absence of the complementary
oligonucleotide target, a strong SERS signal is observed due
to the hairpin conformation. Upon hybridization, the hairpin
conformation is disrupted and the SERS signal is quenched
due to the physical separation of the Raman label from the
nanoparticle surface. Recently, this research team demonstrated
the feasibility of using this technology for qualitative multiplex
oligonucleotide target detection.130 Besides oligonucleotide detec-
tion, assays for protein detection have been developed using
immuno-AuNPs. In most cases the AuNPs are biofunctionalized
with the protein of interest and afterwards, a Raman-active
reporter molecule is co-immobilized. With these ‘so-called’ SERS
nanotags, superior detection limits (subpicomolar concentrations)
and sensitivities are obtained (by Proter and co-workers).131 How-
ever a major limitation of this approach is that these nanotags are
prone to spectral changes and colloidal aggregation because they
are not shielded from their environments. To overcome this
problem, several groups have employed various encapsulation
strategies. These core–shell SERS nanotags have a metallic core
Fig. 9 (A) The fabrication of silver-coated polystyrene nanosphere
substrates; known as film over nanospheres (FON) substrates.
(B) Functionalization of the gold or silver FON substrates with a self-
assembled monolayer of decanethiol–mercaptohexanol for glucose detec-
tion via SERS developed by the group of VanDuyne (The publisher for this
copyrighted material is Mary Ann Liebert, Inc. publishers).
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for optical enhancement, a reporter molecule for spectroscopic
signature and a shell for protection and conjugation.132–135
Researchers are currently exploring the use of these SERS
nanotags as biocompatible nanosensors that can be placed
inside small structures such as live cells.136 These mobile
sensors can probe the chemistry taking place in different cell
compartments by revealing SERS spectra of cellular molecules
in their close vicinity.137 Moreover, these SERS-based nano-
sensors allow structural characterization of molecules in live
cell and as such providing key information for monitoring
cellular processes such as enzymatic activity. AuNPs with reporter
molecules attached, which exhibit a known and calibrated pH
dependent SERS signal, can also act as intracellular pH sensors.
Oxonica, a nanomaterials group, has developed commercial
Nanoplext Biotags. These are nanoparticles with a diameter
of 90 nm composed of a gold core, an adsorbed layer of SERS
active molecules and a silica shell. Oxonica has developed
various nanoparticles composed of the same layer structure
but with different embedded SERS active molecules. Since
each organic molecule has its own fingerprint-like spectra,
these nanoparticles can be used for multiplexed biomarker
quantitation. In addition, Oxonica claims that their particles
are extremely stable and can be used in any biological matrix,
including whole blood. These products of Oxonica are currently
being investigated by several research groups in order to ascertain
their potential for in vitro and in vivo diagnostics. There are
currently no SERS-based diagnostic products on the market.
However, as a leading supplier of Raman instrumentation,
Renishaw has now invested in D3 Technologies Ltd. This
company is currently developing a complete SERS-based
molecular diagnostic system. They explore the use of nano-
engineered Karites SERS substrates comprising of a gold
covered regular array of holes on a silica wafer. By using these
disposable substrates they are able to identify and characterize
minute amounts of material without the use of surface chemistry.
In addition they are working on all other facets of the system
like the instrumentation to perform the measurements and the
software to evaluate the sensor output.
3.4.2 Metal-enhanced fluorescence. Fluorescence is an
established and a dominant sensing technology in medical
diagnostics and biotechnology. Although fluorescence is
known as a highly sensitive technique, where single molecules
can readily be detected, there is still a drive for further
reducing detection limits.138 The detection of a fluorophore
is usually limited by its quantum yield, photostability and the
autofluorescence of samples. To overcome some of these
constraints, intense recent research is devoted to the use of
metallic nanostructures to favorably modify the spectral properties
of fluorophores. The use of fluorophore–metal interactions has
been termed radiative decay engineering, metal-enhanced fluores-
cence or surface-enhanced fluorescence.
The current interpretation of metal-enhanced fluorescence
(MEF) is that it is comprised of two cooperative mechanisms,
a near-field effect and an induced plasmon effect.139 In the
near-field effect, the generated increased electric field between
or around the metal nanoparticles results in an increase in the
absorption cross-section of a nearby fluorophore and sub-
sequently an increase in the fluorescent emission. Partially energy
transfer from the fluorophore to the surface plasmon (induced
plasmon effect) results in enhanced plasmon scatter that
positively influences the fluorescent emission with or without
reducing the excited-state decay time. As such, MEF is also
supported by the scattering component of the metal extinction,
i.e. the ability of fluorophore-coupled Plasmon’s to radiate.
The first experimental and theoretical reports on metal-
enhanced fluorescence in the 1970’s and 1980’s have however
been overshadowed by the large signal enhancements seen
with SERS. In SERS, enhancement factors of 1014 have been
frequently reported whereas the increase in fluorescence signal
of appropriate fluorophores near metal nanostructures is only
a factor of B10.140 Although both technologies require the
proximity of a metal nanostructure to enhance the Raman or
fluorescent properties, they do have different requirements.
For example, efficient SERS requires close contact of the
studied molecules with the metallic surface, at distance below
20–30 A whereas at this distance, the fluorescence of the
molecules is significantly quenched, primarily by energy transfer
to the metal surface. In MEF, the optimal separation distance of
the fluorophore and the metal nanoparticles is larger, but very
limited.When the fluorophores were placed at leastB11 nm from
the nanostructured metals or from shell protected nanoparticles,
enhanced fluorescence has been reported.140,141 For example,
Aslan et al. used an additional silica coating around the metal
nanoparticles to provide the surface nanostructure functionality
(Fig. 10), the surface plasmon absorption and to tune and
ensure the distance of the fluorophores from close-range metal
quenching.142,143 Also other spacers, including DNA strands
or antibodies, have been used to obtain efficient fluorophore–
metal separation for enhanced fluorescence observations.144
The fluorophore emission near metal nanoparticles depends
not only the fluorophore–particle surface distance but also the
molecular dipole orientation versus particle surface. Zhang
et al. also reported on the wavelength dependency of MEF.145
Fig. 10 Comparative emission spectra of a fluorescent (doped with
Rhodamine 800) core–shell Ag@SiO2 nanoparticle and a control nano-
particle containing no Ag. The optimal thickness of the shell is around
11 nm. These core shells Ag@SiO2 show potential for applications in
MEF solution-based sensing (Journal of Fluorescence by Springer
New York LLC. Reproduced with permission of Springer New York
LLC in the format Journal via Copyright Clearance Center).
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There is a correlation with the scattering portion of the
extinction spectrum of metal nanoparticles and MEF.
Furthermore, several research groups have reported on the
effect of AuNP size and shape on the fluorescent properties of
a fluorophore.146,147 Particles with large scattering cross-section
increase the fluorescence yield, as is the case for gold nanoshells,
nanorods, and nanoparticles of larger size. This can be simply
explained by the angular dependent nature of plasmon scattering
and the scattering vs. absorption contribution to the gold
extinction spectrum favoring the fluorescent emission.
The observation of fluorescence enhancement has been
limited to silver nanoparticles and the effect of AuNPs on
fluorophores can only be found sporadic.148 Gold serves as an
ultra-efficient quencher of the light exciting fluorophores as
demonstrated for several AuNP–fluorophore composites and
used in various homogenous assays for DNA and protein
detection.149 Nevertheless, Matveeva et al. demonstrated a
strategy to reverse the quenching of fluorescence by AuNPs
to enhancement by using an additional coating of silver.141
Also Aslan et al. and Cheng et al. demonstrated that AuNPs
of sufficient large size (Z 100 nm), where the fluorophore is
separated by a spacer layer of at least 10 nm from the AuNP
surface, ensure MEF.147,150 There are still many indications
for using gold instead of silver for MEF because gold has
better chemical stability and the surface chemistry is well under-
stood, while surface modification and binding of biomolecules
can easily be accomplished. In this respect, some development of
homogeneous assays for the detection of DNA and proteins can
be found. For example, a label free DNA sensing by using the
fluorescence quenching and enhancement was shown by Cheng
et al.150 They developed a homogenous assay for the detection of
DNA based on fluorescently labeled DNA hairpin probes and
reported a detection limit below 100 pM of target DNA. Most
recently the detection of terbium-levofloxacin, a synthetic
chemotherapeutic antibiotic derived from a fluorinated quinolone,
was demonstrated in pharmaceutical preparations,151 opening the
potential application of this technique for pharmaceutical research.
4. Discussions and future perspective
As illustrated from the literature survey, many techniques have
been or are being developed for chemical and biological
sensing and analysis based on the optical properties of AuNPs.
Briefly, the following is a summary of the advantages and
disadvantages of each detection method and the remaining
challenges.
Detection based on the LSPR property change of AuNPs is
perhaps the easiest technique to use. It requires low cost, well-
known instruments such as a UV-Vis spectrophotometer, or
sometimes, even no instrument. Similar to the SPR technique,
LSPR techniques can be considered as ‘‘label-free’’ detection.
Sensing molecules such as antibodies or chemical ligands do
need to be immobilized on AuNP probes (while in SPR, they
are immobilized on a gold monolayer film), however, there is
no need to label the target analyte or use an optically-labeled
sensing molecule or binding ligand. This detection can be used
for both homogeneous solution or heterogeneous assay formats.
The major downside of this technique is the relatively low
sensitivity. Although some improvements can lead to higher
sensitivity, most reports have shown the detection limit for protein
in the ng per mL regime and DNAs down to nM. The LSPR
technique has also been used for small chemical detection. Another
problem for homogeneous solution based LSPR detection is the
color of the sample. Because LSPR is in principle a colorimetric
method, this technique is not suitable for analyte detection
from intensely colored samples. Although AuNPs with a
LSPR wavelength at near-IR can be used for deeply colored
samples such as blood, they require the use of gold nanoshells,
nanorods, or other non-spherical AuNPs. However, their
synthesis method is much more complicated than the citrate-
protected spherical AuNPs and associated with this, it is a
significant challenge to functionalize them with biomolecules.
LSPR-based techniques have been successfully commercia-
lized. The most known one is the pregnancy test kit. Also the
SoPRanot product, which makes use of a homogenous assay
format with spherical AuNPs, has been commercialized by
PharmaDiagnostics. A heterogeneous analog product, Light-
Patht was recently launched by LamdaGen Corporation.
Overall, light scattering-based techniques have a substan-
tially higher sensitivity compared to adsorption-based techni-
ques. A number of highly sensitive techniques were all based
on the light scattering of gold and silver nanoparticles. The
light scattering cross-section of AuNP increases dramatically
when the diameter of AuNPs exceeds 80 nm. Many biological
sample matrices such as blood and serum also scatter light
intensely, since it contains a high concentration of colloidal
particles. By using large AuNPs (exceeding 80 nm), the light
scattering detection can be used for a wide variety of samples,
including blood and serum. The instrument used for light
scattering detection can be a typical spectrophotomer, or
dynamic light scattering (DLS) instrument. The cost of a
DLS instrument is only slightly higher than most spectro-
photometers. The light scattering from AuNPs does not suffer
from photobleaching and instability issues as in the case of
fluorescence-based techniques.
The nanoparticle-enabled dynamic light scattering assay
(NanoDLSayt) provides unique advantages and capabilities
for biomolecular research. NanoDLSayt not only can be used
for target analyte concentration analysis, it can reveal the
‘‘size’’ information of the analyte directly from the assay. This
capability is particularly useful for studying protein–protein
interaction and for complexed protein detection and analysis.
In terms of simple concentration analysis of protein analytes,
NanoDLSayt is on par with most other existing immunoassay
techniques. For the detection of DNA, metal ions, and virus,
NanoDLSayt has shown 1–5 orders of magnitude of improved
sensitivity compared to many other existing techniques. Nano
Discovery Inc. is commercializing NanoDLSayt. The company
has developed a new DLS instrument, NDS1200, that is
especially designed for high throughput analysis and also
simultaneous kinetic study of multiple samples automatically
using a NanoDLSayt technique.
There have been mainly two forms of detection methods based
on the surface chemistry of AuNPs. The DNA bio-bar-code
method developed by Mirkin’s group has the distinct advantage
of an ultra-high sensitivity of detection. This method probably
provides the best sensitivity for protein detection among all
existing analytical techniques. The DNA bar code attached to
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the AuNPs leads to very unique integration of both high
sensitivity detection and multiplexing analysis capability.
The drawbacks of this method are the relatively high cost
associated with AuNP probe preparation, the multiple steps
that are required for conducting the assay and the assay
format that is still based on a heterogeneous solid–liquid
interface assay. The other surface chemistry-related detection
method is based on the reversible binding of a fluorescent
polymer introduced by Rotello’s group. The most appealing
advantage of this technique is that one does not need to know
the specific molecular identity of the target in order to detect
the target from a sample matrix. This capability should be
particularly useful for detecting new pathogens and targets of
which the identity is not known or completely known.
As already stated, light scattering based technologies have
the advantage of high sensitivity and this is also the case for
SERS-based detection and analysis. This technique relies on
the interaction of the metal core and the surface ligands. Upon
excitation of the plasmon the electromagnetic field in close
neighborhood of the AuNP surface is enhanced, and in
addition also resonant-charge transfer to chemisorbed molecules
can occur, giving rise to an extreme enhancement of their
corresponding Raman signal. SERS-based biosensing relies
mainly on heterogeneous assay formats, although homogenous
formats do exist. This technology provides specific molecule
information and is not influenced by the sample matrix. More-
over, the SERS technique can be conveniently adapted for
multiplexing analysis. A SERS-based diagnostic product is being
commercialized by D3 Technologies Ltd. Other companies have
commercialized modified AuNPs (Nanoplext Biotags from
Oxonica Inc) or nano-engineered substrates (Karites from
Renishaw Diagnostics) for research purposes.
The last optical property of AuNPs that was described in
this review is metal-enhanced fluorescence. This technology is
perhaps the leastmature of all optical sensing technologies described
here. This has mainly to do with the various constraints related to
the technology. To achieve fluorescent enhancement, the distance
between the fluorophore and the metal nanoparticles needs to be
well controlled. Additionally, the molecular dipole orientation, the
applied excitation wavelength, the AuNP size or shape can all affect
fluorescent enhancement. Nevertheless this sensing technology can
improve the detection limit of the widely used fluorescence-based
detection methods both in homogenous and heterogeneous assay
formats, therefore, is worth of continuing investigation.
5. Conclusions
In summary, research has been extremely productive in AuNP-
enabled biological and chemical sensing and analysis. In the past
ten years, many new techniques have been developed and a
significant number of these techniques have been or are very
close to be commercialized. These new techniques not only
substantially improved the detection limit, but further brought
new analytical capabilities that enable scientists to discover
molecular information related to diseases and other biological
processes that cannot be revealed by existing techniques. All these
accomplishments clearly demonstrate and testify the significance
of nanotechnology in the advancement of modern science and
knowledge.
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