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BIOSENSOR TECHNOLOGY APPLIED TO
HYBRIDIZATION ANALYSIS AND MUTATION DETECTION
PETER NILSSON
ROYAL INSTITUTE OF TECHNOLOGY
DEPARTMENT OF BIOTECHNOLOGY
STOCKHOLM 1998
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Peter Nilsson (1998) Doctoral DissertationBiosensor technology applied to hybridization analysis and mutation detection.Dept. of Biotechnology, KTH - Royal Institute of Technology, 100 44 Stockholm, Sweden.ISBN 91-7170-322-5
ABSTRACT
This thesis demonstrates the application of biosensor technology for molecular biology
investigations, utilizing a surface plasmon resonance based optical device for mass sensitive
detection of biomolecular interactions at a chip surface. Oligonucleotide model systems were
designed for analysis of the action of DNA manipulating enzymes. DNA ligation, DNA
cleavage and DNA synthesis could be quantitatively monitored in real-time. A protocol for
DNA minisequencing was also established, based on prevention of chain elongation by
incorporation of chain-terminators. Determinations of affinities for short oligonucleotides
hybridizing to an immobilized target, were performed with various sequence content, length,
temperature and degree of complementarity. The decrease in affinity for hybridizations
involving mismatch situations was found to be strongly dependent on the relative position of
the mismatch. Interestingly, also end-mismatches were clearly detectable. The stabilization
effect achieved upon co-hybridization of two adjacently annealing short oligonucleotide
modules (modular primer effect) was also investigated for different module combinations and
hybridization situations. The modular concept of hybridizations was subsequently
demonstrated to result in enhanced capture of single stranded PCR products. The sequence-
based DNA analysis, first introduced with oligonucleotide model systems, was extended to the
scanning and screening for mutations in PCR amplified DNA from clinically relevant samples.
Several different formats were investigated, either with the PCR products immobilized on the
chip and oligonucleotides injected or vice versa. Again, mismatch discrimination could be
observed for wild type and mutant specific oligonucleotides hybridizing to the targets. The
experimental set-up for mutation detection was further developed by the introduction of a
subtractive mismatch sensitive hybridization outside the instrument and a subsequent
determination of the relative amounts of remaining oligonucleotides with analytical biosensor
monitoring of hybridizations between fully complementary oligonucleotides. In conclusion, the
applied technology was found to be a suitable tool for a wide range of molecular biology
applications, with emphasis on hybridization analysis and mutation detection.
Keywords: biosensor, genosensor, surface plasmon resonance, hybridization, nucleic acids,
oligonucleotide, mutation detection, mismatch discrimination, modular
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LIST OF MAIN REFERENCES
This thesis is based on the following reports, which will be referred to in the text by their
Roman numerals:
I Nilsson, P., Persson, B., Uhlén, M. and Nygren, P-Å. (1995).
Real-time monitoring of DNA manipulations using biosensor technology.
Analytical Biochemistry 224: 400-408. A
II Persson, B., Stenhag, K., Nilsson, P., Larsson, A., Uhlén, M. and Nygren, P-Å. (1997).
Analysis of oligonucleotide probe affinities using surface plasmon resonance: a means for
mutational scanning.
Analytical Biochemistry 246: 34-44.A
III Nilsson, P., O’ Meara, D., Edebratt, F., Persson, B., Uhlén, M., Lundeberg, J. and
Nygren, P-Å. (1998)
Quantitative investigation of the modular primer effect for DNA and PNA hexamers.
(submitted)
IV O’ Meara, D., Nilsson, P., Nygren, P-Å., Uhlén, M. and Lundeberg, J. (1998).
Capture of single-stranded DNA assisted by oligonucleotide modules.
Analytical Biochemistry 255:195-203. A
V Nilsson, P., Persson, B., Larsson, A., Uhlén, M. and Nygren, P-Å. (1997).
Detection of mutations in PCR products from clinical samples by surface plasmon resonance.
Journal of Molecular Recognition 10:7-17. B
VI Nilsson, P., Larsson, A., Lundeberg, J., Uhlén, M. and Nygren, P-Å. (1998).
Mutational scanning of PCR products by subtractive oligonucleotide hybridization analysis.
BioTechniques (in press) C
The articles are reproduced with the permission of the copyright holders;©Academic Press, Inc. A, ©John Wiley & Sons, Ltd. B, ©Eaton Publishing Inc. C
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TABLE OF CONTENTS
INTRODUCTION
SEQUENCE-BASED DNA ANALYSIS 8
HUMAN GENOME PROJECT 10
MUTATION DETECTION 11
Scanning for unknown mutations 12
Screening for known mutations 13
DNA arrays 15
Sequencing by hybridization 15
DNA chips 17
BIOSENSORS 19
Electrochemical transducers 19
Amperometric 19
Potentiometric 20
Conductimetric 21
Mechanical transducers 22
Piezoelectric 22
Thermal transducers 23
Calorimetric 23
Optical transducers 24
Evanescent wave 24
Surface plasmon resonance 24
Optical waveguiding 28
Other optical devices 29
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TABLE OF CONTENTS
RESULTS AND DISCUSSION
INTRODUCTION 31
REAL TIME MONITORING OF DNA MANIPULATING ENZYMES (I)
32
DNA assembly using DNA ligase 32
Endonuclease cleavage 33
DNA synthesis by DNA polymerases 33
MISMATCH DISCRIMINATION IN OLIGONUCLEOTIDES (I, II) 34
Minisequencing (I) 34
Hybridization analysis by determination of equilibrium affinities (II) 35
Mutational scanning and influence of mismatch position (II)
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ANALYSIS OF MODULAR HYBRIDIZATIONS (III, IV) 38
Increased stability by modular hybridizations (III) 38
The use of oligonucleotide modules for capture (IV) 40
MUTATION DETECTION IN CLINICAL SAMPLES (V, VI) 41
Mutation detection on immobilized or injected PCR amplicons (V) 41
Mutation detection by subtractive hybridizational scanning (VI) 43
CONCLUDING REMARKS 45
ABBREVIATIONS 46
ACKNOWLEDGEMENTS 47
REFERENCES 48
APPENDIX
Main references I - VI
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INTRODUCTION
SEQUENCE-BASED DNA ANALYSIS
equence-based DNA analysis is today a corner-stone in many clinical and research
fields, such as biology, biotechnology, evolutionary studies, forensic science and a
wide variety of branches within the field of medicine. The analysis can roughly be
divided into two different areas; sequence specific detection or sequence determination. The
first type of analysis is aiming at detecting the presence of a certain nucleotide sequence in a
complex background, either for the purpose of identification, localization or just presence.
Sequence determination is more advanced and is aiming at identifying a specific nucleotide at a
specific position or more commonly, determine the whole sequence, i.e. the identities and
order of nucleotides in a DNA fragment.
The constantly increasing importance of sequence-based DNA analysis can not be argued by
anyone today. There has been an enormous development of technology for this purpose, since
the landmark paper by Avery et al in 1944, where it for the first time was suggested that DNA
and not protein is the hereditary material. Another more than obvious milestone is the Watson
and Crick paper in 1953, describing the double stranded helical nature of DNA and the
principle of the basepairing.
There have of course been many scientific breakthroughs related to DNA analysis during the
last decades, but three out of the major technical and methodological achievements are here
selected as very important for the present sequence-based DNA analysis and many of the more
recent developed techniques have utilized one or more of those three as a methodological
starting point.
E. M. Southern described in 1975 how specific nucleic acids could be identified in complex
mixtures using a technique later termed Southern blotting. In its typical format, the DNA to be
analyzed is fragmented with e.g. a restriction enzyme. The fragments are separated according
to size by gel electrophoresis and subsequently transferred to a filter or membrane. A labeled
DNA probe is hybridized, allowing the detection of its complementary sequence present on the
filter. This sequence specific hybridizational detection of nucleic acids and variants thereof, is
still a major component in many of the later developed techniques for the analysis of nucleic
acids.
S
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A Nobel Prize awarded technique for determining the sequence of a DNA fragment
enzymatically was presented by Sanger et al in 1977. The method is now called Sanger or
dideoxy sequencing. A labeled primer is hybridized to a single stranded version of the DNA to
be sequenced. Added DNA polymerase extends the primer in the presence of the four
nucleotides and one chain-terminating dideoxynucleotide, which also can be an alternative
molecule to label. The terminator will be incorporated in a fraction of the fragments when the
nucleotide in the template is complementary to the dideoxynucleotide and prevent any further
extension of that fragment. After completed DNA synthesis, the reaction mixes from the use of
different terminators will contain fragments of different lengths, where each length corresponds
to a nucleotide position in the template. The fragments in the four reactions (one for each
dideoxynucleotide) are separated by gel electrophoresis and the sequence can be determined by
the order of the fragments from the four reaction mixes.
The third highlighted epoch-making, in the context of biotechnology, technique is the
polymerase chain reaction (PCR) (Mullis, 1986; 1987; Saiki, 1985; 1988), which also was
awarded the 1993 Nobel Prize in chemistry (K. B. Mullis). With the PCR came the ability to
selectively and exponentially amplify a desired DNA sequence present in complex mixtures and
produce millions of copies of it. "It is like finding a needle in a haystack and then make a new
stack of that needle" is a metaphor frequently used to describe PCR. The principle is simple
and in its simplest form based on enzymatic DNA synthesis in three-step temperature cycles
involving, denaturation of double strands, annealing of primers and finally, polymerase-
dependent primer extension. The procedure is repeated for approximately 30 cycles, leading to
a theoretical accumulation of approximately 230 copies of the desired fragment. The inventive
step was to combine a thermostable enzyme with the thermocycling and thereby avoiding the
need to add new enzyme after each cycle, which also led to increased primer specificity by
enabling a higher annealing temperature.
Both the PCR technology and the Sanger sequencing method have, in many aspects,
continuously been further developed and also several different variants of those techniques
have arisen. The triumphant introduction of the Sanger sequencing and the PCR amplification
and also the power of the combination of these techniques together with progress in
automation have led to a dramatic increase in sequencing capacity. Large scale sequencing
projects could be accomplished and with the increasing speed at which DNA sequence
information was generated, it was realized that the whole human genome would be possible to
sequence and an international human genome project was initiated.
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HUMAN GENOME PROJECT
The human genome project (HGP) is coordinated and mainly funded by the US Department of
Energy (DOE) and the US National Institute of Health (NIH) and was formally started in 1990
after five years of debate and planning. Also several Japanese and European consortiums, such
as the Welcome Trust, UK, is involved in funding HGP. In 1988 the US National Academy of
Science reported that the complete human genome could be mapped and sequenced within 15
years. According to the original plans, the project would then be finished by the year 2005. A
5-year report in 1995 although stated that the project was ahead of schedule and that the goal
of having all human genes (approximately 80 000) discovered and the sequence of the
approximately 3 billion DNA bases determined, could be reached sooner than first estimated.
Several other genomes than the human are also included in HGP, as a way to increase the
knowledge of genome organization and for comparative genomic analysis. Among the non-
human organisms are several of the most studied and frequently used for experimental
manipulations, such as Saccharomyces cerevisiae (yeast), Escherichia coli (bacteria),
Drosophila melanogaster (fruitfly), Caenorhabditis elegans (nematode), Arabidopsis thaliana
(plant) and Mus musculus (mouse). In September 1998, 16 complete microbial genomes had
been completely sequenced, including S. cerevisiae and E. coli, and the complete sequencing
of the 97 Mb genome of C. elegans is predicted to be finished before the end of 1998. The
human genome had at the same time been sequenced to roughly 7 % (207 Mb / 3 Gb), if only
contigs longer than 1 kb are counted (116 Mb with 100 kb cut-off). The rate of sequencing has
been doubled the last two years and the estimation for the end of 1998 is 320 Mb of finished
sequence (Venter, 1998), corresponding to almost 11% of the genome.
HGP has greatly contributed to the increased rate of production of high-resolution maps,
which have been very important for the accelerated pace of discovery and identification of
disease related genes. The mapping and sequencing has proceeded in parallel. Sequence-based
gene discovery is although more and more replacing the map-based discovery by the shift from
structural to functional genomics with the aid of comparative genomics (McKusick, 1997).
The impact from this enormous sequencing and mapping effort on biology and medicine
research will probably lead to a paradigm shift, where some information of all genes are
available in databases. The databases themselves will be an important research tool for many
scientists and a lot of knowledge of genomic function can be gained directly from the
databases. Identification of sequence homology between human and other species, such as
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yeast, can help define the function of genes. The increasingly high rate of genes being
identified, sequenced and given a function, will for certain be important for the analysis of
genes related to the development of diseases. More than 600 allelic variations of genes with
known disease-producing mutations have been catalogued (McKusick, 1997).
Figure 1. Human genomic sequences in the EMBL database. The columns represent the accumulated amountof sequence with contigs of at least 1 kb. The line represents the percentage finished sequence of the totalapproximately 3 Gb. Numbers are taken from the Genome Monitoring Table (Beck, 1998)(http://www.ebi.ac.uk/~sterk/genome-MOT/). * Estimated
MUTATION DETECTION
The spectrum of mutations ranges from large chromosomal rearrangements to small deletions,
insertions and single base substitutions. Identification of mutations in nucleic acids is an
important part of genetic research, not at least for the prediction and diagnosis of diseases.
Many methods for detecting mutations exists, based on a wide range of different technologies.
There is a constant flow of reports of new or improved methods, all with the hypothetical goal
of obtaining an optimal system, in the aspect of sensitivity, selectivity, simplicity, reduced time
and cost etc. Certainly, the complete determination of the whole DNA sequence in the region
of interest, is the optimal result that can be achieved. DNA sequencing is although still
relatively time consuming and costly and therefore a need for complementary methods exists.
These could at least be a first selective step to sort out a reduced amount of samples later
0
40
80
120
160
200
240
280
320
pre-1990 1990 1991 1992 1993 1994 1995 1996 1997 1998 (Sep)
1998(Dec)*
[Mb]
0
1
2
3
4
5
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7
8
9
10
11
[%]
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subjected to complete sequence determination or even obviate the need for sequencing if the
method allows for description of the exact nature of the mutation.
The different methods can be divided by their purposes, scanning or screening. Scanning
procedures are aiming at the search for unidentified variations, in comparison to the known
wild type sequence, across one or several whole genes or parts thereof. Screening methods are
on the other hand more devoted to detecting predefined mutations at specific positions, so
called hot spots. Those should be able to handle larger amounts of samples, since population
based carrier screening can be required for efficient identification of disease alleles. The
scanning and screening terminology have been defined in different ways, such as that screening
methods is used for detection of unknown mutations (here called scanning) and diagnostic
methods is used for the detection of defined mutations (here called screening) (Cotton, 1993).
Some of the most commonly used methods for the detection of small alterations in a sequence
have here been selected for a brief overview of their basic original principles. All of them have
continuously undergone developments and there are many different variants existing of each
type here described, where each usually have been denoted with a new acronym.
Scanning for unknown mutations
The first methods to be introduced for routine analysis were all based on mobility shifts in gel
electrophoresis and only with the ability to determine if a sample contained sequence
differences, compared to a known wild type sequence, not what kind of changes that had
occurred. In the SSCP method (single strand conformation polymorphism analysis) (Orita,
1989), PCR products are heat denatured and rapidly cooled for avoidance of reassociation.
The single strands form sequence dependent conformations that influence gel mobility and
different mobility indicate sequence differences. Despite the fact that the sensitivity and
specificity is relatively low (Jordanova, 1997), SSCP is still widely used. Once the protocol has
been optimized for a specific analysis, the simplicity is attractive for routine analysis as a first
sorting step.
Denaturing gradient gel electrophoresis (DGGE) (Fischer, 1983) is a similar method in which
the differences in stability for double-stranded DNA of different compositions are utilized. The
point of denaturation where the double-strands starts to turn into single-strands, due to a
gradient in temperature or chemical denaturant, is detected by gel electrophoresis and single
nucleotide alterations are possible to detect.
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A third method based on sequence dependent conformation variations is heteroduplex analysis
(HA) (White, 1992). PCR amplified sample and wild type DNA is mixed, denatured and
renatured, resulting in homoduplexes and heteroduplexes. If the heteroduplexes contain
different alleles, the presence of mismatched basepairs can affect the mobility through a gel.
Several different compounds have been used for the cleavage of mismatched regions in
heteroduplex DNA, usually analysed by the appearance of short fragments in a gel
electrophoresis, although with various degree of success. In chemical mismatch cleavage
(CMC) (Cotton, 1988) the mismatches are modified by osmium tetroxide or hydroxylamin and
then cleaved by piperidine. Enzymatic mismatch cleavage (EMC) methods involve RNase
(Myers, 1985), T4 Endonuclease VII (Youil, 1995) and the E. coli mismatch repair enzymes
(MutH, MutL and MutS) (Smith, 1996). The binding of MutS, which is responsible for the
recognition of the mismatch, has also been used alone without successive cleavage (Bellanne-
Chantelot, 1997).
Screening for known mutations
Knowledge of the position and the surrounding sequence of the eventual mutation investigated
allows for a discrimination of samples by differential sequence specific hybridization analysis.
This technique is broadly used in several of the existing screening methods, of which some also
have the possibility to determine not only the presence, but also the identity of the mutation.
The use of allele-specific oligonucleotides (ASO) for mutation detection was the first method
devoted for mutation detection (Cotton, 1993). Utilizing the principles of Southern blotting,
Wallace and coworkers (1981) could discriminate between the hybridizations of mutant and
wild type specific oligonucleotides to membrane immobilized mutant genomic material. A
direct immobilization of PCR amplified sequences on a membrane, followed by a measurement
of the relative quantities of a label from hybridized mutant or wild type oligonucleotides have
been denoted the dot blot format (Saiki, 1986). A reverse dot-blot format is then obviously
consisting of immobilized oligonucleotide probes to which an amplified target is hybridized
(Saiki, 1989). This format allows for simultaneous analysis of many different alleles. Numerous
copies of a single PCR product are let to hybridize under stringent conditions to an array of
immobilized oligonucleotides and after rigorous washing the positions of the labeled target can
be visualized.
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By designing a PCR primer so that the 3'-end is localized on the position of the mutation, a
mismatch in that position will prevent extension and hence no amplification can occur. This
method was in 1989 described by several groups, extending the list of existing method
acronyms; allele-specific amplification (ASA) (Okayama, 1989), amplification refractory
mutation system (ARMS) (Newton, 1989), allele specific polymerase chain reaction (ASPCR)
(Wu, 1989) and PCR amplification of specific alleles (PASA) (Sommer, 1989).
Figure 2. A schematic view of the principles of some of the most commonly used scanning and screeningmethods for mutation detection. Adapted from Cotton, 1993.
Several variants exist of methods based on the mismatch discrimination displayed by DNA
ligase upon the covalent joining of adjacently hybridized oligonucleotides. If an internal end-
nucleotide is affected by a mismatch, the ligation is inhibited. The detection of the ligation
product was in the original method, oligonucleotide ligation assay (OLA) (Landegren, 1988),
performed with solid phase capture of one of the oligonucleotides via the biotin-streptavidin
system and the presence of a ligation product could be detected by a label on the second
oligonucleotide. With the avoidance of electrophoretic separation, the method has also been
shown to be amenable for automation (Nickerson, 1990). The discovery of a thermostable
SSCP
DGGE
HA
CMCEMC
ASO
ASA
OLA
PEX
Normal Mutant
Changedmobilityin gel
Cleavage
No duplex
No amplification
No ligation
No extension
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ligase led to the introduction of ligase chain reaction (LCR) (Barany, 1991), in which the
ligated product of oligonucleotide pairs is exponentially amplified, if there are no mismatches
in the position of nucleotide joining.
Single nucleotide primer extension (PEX) or DNA minisequencing (Syvänen, 1990) is a
method where the identity of a mutation can be determined. A primer is annealed adjacent to
the site of the mutation on an immobilized target and is extended by DNA polymerase with a
single labeled nucleotide, if it is complementary to the site of mutation. By dividing the target
and primer into four different reactions, a different nucleotide can be added to each. Not only
the identity is determined but also the ratio between different alleles. This concept has also
been applied on oligonucleotide arrays (Pastinen, 1997).
A relatively recently developed technology for sequence determination of short DNA fragment
is called pyrosequencing (Ronaghi, 1998), where an approach radically different from all other
existing methods have been applied. A four-enzyme mixture is utilized for the detection of
released pyrophosphate groups (PPi) during DNA polymerase dependent extension.
Nucleotides are added to a primer/template duplex in an iterative way and eventual
incorporation on the primer is measured by the conversion of pyrophosphate, via ATP, to light.
DNA arrays
Sequencing by hybridization
The idea of sequencing by hybridization (SBH) is elegant and large efforts have been made
during the ten years that has passed since the first reports, to make this principle working not
only in theory but also in practice. It is not hard to imagine that the influence from the allele-
specific hybridization experiments described above was important for the appearance of the
SBH strategy. With the insight that a large amount of different oligonucleotides could be
separately immobilized on a solid support, it was realized that a target DNA sequence could be
determined if all possible combinations of a short oligonucleotide were orderly immobilized,
and to which the labeled target to be sequenced was hybridized. The sequencing strategy is
based on computer assisted assembly of the target sequence with the knowledge of the
sequence identity of the oligonucleotides that the target has hybridized to. For the step going
from a theory to a method that can be applied in practice is it of course necessary to find
hybridization conditions able to discriminate between match and mismatch situations.
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Figure 3. A schematic outline of the principle of sequencing by hybridization. All possible combinations of ashort oligonucleotide, which is here exemplified with dimers, are immobilized on a solid support. The target,which is here a hexamer, is hybridized under conditions where only fully complementary sequences can createstable duplexes. The immobilized complementary oligonucleotides are identified by a label on the target andthe overlapping sequences can be assembled to a continuous complementary sequence, revealing the targetsequence.
Two groups independently described the theoretical principle of the methodology in papers
submitted in 1988 (Lysov, 1988; Drmanac, 1989). Drmanac and coworkers envisioned a dot-
blot format (also denoted format 1) in which 95 000 11-mers consecutively should be
hybridized to immobilized genomic clones in order to sequence 1 Mb. In contrast, Lysov and
coworkers foresee a reverse dot-blot format (format 2) with a complete set of immobilized
octamers (48=~65 000) for the sequence determination of a target of a few hundred basepairs.
However, the experimental results of sequencing by hybridization did not indicate an
immediate success and most involved researchers had finally to realize that SBH was not
perfectly suited for de novo sequencing, but definitely for other types of sequence-based DNA
analysis, such as confirmatory sequencing and mutation detection (Drmanac, 1998).
DNA chips
AA CTAG TTCT TA CTTAAG GAATTCTA AATT AG
GAATTC GAATTC AA AC AG AT
GAATTC CA CC CG CT
GA GC GG GT GAATTC GAATTC TA TC TG TT
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The introduction of chip based technology for the creation of high-density microarrays of
oligonucleotides has recently had an enormous impact on sequence-based DNA analysis. It
was originally the need to develop functional SBH array systems that led to the development of
the now existing chip technology. The procedure can be summarized in five steps; i)
immobilization of oligonucleotides or amplified DNA fragment on the chip which usually is a
coated glass plate; ii) sample preparation including labeling and fragmentation; iii)
hybridization and washing; iv) scanning; v) complex algorithms for data interpretation.
Several groups have developed variants of methods for immobilization of nucleic acids. The
oligonucleotides can either be attached presynthesized or synthesized in situ, on the chip, as
described e.g. by Southern et al (1992) who used standard reagents for oligonucleotide
synthesis in a circular reaction chamber. They have applied a combinatorial technique for the
arraying of all possible matching oligonucleotides in a given region for the selection of
antisense reagents (Milner, 1997). Another technique for in situ synthesis is the
photolithography (Pease, 1994), which is adapted from the semiconductor industry and based
on light-directed removal of protecting groups from the nucleotide with the aid of a masking
system. All possible oligonucleotides of a given length (n) can be synthesized in 4 x n cycles.
The current generation of technology allows for the fabrication of approximately 320 000
distinct oligonucleotides in a 1.6 cm2 array, where each spot is 20 µm in diameter and contains
~107 probes (Wang, 1998). Such chips have recently been successfully applied to extensive
analysis of sequence variations (see e.g. Chee, 1996; Hacia, 1996; Kozal, 1996; Wang, 1998;
Winzeler, 1998) and monitoring of gene expression levels (Lockhart, 1996; Wodicka, 1997).
Mirzabekov and coworkers have developed another variant of attaching pre-synthesized
oligonucleotides to the chip surface, namely via patches of activated polyacrylamid in small gel
pads (Yershov, 1996). This technique has also been used for immobilization of PCR products
(Proudnikov, 1998). However, this is not a high-density array system, recent published reports
with analysis of temperature melting curves for mutation detection (Drobyshev, 1997) and
thermodynamic analysis (Fotin, 1998), demonstrated the use of 64 pads on a chip. The
immobilization capacity for each spot is although higher than for other systems.
Researchers at the Stanford University, CA, have developed an array system where amplified
DNA is immobilized on the chip instead of oligonucleotides. They have for instance PCR
amplified all open reading frames (ORF) from the yeast genome and spotted those more than
6000 amplicons on the arrays, which have been used for genome wide comparative gene
expression analysis (DeRisi, 1997; Lashkari, 1997a; b). Furthermore, oligonucleotides
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corresponding to all genes in the yeast genome have been arrayed on a chip by light-directed
photolitographic synthesis (as described above) for analysis of genetic selections and genome
wide transcriptional analysis (Cho, 1998a; b). For a recent review on the advances in
microarray technology, see Schena, 1998.
The sample preparation is a crucial step. Fragmentation of the amplified target can be utilized
to obtain less secondary structure and lower risk for multiple interactions. Different means of
fragmentation have been described, such as cleavage by deoxyribonuclease (Wang, 1998) or by
fragmentation of RNA. In the latter case, the target DNA amplification or the reverse
transcription of mRNA to cDNA is performed with primers containing RNA polymerase
promotor sequences, for subsequent in vitro transcription. The instability of RNA is utilized for
heat and salt fragmentation to 20-40 mers (Drobyshev, 1997) or 30-50 mers (Wodicka, 1997).
The labeling procedure is also an important part of the sample preparation and several different
variants have been explored (Chee, 1996). In general, the last step of nucleic acid amplification
is utilized for incorporation of dye-labeled primers or polymerase assisted incorporation of
fluorescent labeled nucleotides for direct scanning after hybridization or with biotinylated
nucleotides, which require a post-hybridizational adding of a dye-streptavidin conjugate.
All those described chip technologies are depending on having some sort of label incorporated
into the sample. One way to simplify the DNA array technology is to remove the need to label
hybridized samples. Alternative methods for detecting the specific spots where stable duplexes
have been formed must then be found. Since the hybridization signals often are spread over the
whole spectrum of signal intensities, due to the problems to discriminate all perfect matched
hybridizations from all mismatched situations, a system which at least is capable of measuring
relative quantities of hybridized sample DNA is desired. The label-free detection principles
developed for biosensors could possibly be imagined to be applicable also to high-density DNA
micro arrays.
BIOSENSORS
Generally, biosensors can be regarded as real-time analytical devices comprising a transducer
coupled to a sensing unit capable of detecting biological molecules at a surface. Such
molecular sensors combine the specificity of a biological recognition mechanism with a
physical transduction technique, which can be based either on electrochemical, mechanical,
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thermal or optical sensing principles. The most usual aim of a biosensor is to produce
continuous signals that are proportional to the amount of molecules bound to or reacting at the
sensor surface.
There are a wide variety of transducers used in biosensors and a brief overview of the different
types of sensing principles will be described here, with the focus on recent developments in
nucleic acid based biosensors (Bier, 1997a; Yang, 1997; Zhai, 1997). Genosensors, which they
also have been denoted, have gained large attention as attractive analytical tool as late as in the
beginning of the 1990’s, whereas the more traditional enzyme sensors, immunosensors and
microbial sensor have undergone several decades of development. Nucleic acid based
biosensors normally employ immobilized DNA oligonucleotides or fragments on the sensor
surface, as the recognition element. Sequence specific hybridizations or interactions with
DNA-binding proteins can then be monitored and analyzed.
Electrochemical transducers
Amperometric devices
The measurement of electric current flowing at constant potential is the principle behind
amperometric biosensors, which typically utilize electrodes coated with enzymes which enables
the analyte to undergo oxidation or reduction, resulting in a detectable current. The magnitude
of the catalysis generated current has been shown to be proportional to the substrate
concentration (Lorenzo, 1998). Although, the majority of commercial biosensor devices are
amperometric enzyme electrodes, they have not made a deeper impact on the markets where
continuous monitoring is required (Griffiths, 1993).
Each amperometric biosensor is designed for detection of only one or maybe a few molecular
species, depending on the specificity of the enzyme. The definitely most commonly used
biosensor is the single-use amperometric glucose oxidase based sensor for home glucose
assays by diabetic patients. Another common type is sensors for hydrogen peroxide detection
in flow systems. Immunoassays can also be performed with amperometric detection, where
secondary antibodies are labeled with an enzyme whose product is oxidized at the electrode
(Heller, 1996).
Historically, major problems have been concerning how to functionalize the electrode surface
for site-specific immobilization of DNA fragments (Moser, 1997). Several examples of
electrochemical sensors for detecting DNA hybridizations have nevertheless been described
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(Mikkelsen, 1996). The most common amperometric strategies for detecting the hybridization
of unlabeled DNA strands rely on redox-active hybridization indicators that bind more strongly
to DNA duplexes than to single stranded DNA, such as a minor groove binder (Hashimoto,
1994) or intercalating metal complexes of e.g. ruthenium or cobalt (Millan, 1994). Recently it
was showed by Napier et al (1997) how electron transfer could be monitored by cyclic
voltammetry for the specific detection of PCR amplified DNA with increased discrimination
between single stranded and hybridized DNA. Guanines have an enhanced reactivity compared
to the other nucleotides (Thorp, 1998) and the electron transfer is originating from oxidation
of guanines, catalyzed by a redox-active metal complex, such as ruthenium bipyridine. An
oligonucleotide probe with all guanines substituted for inosines is immobilized and let to
hybridize to an unlabeled guanine-containing target and a catalytic current is detected upon
hybridization to the immobilized probe. Despite that the introduction of inosines by definition
is leading to decreased sequence specificity, unpurified PCR amplicons of different origins and
lengths could be specifically detected.
Potentiometric devices
Another closely related group of electrochemical transducers are the potentiometric devices,
where potential changes is measured at constant current (usually zero). A logarithmic
relationship exists between the potential generated at the electrode surface and the activity of
the ion of interest. This leads to a wide dynamic range (Griffiths, 1993). Potentiometric
enzyme electrodes were the first to be investigated for biosensing purposes and the first
description of a biosensor, where the bio-component was an enzyme operating in combination
with an electrochemical transducer came in 1962 (Clark). Glucose oxidase was entrapped at an
oxygen electrode and the measured oxygen concentration was proportional to the glucose
concentration. Typically, an ion-selective or gas-sensing electrode is used to monitor changes
in product or substrate concentrations within the enzyme layer by detection of the presence of
the charge of an adsorbed analyte. The range of substrates to analyze is rather limited and the
gas sensors (CO2 and NH3) are sensitive for background variations and the ion-selective
electrodes are associated with problems of selectivity.
During the last years, the development of potentiometric methods for biosensing purposes has
taken significant steps forward, not at least for analysis of nucleic acid hybridizations.
Sequence-specific detection have been reported for hybridizations between 21-mers and 42-
mers (Wang, 1996). Another recent example of the advancement is described by Wang et al
21
(1997b) where mismatch discrimination was obtained for hybridizations between 17-mers.
PNA (peptide nucleic acid, recently reviewed by Eriksson, 1996 and Corey, 1997) and DNA
probes were immobilized on carbon paste electrodes and oligonucleotides with or without a
centrally positioned mismatch were let to hybridize. A cobalt complex bound to the duplex was
used as a redox-active indicator for presence detection. The PNA probe was shown to give a
significantly higher degree of discrimination under the chosen conditions, but with a five times
higher detection limit, which was claimed to be 0.2 µM for the complementary 17-mer and
even higher for a 30-mer.
A light-addressable potentiometric sensor (LAPS) can detect changes in pH at a silicon chip
surface and with a rather complex set-up, PCR amplicons (Olson, 1991), plasmid fragments
and cDNA (Dill, 1997) have been specifically detected. Probes labeled with either biotin or
fluorescein are mixed and let to hybridize to the target, and subsequently, streptavidin is added.
The formed complex is captured on a biotin coated nitrocellulose membrane and an
urease/anti-fluorescein antibody conjugate is thereafter bound. To create an assay
microvolume, the membrane is pressed against a silicon chip in the presence of urea. The
bound conjugate catalyzes the production of ammonia and carbon dioxide, which leads to a
detectable change in pH. The signal is displayed in µV/s and is said to be proportional to the
amount of analyte, i.e. the nucleic acid target. However, the complex set-up includes several
binding reactions that have to be fully efficient in order to fulfil that criterion.
Conductimetric devices
Conductimetric detection principles have also been used to some extent for biosensor
applications. The solution conductivity is changed when an enzyme reaction generates a net
change in the concentration of some ionized species. Recently, a biosensor that uses a mimic of
biological sensory functions i.e. ion-channel switches (ICS), have been described (Cornell,
1997) as very flexible and sensitive and suitable for a wide range of applications. The sensor is
essentially an impedance element and is based on that the conductance of a population of
molecular ion channels in a lipid membrane is switched by the recognition event.
Mechanical transducers
Piezoelectric devices
22
When an electric field is applied across a so-called piezoelectric material, such as quartz
crystal, it induces a mechanical stress in the material and creates an oscillating motion of a
certain vibrational resonant frequency. The frequency is depending on the mass on the surface
of the oscillator and decreases upon increased mass on the surface. The piezoelectric effect can
be utilized for analysis of a wide range of mass measurements, including biological recognition
events. Changes of less than 1 ng/cm2 can be detected (Ward, 1990). The mass sensing format
is commonly referred to as quartz crystal microbalance (QCM), alternative electrochemical
coupling results in other piezoelectric vibrational modes, such as a surface acoustic wave
(SAW). This format is also called piezoacoustic, where also the amplitude of the mechanical
wave is analyzed for the dependency of the mass changes at the surface. Such piezoelectric
devices have earlier mainly been used for measurements of mass changes in the vapor phase,
but both QCM and SAW have also been applied to analysis in liquids, with e.g. enzymes or
antibodies immobilized as recognition element (Minunni, 1994; Storri, 1998)
Despite the attractive label-free mass sensitive detection principle, experiments involving
detection of nucleic acids have been shown relatively little attendance during the many years of
development of piezoelectric biosensors. The relation between the mass and frequency was
described already in 1959 (Sauerbrey) and hybridization sensors in general, were actually first
discussed in combination with a piezoelectric transducer (Fawcett, 1988). Progress have
nevertheless been obtained in the last few years and some reports on detection of specific
nucleic acid sequences have been published (Ito, 1996; Nicolini, 1997), both involving DNA
fragments of around 4 kb. Su et al (1995) have described attempts of kinetic determinations
for hybridization between 4 kb fragments, where the classical Sauerbrey expression of the
relation between frequency and mass however had to be correlated after measurements of
incorporated radioactivity.
Recently, substantial progress in applications for the analysis of DNA hybridization has been
described. Time resolved kinetic measurements of hybridization between oligonucleotides with
a QCM, with a high frequency device for increased sensitivity, have been performed by
Okahata et al (1998). The immobilization was performed using the avidin-biotin system.
Through calibration of the QCM, the negative effects of interfacial liquid properties (i.e.
density, viscosity, electrode morphology etc) could be avoided. However, for longer DNA
fragments (>100 nt) it was not possible to obtain a linear correlation between the accumulated
mass and frequency. Interestingly, mismatch discrimination was obtained for hybridizations of
10-mer and 20-mer pairs, respectively, involving either a perfect match or one centrally
23
positioned mismatch. The association- and dissociation rate constants could be determined and
the effect on hybridization of spacer length, ionic strength and temperature was also
investigated.
A self-assembling monolayer of thiol-derivatized PNA on a gold plated QCM was the key
component in experiments described by Wang et al (1997a). Upon addition of a
complementary DNA oligonucleotide to the immobilized PNA (both 15-mers), the frequency
decreased, but remained unchanged when a 15-mer with a centrally positioned mismatch was
added at five times higher concentration. The detection limit for the complementary
oligonucleotide was 1 µg/ml, corresponding approximately to 0.2 µM for a 15-mer.
Thermal transducers
Calorimetric devices
Calorimetric biosensors, such as the enzyme thermistor (Danielsson, 1991), utilize that the
conversion of substrate to product generally is a more or less an exothermic process. The
enzyme is immobilized on a thermostatted column and what is actually monitored is the
temperature dependent resistance of the column. The biologically generated temperature
increase is proportional to the substrate concentration and the sensitivity is in the 10-50 moC
range, which have been shown to correspond to substrate concentrations in the lower µM
range (Danielsson, 1991). Assays have so far included detection of a wide variety of
compounds such as glucose, urea, ethanol, penicillin and sucrose.
A calorimetric device, which not can be regarded as a biosensor, but can be used for the
analysis of binding affinities between biological molecules, without the need to modify or have
one interacting molecule specie immobilized is the isothermal titration calorimetry (ITC)
device. The ITC is regarded as one of the most accurate methods for determining binding
affinities (Doyle, 1997). Since the binding enthalpy change is measured, i.e. the absorbed or
released heat during a binding reaction, the thermodynamic characteristics can also be
revealed. Analysis described involving nucleic acids have mainly been with investigation of the
action of DNA binding proteins (see e.g. Lundbäck, 1998; Plum, 1995). However, ITC have
recently been applied for thermodynamic analysis of DNA/DNA, PNA/DNA and PNA/PNA
decamer hybridizations (Ratilainen, 1998). Differential scanning calorimetry is a methodology
related to ITC and Breslauer and coworkers reported in 1986 how this method was used to
predict DNA duplex stability from the base sequence. This work resulted in an algorithm for
24
prediction of melting temperature for oligonucleotide duplexes, the nearest-neighbor method,
which is now widely used.
Optical transducers
Evanescent wave based devices
The reflectance of light at a surface is altered by the presence of surface bound analytes. The
common principle for optical biosensors is how the light is behaving at boundaries between
media of different refractive indices. Fundamental properties, such as intensity, phase and
angle, of the reflected light is measured directly and used to calculate the mass of analyte
molecules at the solid/liquid interface. The refractive index at the interface is changed in
proportion to mass changes at the surface, i.e. upon binding of molecules. In order to clarify
the relations between an evanescent wave, changes in refractive index and the measured signal,
a summary will follow of the techniques used in the commercially available optical biosensors
for real-time monitoring of label-free biomolecular interactions.
Surface plasmon resonance
The existence of surface plasmons had been anticipated for a long time before they were first
experimentally described in 1959 (Turbadar). Surface plasmons are charge density waves,
caused by collective excitation of free oscillating electrons. These occur at and propagates
along the interface between a thin layer of metal and a dielectricum, which in this context is an
aqueous solution (Liedberg, 1993). Surface plasmons can not be directly excited by light,
instead is a so-called evanescent wave used for indirect excitation (Lundström, 1994).
When the incident angle of a light beam propagating through an interface between higher and
lower refractive indices, exceeds a specific critical angle, total internal reflection (TIR) will
occur. In 1971 it was described how to excite plasmons in metal films under attenuated total
reflection (ATR) conditions, by directing the incoming light through a glass prism with direct
contact to a glass slide onto which the metal film is attached (Kretschmann, 1971). At total
reflection there is still a small portion of the light not being reflected, and this part of the light
constitutes the evanescent wave; an electromagnetic field that passes from the interface into
the lower refractive index medium. The evanescent wave interacts with the electrons in the
metal film and sets up a surface plasmon.
25
When the energy and momentum of the evanescent wave coincide with the surface plasmon
charge density wave, the phenomenon of surface plasmon resonance (SPR) can be observed as
a sharp dip in the intensity of the reflected light at a specific angle, the resonance angle. The
dip corresponds to a loss in energy in the reflected light, which is created by the transfer of the
photon energy to the charge density wave. The light energy is converted to heat. SPR occurs
in so-called free-electron metals where the electrons exhibit a gas-like behaviour, such as in
aluminium, copper, silver and gold. Another requirement is that the thickness of the thin metal
film is only a fraction of the wavelength, which should be monochromatic and in the visible
region. For a thorough review on the theory and physical properties of surface plasmons see
(Welford, 1991).
The evanescent electric field outside the metal decays exponentially with the perpendicular
distance from the surface and a typical penetration depth for the evanescent wave is 100-200
nm (Garland, 1996), it is however directly depending on the wavelength of the incident light.
Changes of the optical properties in the evanescent field will alter the resonance angle, with a
larger influence the closer to the surface the changes occur. The relation between changes in
optical properties and resonance angle is the basis for the use of SPR for biosensing purposes
and real-time biomolecular interaction analysis. Molecules that bind to the surface alter the
refractive index in proportion to the accumulated mass and the SPR angle is correspondingly
changed according to the mass of the bound molecules. Refractive indices measured for
specific wavelengths are convenient indications of the dielectric constants, which is the actual
physical parameter that influences the shift in the resonance angle.
In the BIACORE instruments (Biacore AB, Uppsala, Sweden) (Jönsson, 1991; 1992) the
resonance angle is called a resonance signal and expressed in resonance units (RU), since the
measured quantity is the interpolated position of the SPR-minimum and not the resonance
angle itself (Lundström, 1994). A linear correlation between resonance angle shift and surface
concentration has been demonstrated (Stenberg, 1991), with measurements of radioactively
labeled molecules and it was found that 1 RU approximately corresponds to a mass change of
1 pg/mm2, and an angle shift of 0.1 m° (millidegree). The detection limit is depending on the
stability of the biomolecular system, but is approximately 10 RU and since the detected area is
0.2 mm2 this is corresponding to 50 pg (Jönsson, 1991).
26
Figure 4. The principles of surface plasmon resonance (SPR). The evanescent wave causes the phenomenon ofsurface plasmon resonance. This is observed as minima in the intensity of the reflected light and the angle ofthis dip in energy, the resonance angle, is depending on the refractive index and the mass in the close vicinityof the sensor chip. The resonance angle is changed upon molecular binding and the shift in angle is convertedin a sensorgram to a plot of the shift in resonance signal versus time.
The first use of surface plasmon resonance for biosensing purposes was demonstrated in 1983
(Liedberg), where immunoglobulins were spontaneously adsorbed to a silver surface and the
subsequent binding of a second antibody was detected. SPR had earlier been used to
characterize organic molecular monolayers in gas phase (Pockrand, 1978).
Since the evanescent field is extended from the metal surface, a hydrogel matrix can be used
for biospecific interactions with one of the interacting molecule species covalently bound to the
matrix instead of direct adsorption to the metal surface. By introducing a dextran layer on the
gold surface (Löfås, 1990), a hydrophilic biocompatible surface and pseudohomogeneous
(semi-liquid) conditions can be achieved. Despite the extension out to the weaker evanescent
field, the sensitivity is retained and even increased due to the possibilities for higher amounts of
immobilized molecules in the evanescent field. An immobilization level corresponding to 1.5
monolayers in a matrix with a thickness of 100 nm have been shown to result in approximately
the same change in resonance angle as a monolayer adsorbed directly on the surface (Löfås,
Lightsource
Prism
Resonanceangle
Detectionunit
Sensorchip
Flowcell
I
II Resonancesignal
II
I Time
ReflectedIntensity
AngleI II
Sensorgram
Glass prism
Metal film
Evanescent wave
Incoming light Reflected light
27
1991). The first in the family of BIACORE instruments was introduced to the market in 1990
for real-time monitoring of biomolecular interaction analysis, where the acronym BIA has
become synonymous to the technology in general.
Figure 5. The sensor chip and the integrated micro-fluidics cartridge (IFC). The thin gold film is attached ontoa glass support, which is in contact with the prism. The hydrogel dextran matrix is immobilized via a linkerlayer. Four flowcells are created when the chip is docked on top of the IFC and the flow can then be directedwith pneumatic valves.
Besides the SPR based optical detection system, there are two important constituents of the
instrument, the integrated micro-fluidics cartridge (IFC) and the sensor chip. The IFC controls
delivery of buffers and samples, together with an autosampler, to the sensor chip surfaces and
channels are opened and closed through pneumatic microvalves (Sjölander, 1991). The sensor
chip consists of a glass support coated with a 50 nm gold film onto which the biocompatible
and flexible dextran layer is attached. The IFC is designed in such a way that when the sensor
chip is docked onto the IFC, four separate flowcells or reaction chambers are created.
Injections can be performed in series, with consecutive flow over all four flowcells, enabling
exact comparisons between the interaction of the injected analyte and different immobilized
ligands.
Another recently introduced SPR based instrument is IBIS (Instrument for Biomolecular
Interaction Sensing) (Windsor Scientific Ltd., Berkshire, UK / Intersens Instruments,
Amersfoort, The Netherlands). Consequently, the available amount of information regarding
the experimental performance of the instrument is very limited. The system is equipped with an
autosampler for injections and the biomolecular interactions occur either in a cuvette or in a
flow through system. They actually provide a one-channel adapter for BIACORE sensor chips.
Flow cellSensor chip
Valve
IFC
IFCD e x t r a n
G o ld f ilm
G la s s
Sensor chip
28
The quotation “Use the IBIS disks for simple routine assays and the more expensive
BIACORE sensor chips for publication material” follows the line of a low cost instrument,
which it is claimed to be. The IBIS instrument is displaying the response signal directly as m°.
Figure 6. Schematic representations of two waveguiding devices, a resonant mirror and a grating coupler. Ashift in the phase of the reflected light corresponds to a change in the refractive index in the evanescent field.
Optical waveguiding
Resonant mirror (RM) devices (Cush, 1993) are not depending on surface plasmon resonance,
but still utilize an evanescent wave to detect changes in the refractive index profile across a
solid-liquid interface. The sensing surface in this case is a dielectric resonant layer of high
refractive index, such as titania oxides or silicon nitrides. An incident beam of light is coupled
to the device by a prism. At certain angles of the incident light, where the phase is matching the
resonant mode of the high refractive index layer, the resonant point, light couples into the high
index layer, where it undergoes multiple total internal reflections and propagates along the
sensing interface before coupling back into the prism. This phenomenon is known as
Evanescentwave
Sample liquid
Incidentlight
Reflected light
Prism
Low indexcoupling layer
High indexresonant layer
Hydrogellayer
Resonant mirror
Grating coupler
Waveguidingfilm
Evanescentwave
Incidentlight
Reflectedlight
Grating
Sampleliquid
Glass slide
29
waveguiding. The angle of excitation of resonance is very sensitive to changes in refractive
index at the sensing interface. When the resonance angle is changed, a phase shift in the
reflected light can be detected as a peak in reflected light, instead as a dip in SPR, and the basic
principle behind the resonant mirror technique is the dependency of the phase shift on the
refractive index in the sensing layer (Hutchinson, 1995). A resonant mirror based instrument
was launched in 1993, the IAsys (Affinity Sensors, Cambridge, UK) (Cush, 1993). It works
with an open stirred and dextran coated cuvette system and has later been equipped with an
autosampler for a more automated operational mode.
The grating coupling instruments (Tiefenthaler, 1992) is based on a variation of the optical
evanescence technique, where a diffraction grating is used to couple the evanescent wave
instead of the low refractive index layer in the resonant mirror devices. Both do have a high
refractive index layer, as a waveguiding film (Ramsden, 1997). The IOS instrument (Integrated
optical sensor) (Artificial Sensing Instruments (ASI AG), Zurich, Switzerland), also launched
in 1993, constitutes of a more manual and also more modular system. The small-company
produced IOS device is hardly present at all on the list of published research reports based on
the different instruments, while there are Swiss and German academic groups working with
their own variants of waveguiding grating coupler systems utilizing modules from ASI
(Lukosz, 1995; Polzius, 1997).
Other optical devices
Devices based on total internal reflection fluorescence (TIRF) measure the binding of a
fluorescence-labeled ligand to its partner at the surface, which is recognized by the
fluorescence excited by the evanescent wave close to the surface. Non-specific adsorption of
fluorescence labeled molecules to the surface is the major practical limitation. Optical fibers
have relatively frequently been used as a solid support for TIRF analysis for sequence specific
detection of nucleic acids and even for direct synthesis of oligonucleotides on the fiber
(Piunno, 1995). Detection of single base mismatches in oligonucleotide targets have been
shown by (Kleinjung, 1997). A wave guiding alternative with a selenium-antibiotin conjugate
as a source of light scattering have also been demonstrated in a small chip format, for the same
purpose (Stimpson, 1995). An attempt to detect a point mutation in a 109-bp PCR amplicon
has also been reported (Healey, 1997), where two different oligonucleotides were immobilized
on optical fibers. In order to be able to discriminate between hybridization upon a 10-mer with
a mismatch and a perfect matched 11-mer, the differences in melting temperature between the
30
oligonucleotides had to be utilized by using a temperature just below the melting temperature
of the 11-mer. The PCR amplicon was biotinylated and detected by addition of a streptavidin-
fluorophor conjugate.
Imaging ellipsometry for visualization of biomolecular interactions, such as detection of
antibody-antigen complexes, is based on an optical biosensor device with a CCD camera for
analysis of surfaces. Ellipsometry is based on the change of polarization of light due to the
reflection from a surface. The change depends on the optical and microstructural properties of
the surface, which means for biosensing purposes the thickness of an adsorbed layer (Jin,
1995). The time resolution of an ellipsometer is relatively low, 1-10 s, (Ramsden, 1997)
compared to the millisecond range for the commercially available evanescent wave based
biosensors. Ellipsometry was the first method introduced to quantitatively investigate thin
layers at solid/liquid interfaces and it is mainly a surface characterizing technique, which can be
applied to all reflecting surfaces.
Flow cytometry is a method for measuring the fluorescence or light scatter of particles (Nolan,
1998). The analysis of molecular interactions can be made in real-time with subsecond kinetic
resolution, due to the possibility to discriminate between free and particle bound fluorescent
molecules. Fluorescent dyes associated with the particle are excited when sample flow passes
through a laser beam and the emitted fluorescence is detected. The particles have historically
mainly been cells for the analysis of ligand-receptor interactions on the cell surface. Recently,
also molecules have been immobilized on the surface of uniform microspheres and the second
molecule is fluorescently labeled and the interaction is measured as a change in the particle
fluorescence. Flow cytometry is also suitable for analysis of multimolecular complexes, with
different fluorophores on each interactant. Apart from kinetic studies of a wide range of
protein-protein interactions, DNA cleavage by endonuclease (Nolan, 1996) and the activity of
DNA ligase (Cai, 1997) have been measured in real-time.
Fluorescence correlation spectroscopy (FCS) is an interestingly method that have been applied
to kinetic analysis at single molecule level of an oligonucleotide hybridizing to a 7 kb target in
an extremely small volume element of 0.2 fl (Kinjo, 1995). FCS have also recently been applied
for single molecule detection of PCR products (Björling, 1998) and analysis of DNA
endonuclease activity (Kinjo, 1998).
31
RESULTS AND DISCUSSION
INTRODUCTION
The commercially available optical biosensors with capacity for real-time monitoring of
biomolecular interactions for determination of e.g. kinetic binding data (association and
dissociation rate constants) are now really established in many research areas. The two main
suppliers, Affinity Sensors and Biacore, have collectively more than 1100 articles in which
their instruments have been used, but almost 90% of those are based on the latter. In general,
the vast majority of analyses that have been performed can be categorized into the broad field
of protein-protein interactions. For an overview of applications, see e.g. Hutchinson, 1995;
Szabo, 1995; Malmqvist, 1997; Panayotou, 1998 and references therein. Nucleic acid analysis
have also been performed, although not at all to the same extent, employing nucleic acids
either as immobilized ligands for investigation of the action of DNA binding proteins or for the
analysis of interactions between nucleic acids.
The immobilization of nucleic acid templates on a sensor surface has been a major concern
during the years of research and development of nucleic acid based biosensors. Adsorption was
for long time the only alternative for immobilizing nucleic acids on the electrodes used as
sensor surfaces in electrochemical and piezoacoustic biosensor devices. It was a relatively
simple procedure with no requirements of surface or ligand modifications, but the random
immobilization led to low efficiencies in subsequent hybridizations. In addition, a wide range of
chemical modifications, via linkers introduced at the oligonucleotide and an adhesive agent on
the surface, have been used for site-directed covalent coupling (Yang, 1997). In 1990
(Ebersole) it was shown how an active monolayer of avidin could form on metal surfaces. The
streptavidin-biotin system is now a widely used procedure for the site-directed immobilization
of nucleic acids on a solid support, utilizing one of the strongest known non-covalent
biological interactions, KD ~10-15 M (Wilchek, 1988). The introduction of a flexible and
biocompatible dextran matrix (Löfås, 1990) in which streptavidin can be covalently bound,
have certainly increased the efficiency of nucleic acid immobilization. Watts et al (1995) have
compared different methods for immobilization of oligonucleotides on a sensor surface.
Adsorption and aminolinkage required almost 20 times higher concentrations to yield
maximum responses compared to the use of biotin-streptavidin capture in a dextran layer, but
the maximum response was still four times higher for the latter.
32
The possibilities for convenient and efficient immobilization of biotinylated nucleic acids
together with the mass sensitive detection system offered by the BIACORE instruments,
demonstrates an appealing technology for biomolecular interaction analysis. The herein
described experiments were initialized in order to investigate how far this surface plasmon
resonance based biosensor system could reach into the relatively untouched area of molecular
biology applications.
REAL TIME MONITORING OF DNA MANIPULATING ENZYMES (I)
To investigate if basal unit operations in molecular biology could be analyzed with optical
biosensor technology, a model system was designed, consisting of six oligonucleotides. They
could be assembled into a 69-bp double stranded DNA fragment and subsequently utilized as a
target for endonuclease cleavage and after strand separation, as a template for DNA
polymerases.
DNA assembly using DNA ligase
One oligonucleotide was biotinylated in the 5'-end for fast and efficient immobilization onto a
sensor chip where the dextran layer was coated with streptavidin. A double stranded fragment
with a 3-nt protrusion was achieved by letting a complementary oligonucleotide hybridize.
Two consecutive ligation steps with prehybridized oligonucleotides containing 3-nt protrusions
completed the assembly. The efficiencies in those non-optimized hybridization and ligation
steps were each calculated to approximately 64 % of the stoichiometric maximum. Control
injections without ligase or with non-complementary protrusions did not result in any
accumulated mass on the surface. Furthermore, the response curves for injection with ligase
and DNA fragment were not identical for the different ligation steps. A bi-phasic response
curve was observed for events where both strands were ligated, which was not observed when
only one strand was involved in the formation of a phosphodiester bond.
DNA assembly can be an alternative way of creating a desired DNA fragment with a length
longer than what is optimal for an ordinary DNA synthesizer. The possibility to monitor such
DNA assemblies in a step by step manner leads to the advantage of known efficiencies in each
step of the reaction. Such an assembly usually involve several reaction steps and there are often
no possibilities to evaluate the outcome until the process is finished and the end product is
analyzed, by electrophoresis or other means. The concept used here demonstrates not only the
33
opportunity to optimize reaction conditions, regarding buffer, temperature, ionic strength etc,
but also possibilities for basic research regarding the activity of DNA ligase. Besides being an
analytical tool, the methodology can also be used preparatively. Parts of the assembled DNA
fragment can either be eluted with cleavage by an endonuclease at a designed cleavage site.
Alternatively, the non-biotinylated strand could be eluted by chemical denaturation, and used
as template in subsequent PCR amplification to increase yields.
Endonuclease cleavage
The elution of the assembled fragment by endonuclease cleavage was also demonstrated, not
for preparative purposes but to evaluate if an endonuclease activity could be monitored. In
contrast to later released versions of the instrument, the model used here did not support
automatic recovery of eluted samples. The 69-bp DNA fragment contained the recognition
sequence for the endonuclease Xho I and injection of the restriction enzyme resulted in a clear
decrease of mass on the surface. The recognition site was positioned in such a way that
cleavage would leave a 16/20 nt long fragment on the chip. The net decrease obtained by
comparison of response levels before and after injection indicated a cleavage efficiency of 93%.
The real-time monitored response curve for the reaction is relatively complex to interpret,
since it represents the sum of three simultaneously occurring processes; enzyme binding,
enzyme dissociation and the release of DNA by the cleavage reaction. Nevertheless, the results
demonstrate the possibilities of kinetic analysis of the action of DNA endonucleases.
DNA synthesis by DNA polymerases
A third class of enzyme, which is very common in many types of molecular biology
applications, is DNA polymerases. Using the model system, the activities of T7 DNA
polymerase (T7) and the Klenow fragment of DNA polymerase I (Klenow) were investigated.
The biotinylated strand of an assembled 69 bp fragment served as a template and an annealed
primer was extended towards the biotin. Differences in the behaviour between the two
polymerases were evident just by a visual comparison of the obtained response curves. In
experiments using T7 a continuous increase in the response was seen during the whole
injection. In contrast, Klenow displayed a fast and narrow peak during the first part of the
injection and then reached a plateau value. Furthermore, the response levels after the injections
were twice as high for T7 compared to Klenow. Interestingly, after a short pulse of SDS for
34
removal of eventually accumulated enzyme on the DNA, the increases in response
corresponding to the DNA synthesis were almost identical. Interpretation of the results
suggests that T7 remains bound to the DNA fragment even after the extension is completed,
while the Klenow "jumps off" after the synthesis is finished. In other words, T7 display affinity
not only for partly double stranded DNA fragment (primer + template) but also for double
stranded DNA, which the Klenow enzyme does not. This simple assay should be useful also for
the characterization of other polymerases. Buckle and coworkers (1996) have also performed
real-time measurements of polymerase dependent elongation using a reverse transcriptase,
including quantitative analysis of the polymerization process.
Taken together, the work showed upon possibilities of using biosensor technology for
quantitative and qualitative analysis in real-time for the characterization and monitoring of the
action of several of the most commonly used DNA manipulating enzymes. Later, several other
reports of biosensor facilitated investigations of interactions involving such enzymes have been
reported. They include the kinetic and stoichiometric analysis of mutant variants of the E. coli
RNase HI binding to pre-hybridized and thereafter immobilized RNA-DNA hybrids of lengths
up to 36 bp. Also comparisons with the reverse set-up was performed, with the duplex injected
as analyte (Haruki, 1997). Another recent example of analysis of DNA manipulating enzymes
is the investigation of the mechanism of substrate recognition for inactive mutant variants of
the DNA repair enzyme uracil-DNA glycosylases described by Panayotou (1998). The IBIS
instrument has been used to characterize different mutant variants of the DNA unwinding
adenovirus single-stranded DNA binding protein by affinity determinations of the binding upon
an immobilized 41-mer oligonucleotide (Dekker, 1998).
MISMATCH DISCRIMINATION IN OLIGONUCLEOTIDES (I, II)
Minisequencing (I)
The results from the extension experiments described above implied the possibilities to develop
a strategy to employ the resulting SPR signal for a qualitative analysis of the template DNA
strand. Therefore, a minisequencing protocol based on biosensor analysis was designed and
investigated. Immobilized single stranded templates were generated by assembly and
subsequent strand separation, followed by primer annealing. DNA polymerase assisted
incorporation of one of the four dideoxynucleotides at the position adjacent to the primer in a
first step would prevent any further extension in a subsequent step using all four
35
deoxynucleotides. The identity of the base adjacent to the primer would then be revealed by
the absence of a signal related to the extension in the second step. Each experimental series
consisted of consecutive injections with i) alkali for strand separation, ii) primer annealing, iii)
polymerase together with one defined dideoxynucleotide, iv) SDS for removal of polymerase,
v) polymerase together with all four deoxynucleotides, vi) SDS. The response after step vi)
was compared for the four series with different chain-terminators. Thus, three high signals
were expected, corresponding to non-prevented extension and a fourth low signal,
corresponding to an incorporation of a dideoxynucleotide. The results showed, in principal,
that the technique worked, but to increase performance an alternative could be to utilize a four
flowcell system and have the template immobilized on all four surfaces and perform all
injections, except the one containing dideoxynucleotides, in a serial mode over all flowcells.
This would save time but increase the chip consumption. Another alternative for serial
injections would be to use four different primers for the analysis of four different mutational
hot spots.
An interesting feature of the minisequencing results can be added to the discussion regarding
the differences in DNA binding displayed by Klenow and T7 (see DNA polymerases above).
Klenow DNA polymerase was used in the minisequencing protocol and in the three cases of
extension, all obtained curves displayed a characteristic “Klenow extension shape” as observed
earlier. However, in the case with dideoxy-terminated extension a gradual increase was
observed during the injection. This further supports the theory that Klenow only show affinity
to partly double stranded templates, leading to an accumulation with time. The appearance of
this atypical curve also strengthens the discriminatory power of the minisequencing
methodology, by providing a second indication of which dideoxynucleotide that has been
incorporated. On the negative side of features displayed by Klenow is the 3'-5' exonuclease
activity, which could be a reason for the background extension signal that was observed. The
level of the background signal was 37% of the average net response observed for the other
three cases. The results suggest that the polymerase to use should be chosen with care.
Hybridization analysis by determination of equilibrium affinities (II)
In order to investigate the hybridizational behaviour of short oligonucleotides, a second
oligonucleotide based model system was designed. The rapid dissociation of a hybridized short
oligonucleotide from the template enables affinity determinations from a monitoring of steady-
state responses at equilibrium and it also circumvents the need for regeneration between
36
sample cycles. Affinity data are easily obtained from the plotting of equilibrium responses
versus the concentration. An analysis of the effect of temperature and oligonucleotide length
on affinity was performed for hepta-, octa- and nonamers hybridizing onto a sensorchip-
immobilized 25-mer. An approximate 10-fold increase in affinity was observed when the length
was increased from eight to nine nucleotides (in the temperature range of 20-35 °C), while the
difference between a heptamer and an octamer only were two-fold (10-35 °C).
The affinity determinations of eleven different octamers hybridizing to different positions on
the same complementary target revealed a difference in affinity of almost two orders of
magnitudes. A comparison to calculated Tm (melting temperature) values suggested that a
difference in Tm of 10 °C correspond to a 10-fold difference in affinity. Those results highlight
the fundamental difficulties encountered in early experiments designed for sequencing by
hybridization (see Introduction). It is obviously very hard just to find a single condition where
all perfectly matched hybridizations should result in stable duplexes, whereas mismatched
events should not.
Mutational scanning and influence of mismatch position (II)
The possibility to detect base substitutions in the target sequence through affinity
determinations of hybridizing oligonucleotides was also demonstrated. The sensitivity of the
strategy was shown by a comparison of the affinities between a nonamer and two different
targets, for which the oligonucleotide was either fully complementary or contained a single 5'-
end mismatch. The resulting affinity plots shows that even for an end-mismatch situation, the
discrimination factor is, expressed as difference in affinity, one order of a magnitude. After
such curves have been established, it is suitable to choose a single concentration for which the
largest differences are obtained. Thus, a subsequent discriminatory analysis can be performed
with only one concentration.
The effect of the relative localization of single mismatched bases was further analyzed using a
set of eleven octamers for scanning of three different 25-mers as targets, where two contained
a substituted nucleotide at different positions. By plotting the equilibrium responses for the
three targets a "mutational scanning profile" was obtained, which displayed how the mismatch
position dramatically influenced the responses. The effect was, as expected, more pronounced
when the mismatch was localized in an internal position. Noteworthy, a comparison of the
responses obtained for octamers hybridizing with a 3'- or 5'-end mismatch indicates that the
37
stability in this case was mostly affected by a 3'-end mismatch. This was not due to different
mispaired bases, since they were identical at both sides. The average response for the two
octamers with a mismatch in the 3'-end was only 18% of that obtained for hybridization to the
complementary target. The corresponding value for the 5'-end was 45%.
Figure 7. Overview of the different applications investigated in paper I-III, where oligonucleotide modelsystems were used.
The first description, in this context, of the monitoring or rather detection of oligonucleotide
hybridizations was submitted for publication (Wood, 1993) little more than a year after the first
launch of the instrument, demonstrating an early insight into the possibilities of molecular
biology application. More recent investigations of the influence of several different variants of
mismatches on the kinetic rate constants for oligonucleotide hybridizations have been reported
(Gotoh, 1995 and Jensen, 1997), where the latter work also included RNA and PNA
oligonucleotides. The ability for grating coupler devices to monitor and analyse DNA
hybridizations between oligonucleotides have been shown by Bier et al (1996; 1997b).
Mismatch discrimination was achieved through determination of kinetic data for 13-mers, with
B
DNApolymerase
DNA synthesis
B
ddCTP
Minisequencing
DNApolymerase
G
ddGTPddTTPddATP
DNA cleavage
B
DNAligase
Gene assembly
B
Immobilization
B
Hybridizations
B B
DNA endo-nuclease
B
Modular hybridizations
38
or without one or two centrally positioned mismatches, hybridizing upon an immobilized 24-
mer. Also the IAsys instrument has been utilized for real-time monitoring of oligonucleotide
(up to 40-mers) hybridizations. Investigations of the influence of oligonucleotide length and
the relative position of complementary sequence was performed (Watts, 1995). Furthermore,
antisense reagents have been evaluated by analysis of the binding of a triple helix forming
oligonucleotide and a DNA binding drug, separately or in combination, to an immobilized
oligonucleotide duplex (Rutigliano, 1998). Kinetic studies of oligonucleotide triplex formation
have also been described by Bates et al (1995).
Analysis of modular hybridizations (III, IV)
Increased stability by modular hybridizations (III)
Another type of hybridization analysis that has been performed was an investigation of the
stabilizing effect achieved upon co-hybridization of adjacently annealing short oligonucleotides,
the so-called modular primer effect. This effect can be utilized for the substitution of a single
longer primer or other oligonucleotides with a combination of shorter, e.g. hexamers.
Interactions between target DNA and pairwise combinations of both DNA and peptide nucleic
acid (PNA) hexamers were quantitatively analyzed for different adjacent hybridization
situations as well as overlap and one or two base gaps. The influence of concentration and
individual inherent affinities on the stabilizing effect was investigated in order to illustrate the
importance of those parameters for use in different modular hybridization applications, and
also to provide a suitable methodology with capacity for such analysis.
Again, the fast hybridization kinetics for short oligonucleotides, in this case hexamers, were
utilized for the determinations of apparent duplex affinities from equilibrium responses. Two
out of the four flowcells were utilized for the separate immobilization of two different but
closely related 25-mers, designed to result in different hybridization situations. In the third
flowcell, a mixture of two targets was immobilized, each separately comprising either of the
two annealing sites. Hence, any co-operative stabilizing was ruled out, allowing for
comparative analysis between separate and modular hybridizations.
Firstly, the modular primer effect was investigated at fixed total hexamer concentration, but
with different concentration ratios between the module pairs. Four different hexamer
sequences, where two were used both as DNA and PNA hexamers, were analyzed for seven
different combinations of pairwise injections. In order to observe co-operative effects, the
39
arithmetic sums of hybridization responses for corresponding hexamer combinations and
concentrations, previously obtained from injections of individual hexamers, were subtracted
from the responses obtained from the co-injections. Hence, any co-operative effects would
result in positive responses in the processed data. For situations of adjacent DNA hexamer
hybridizations, a clear net effect from the co-injection of modules was observed, demonstrating
an increased apparent affinity as compared to responses from separate injections of the same
modules. The inherent affinities of each hexamer had previously been determined and the data
shows that a more pronounced stabilization occurs after addition of small amounts of a higher
affinity hexamer module, as compared to the stabilization obtained after addition of small
amounts of a module with lower inherent affinity. Also for DNA hybridization formats
involving either a one-base overlap or two out of the three one-base gap situations, a small
modular stabilization effect could be observed. When DNA hexamer modules were replaced by
their PNA counterparts in different module combinations, it was found that also this nucleic
acid analogue with a different molecular backbone could contribute to a stabilization, either in
combination with a DNA module or as a PNA- PNA pair.
To further investigate the modular primer effect, a comparison was performed of apparent
combined affinities for two DNA hexamers with different inherent affinities, one injected
without or with different concentrations of the second module. Several injection series with
varied concentration of one hexamer and fixed concentration of the second hexamer
throughout each injection series, and vice versa, were performed to analyze the stabilization
dependency of module concentration. Large differences in combined apparent affinities
between hybridizations without any stabilizing module and with different degrees of adjacent
supplementation were observed. Up to an 80-fold increase in apparent combined affinity was
observed when a "low affinity" module was supplemented with a "high affinity" module and up
to a 20-fold increase was seen for the opposite combination. Also, for a hybridization situation
with a one-base gap, a small stabilizing effect could be observed. The stabilization factor was
approximately 5% of the value obtained by adjacent hybridization.
The use of oligonucleotide modules for capture (IV)
The favourable stabilization effect obtained by modular hybridizations was further utilized and
analyzed for the enhanced capture of single stranded PCR amplified DNA. The PCR amplified
target was a 324-bp fragment, originating from the nontranslated region of the hepatitis C virus
40
genome. The effects of different capturing probes on DNA hybridization, used together with
single oligonucleotides or multiple short modules prehybridized to the single-stranded target,
were investigated. The capturing probes were immobilized on the sensor chip and the PCR
fragment was rendered single stranded by streptavidin - biotin immobilization on a solid phase
followed by strand specific elution of the non-biotinylated strand. Capturing probes of 9 - 36 nt
were surprisingly not able to provide any significant capture of the single stranded DNA
fragment. However, when a prehybridizing step was introduced in which one or two
oligonucleotide modules were let to hybridize adjacently to the target sequence for the
capturing probe, a significant capture was observed. When an 18-mer capturing probe was
used together with single prehybridizing modules with lengths between 11 and 18 nt, all
combinations resulted in a high level of capture, while a prehybridizing nonamer only could
assist to capture a low amount of single stranded DNA. Interestingly, when the 18-mer capture
probe was shortened to a nonamer sequence and an extra prehybridizing nonamer (in total
two) was added, an effective capture was also obtained.
Figure 8. A cartoonlike view of the capture of single stranded DNA assisted by oligonucleotide modules.
In order to further analyze the oligonucleotide-assisted capture approach, single nucleotide
gaps were introduced between the modules and between the capture probe and the neighboring
module. All analyzed gap situations resulted in a significantly reduced capture, some abolished
the capture totally while some were not that detrimental with a 30% reduction. This gap-effect
was more pronounced for multiple modules.
Taken together, the results demonstrate that successful capture can be achieved using multiple
short modules and suggest that it is not primarily the length of the immobilized capturing probe
which is the most important parameter, but rather it depends on the number and length of
No capture Capture
27 nt9 + 9 + 9 nt
41
modules used in the prehybridization step. It can be envisioned that it would be feasible to use
presynthesized module libraries for nucleic acid capture by taking advantage of stacking
interactions between the oligonucleotides and possibly a co-operative suppression of target
secondary structure. The described biosensor technology can as mentioned earlier be used also
for preparative applications, which in this case could lead to an enrichment or purification of a
specific nucleic acid sequence. However, the use of the technology would probably mainly be
of analytic nature, to specifically optimize conditions of modular assisted capture of desired
target DNAs.
Mutation detection in clinical samples (V, VI)
Mutation detection on immobilized or injected PCR amplicons (V)
The introductory positive results on sequence-based DNA analysis with oligonucleotide based
model systems (I, II) were consequently followed up by investigations of the possibilities to
perform such analyses on clinically relevant samples, i.e. PCR amplified DNA.
Exon 6 of the human tumor suppressor p53 gene was chosen as target for the mutational
analysis using clinical samples derived from breast tumor biopsies. Two different hybridization
formats were utilized for mismatch discrimination between fully complementary sequences and
single base mismatches. The two formats, which can be recognized from the sequencing by
hybridization terminology, are format 1 with immobilized PCR products and oligonucleotides
injected for hybridizational comparison of targets and format 2, where oligonucleotides are
immobilized and single stranded PCR fragments injected. In format 1, two biotinylated PCR
products (199 bp) were immobilized, one of known wild type sequence and one with a 100%
single point mutation. After the non-biotinylated strand was chemically denatured and eluted, a
set of four different 17-mers were hybridized to the two targets. One oligonucleotide was a
positive control, which annealed with perfect match on both targets. Two of the
oligonucleotides were differing by only one base, one wild type specific and one mutant
specific. The fourth was also wild type specific, but the mismatch resulting from hybridization
to the mutant sample was localized closer to the end for this oligonucleotide. The results
demonstrated that relatively minor, but nevertheless reproducible and significant differences
could be obtained for hybridizations to the two targets. The two oligonucleotides differing by
one base resulted both in a small hybridizational advantage for their specific targets, while the
other wild type specific oligonucleotide possessed a higher discriminatory power.
42
Experiments in format 2 were initialized to obtain a methodology platform with possibilities to
screen many samples for known mutations, in contrast to format 1 which is more suitable for
the analysis of a longer sequence in few samples. The four flowcells now contained four
different oligonucleotides, a positive and a negative control and a wild type and mutant
specific. The molar capacity of the streptavidin surface was approximately eight times higher,
for the oligonucleotides compared to immobilizations of PCR products. The stoichiometry of
full-match hybridizations was on the other hand corresponding to a use of approximately 8%
of the available oligonucleotides, while in format 1 the corresponding value was approximately
50%.
The single stranded PCR products were generated with solid-phase technology as described
earlier. They were injected in series over the four flowcells and when the responses obtained
from the negative control surface was subtracted, a very clear difference could be observed
between the wild type and mutant sample. The responses from the capture by the specific
oligonucleotides of their complementary targets were gradually increasing during the whole
injection at a relatively high rate. Interestingly, the inverted combinations with a single base
mismatch resulted in no increase at all, leading to a clear mismatch discrimination where the
results in fact can be converted to the form of "1 or 0". A third sample containing a 50/50 mix
of wild type and mutant sequence was also analyzed and even in this case was the mutation
detected. A comparison of the hybridization signals from the wild type specific oligonucleotide
for the wild type sample and the mixed demonstrates a reduced hybridization response, but the
comparison has to be made also with respect to responses from the positive control surface.
Those experiments actually constituted the first published report, according to publicly
available databases, on hybridizational mismatch discrimination with PCR amplified DNA using
a label-free detection system. PCR amplified DNA has also been introduced into optical
biosensors by at least two other groups; Bianchi et al (1997) could specifically and direct
detect asymmetric PCR products amplified from HIV-1 genomic sequences and Gotoh et al
(1997a) have used the mismatch binding protein MutS with preliminary results of mismatch
discrimination between 95 bp homo- and heteroduplexes. The same PCR products were also
utilized for immobilization and hybridization with wild type specific and mutant specific 13-
mers and they obtained a weak mismatch discrimination (Gotoh, 1997b), in accordance with
the corresponding results shown here.
Mutation detection by subtractive hybridizational scanning (VI)
43
The above described methodology for mutation detection, despite the proven functionality, has
some drawbacks. The mismatch discrimination was under those conditions rather small in
format 1 and only three samples could be analyzed per chip, since one of these needs to be a
wild type reference. The limitations of format 2 lies in the relatively short region of the
sequence that can be analyzed, which although is enough for screening of mutational hot spots.
In order to overcome those limitations and to further develop the methodology, a totally new
concept was designed. In this study the mutation sensitive hybridizational scanning of PCR
product was performed outside the instrument, followed by an analytical hybridization analysis
between fully complementary oligonucleotides. The use of such subtracting hybridization on
the amplified target allows for a subsequent biosensor analysis of fast, robust and well
characterized interactions. Furthermore, the capacity in terms of number of samples and
sequence length to analyze is improved in comparison to when the PCR amplicons are
introduced in the instrument.
Sets of overlapping scanning oligonucleotides complementary to wild type sequence were
hybridized to microbead-immobilized PCR products. Mismatch hybridization situations
between a mutant sample and oligonucleotides result in higher remaining concentrations in
solution of involved oligonucleotides. Post-hybridization supernatants were subsequently
analyzed for their oligonucleotide compositions using the biosensor. Relative remaining
oligonucleotide concentrations were monitored through hybridization analysis between
scanning oligonucleotides and their corresponding sensor chip-immobilized complementary
counterparts. This allowed for the construction of composition diagrams revealing the
existence and approximate location of a mutation within an investigated sample DNA
sequence.
Again, the p53 gene was chosen as a model system and both exons 6 and 7 were scanned for
mutations. Fifteen 13-mers covering exon 6 and eleven 13-mers covering exon 7 were used for
scanning, all with six nucleotides overlap relative to flanking oligonucleotides. The scanning
oligonucleotides were divided into two non-overlapping sets for each exon to avoid
interference between oligonucleotides during hybridizations. Supernatants from each set and
sample were divided for injections onto two sensor chips. The supernatants from hybridizations
to sample and wild type reference PCR products were compared. Thus, a higher sample
derived hybridization response signal for a given oligonucleotide interaction reflects a higher
remaining oligonucleotide concentration in the supernatant, indicative of an earlier mismatch
situation due to mutation. The hybridizational responses from wild type supernatants were
44
subtracted from the responses obtained by sample supernatants. This processing of the data
enables the comparison to be performed without the need for equal PCR product
concentrations, since that will just be revealed as a baseline, i.e. the difference between
unaffected scanning oligonucleotides, with average values separated from zero. The complete
mutational scanning profiles can be regarded as a map of the exons, in which the processed
postinjection responses are plotted against the ordered identity of the scanning
oligonucleotides.
Figure 9. To increase the throughput of the method, a series of experiments were also performed withsimultaneous analysis of exon 6 and exon 7, involving the addition of two sets of scanning oligonucleotides to amixture of exon 6 and exon 7 derived PCR products and co-immobilization of two different oligonucleotidesper flowcell. A decreased sensitivity was observed, probably due to the increased complexity and the resultinglower immobilization level for each individual oligonucleotide species, although mutations were still detectableas exemplified here. The sample denoted K5L2 contains a mutation located in a sequence covered byoligonucleotides K and L.
The results presented in paper VI clearly demonstrated a reproducible detection of single point
mutations in five different clinical tumor samples. Due to the biological origin of these samples,
they were contaminated with various amounts of normal cells carrying wild type p53 alleles.
The present protocol used for subtractive hybridizational scanning is capable of detecting a
mutation in a background of approximately 50-60% wild type sequence.
CONCLUDING REMARKS
-50
-40
-30
-20
-10
0
10
20
30
40
50
60
A B C D E F G H I J K L M N O P Q R S T U V W X Y Z
Rel
ativ
e R
esp
on
se [
RU
]
Exon 6 Exon 7
K5L2
45
It has here been demonstrated how an optical biosensor, based on surface plasmon resonance
for mass sensitive detection and analysis of biomolecular interactions, can be utilized for a wide
range of molecular biology applications, with special emphasis on hybridization analysis and
mutation detection. The described biosensor system has been shown to be a suitable tool for
basic research related to investigations of kinetic properties of the hybridization event and with
capacity for discriminating between fully complementary hybridizations and hybridizations
involving a single-base mismatch. Several different methodologies for sequence-based analysis
of clinically relevant samples have here been described. However, without any knowledge of
eventual future instrument developments, it must be stated that the present instrumentation
with only four flowcells prevents the technology from high throughput analysis. The
automated, robust and sensitive system together with the convenient biotin/streptavidin
immobilization and most of all, the label-free detection principle is although an appealing
concept and it can be envisioned that the detection principle could be implemented to other
chip based system.
46
ABBREVIATIONS
ARMS amplification refractory mutation systemASA allele specific amplificationASO allele specific oligonucleotidesASPCR allele specific polymerase chain reactionATR attenuated total reflectionBIA biomolecular interaction analysisbp basepairsCA CaliforniaCCD charge coupled deviceCMC chemical mismatch cleavageDGGE denaturing gradient gel electrophoresisDOE Department of EnergyEMC enzymatic mismatch cleavageFCS fluorescence correlation spectroscopyGb billion basepairsHA heteroduplex analysisHGP Human Genome ProjectICS ion-channel switchesIFC integrated micro-fluidics cartridgeITC isothermal titration calorimetrykb thousand basepairsLAPS light addressable potentiometric sensorLCR ligase chain reactionMb million basepairsNADH nicotine adenine dinucleotideNIH National Institute of Healthnt nucleotidesOLA oligonucleotide ligation assayORF open reading frameOWLS optical waveguide lightmode spectroscopyPASA PCR amplification of specific allelesPCR polymerase chain reactionPEX primer extensionPNA peptide nucleic acidsQCM quartz crystal microbalanceRM resonant mirrorRU resonance unitsSAW surface acoustic waveSBH sequencing by hybridizationSDS sodium dodecyl sulphateSPR surface plasmon resonanceSSCP single strand conformation polymorphismTIR total internal reflectionTIRF total internal reflection fluorescence
47
ACKNOWLEDGEMENTS
I would like to express the most sincere thanks to all people that are working or have workedduring those years, in the Dept. of Biotechnology at KTH - Royal Institute of Technology andespecially in the fantastic and unique DNAcorner®. The people and atmosphere and also theintense activities in this place was the major component in my first thoughts of starting to workfor a PhD.
I would like to resemble the lab with a flock of sheep, where the chief shepherd is alwaysrunning around with a neverending enthusiasm and always with a happy tone in the horn,keeping an eye on the flock and constantly seeking for new ways of providing us occupied inmeans of bringing us to new green grazing lands. The herd is constantly growing, even if theland is not growing at the same speed, and all sheep were divided among the introducedsheepdogs, which take very good care of their groups, despite their burden of amount of work.The herd has an excellent mixture of individuals: the ones that try to keep the place tidy andorganized and looking after the black sheep of the herd; the ones that almost always have asmile in the face, even at tough situations; the ones that take their responsibilities seriously; theones that keep or bring things to work; the ones that always can give and take a joke; the onesthat always have time for a chat; the ones that always are willing to help or does it anyway; theones that always are willing to share their knowledge and experience; the ones that enjoy andorganize social activities, such as parties and beerdrinking; the ones just being good friends andcolleagues etc etc.I hope that all of those that are recognized in the above, know that they are sincerelyappreciated.
Again, I would like to thank:Mathias Uhlén, for accepting me as a PhD student and for being a very good head of thegroup. Per-Åke NygrenGGMMDD, for by all means being a very good supervisor and for letting meslide away from the protein engineering field, for critical reading of this thesis, for being a goodconference companion, etc. Joakim Lundeberg, for scientific discussions and advice, forreading of this thesis, for being a good conference companion, etc.
I also would like to thank the people at Biacore AB for good collaborations, especially BjörnPersson and Anita Larsson.
Co-authors not already mentioned are of course also acknowledged.
I also wish to express my deepest gratitude to my mother and father for all support and for thehuge amount of time spent with taking care of the girls.
Malin & Matilda, for just being there and bringing joy.
Eva, for love, endless support and understanding.
This work was supported by The Swedish Natural Science Research Council(Naturvetenskapliga forskningsrådet, NFR) and in part by Pharmacia Biosensor AB (theformer name of Biacore AB).
48
REFERENCES
Avery, O. T., MacLeod, C. M. and McCarty, M. (1944) Studies on the chemical nature of the substanceinducing transformation of pneumococcal types. Induction of transformation by a deoxyribonucleicacid fraction from Pneumococcus Type III. J Exp Med 79:137-158.
Barany, F. (1991) Genetic disease detection and DNA amplification using cloned thermostable ligase. ProcNatl Acad Sci USA 88:189-193.
Bates, P. J., Dosanjh, H. S., Kumar, S., Jenkins, T. C., Laughton, C. A. and Neidle, S. (1995) Detection andkinetic studies of triplex formation by oligodeoxynucleotides using real-time biomolecularinteraction analysis (BIA). Nucleic Acid Res 23:3627-3632.
Beck, S. and Sterk, P. (1998) Genome-scale DNA sequencing: where are we? Curr Opin Biotechnol 9:116-121.
Bellanne-Chantelot, C., Beaufils, S., Hourdel, V., Lesage, S., Morel, V., Dessinais, N., Le Gall, I., Cohen, D.and Dausset, J. (1997) Search for DNA sequence variations using a MutS-based technology. MutatRes 382:35-43.
Bianchi, N., Rutigliano, C., Tomassetti, M., Feriotto, G., Zorzato, F. and Gambari, R. (1997) Biosensortechnology and surface plasmon resonance for real-time detection of HIV-1 genomic sequencesamplified by polymerase chain reaction. Clin Diagn Virol 8:199-208.
Bier, F. F. and Scheller, F. W. (1996) Label-free observation of DNA-hybridisation and endonuclease activityon a wave guide surface using a grating coupler. Biosens Bioelectron 11:669-674.
Bier, F. F. and Fürste, J. P. (1997a) Nucleic acid based sensors. EXS 80:97-120.
Bier, F. F., Kleinjung, F. and Scheller, F. W. (1997b) Real-time measurement of nucleic-acid hybridizationusing evanescent-wave sensors: steps towards the genosensor. Sens Actuat B 38:78-82.
Björling, S., Kinjo, M., Földes-Papp, Z., Hagman, E., Thyberg, P. and Rigler, R. (1998) FluorescenceCorrelation Spectroscopy of Enzymatic DNA Polymerization. Biochemistry 37:12971-12978.
Breslauer, K. J., Frank, R., Blöcker, H. and Marky, L. A. (1986) Predicting DNA duplex stability from the basesequence. Proc Natl Acad Sci USA 83:3746-3750.
Buckle, M., Williams, R. M., Negroni, M. and Buc, H. (1996) Real time measurements of elongation by areverse transcriptase using surface plasmon resonance. Proc Natl Acad Sci USA 93:889-894.
Cai, H., Kommander, K., White, P. S. and Nolan, J. P. (1998) Flow cytometry-based hybridization andpolymorphism detection and analysis. Proc SPIE 3256:171-177.
Chee, M., Yang, R., Hubbell, E., Berno, A., Huang, X. C., Stern, D., Winkler, J., Lockhart, D. J., Morris, M. S.and Fodor, S. P. (1996) Accessing genetic information with high-density DNA arrays. Science274:610-614.
Cho, R. J., Fromont-Racine, M., Wodicka, L., Feierbach, B., Stearns, T., Legrain, P., Lockhart, D. J. andDavis, R. W. (1998a) Parallel analysis of genetic selections using whole genome oligonucleotidearrays. Proc Natl Acad Sci USA 95:3752-3757.
Cho, R. J., Campbell, M. J., Winzeler, E. A., Steinmetz, L., Conway, A., Wodicka, L., Wolfsberg, T. G.,Gabrielian, A. E., Landsman, D., Lockhart, D. J. and Davis, R. W. (1998b) A genome-widetranscriptional analysis of the mitotic cell cycle. Mol Cell 2:65-73.
Clark, L. C. and Lyons, C. (1962) Electrode system for continuous monitoring in cardiovascular surgery. AnnNY Acad Sci 102:29-45.
49
Corey, D. R. (1997) Peptide nucleic acids: expanding the scope of nucleic acid recognition. Trends Biotechnol15:224-229.
Cornell, B. A., Braach-Maksvytis, V. L., King, L. G., Osman, P. D., Raguse, B., Wieczorek, L. and Pace, R. J.(1997) A biosensor that uses ion-channel switches. Nature 387:580-583.
Cotton, R. G., Rodrigues, N. R. and Campbell, R. D. (1988) Reactivity of cytosine and thymine in single-base-pair mismatches with hydroxylamine and osmium tetroxide and its application to the study ofmutations. Proc Natl Acad Sci USA 85:4397-4401.
Cotton, R. G. H. (1993) Current methods of mutation detection. Mutat Res 285:125-144.
Cush, R., Cronin, J. M., Stewart, W. J., Maule, C. H., Molloy, J. and Goddard, N. J. (1993) The resonantmirror - a novel optical biosensor for direct sensing of biomolecular interactions. 1. Principle ofoperation and associated instrumentation. Biosens Bioelectron 8:347-353.
Danielsson, B. (1991) Calorimetric biosensors. Biochem Soc Trans 19:26-28.
Dekker, J., Kanellopoulos, P. N., van Oosterhout, J. A., Stier, G., Tucker, P. A. and van der Vliet, P. C. (1998)ATP-independent DNA unwinding by the adenovirus single-stranded DNA binding proteinrequires a flexible DNA binding loop. J Mol Biol 277:825-838.
DeRisi, J. L., Iyer, V. R. and Brown, P. O. (1997) Exploring the metabolic and genetic control of geneexpression on a genomic scale. Science 278:680-686.
Dill, K., Chan, S. D. H. and Gibbs, T. W. (1997) Detection of plasmids using DNA and RNA probes and thelight-addressable potentiometric sensor. J Biochem Biophys Methods 35:197-202.
Doyle, M. L. (1997) Characterization of binding interactions by isothermal titration calorimetry. Curr OpinBiotechnol 8:31-35.
Drmanac, R., Labat, I., Brukner, I. and Crkvenjakov, R. (1989) Sequencing of megabase plus DNA byhybridization: theory of the method. Genomics 4:114-128.
Drmanac, S., Kita, D., Labat, I., Hauser, B., Schmidt, C., Burczak, J. D. and Drmanac, R. (1998) Accuratesequencing by hybridization for DNA diagnostics and individual genomics. Nat Biotechnol 16:54-58.
Drobyshev, A., Mologina, N., Shik, V., Pobedimskaya, D., Yershov, G. and Mirzabekov, A. (1997) Sequenceanalysis by hybridization with oligonucleotide microchip: identification of beta-thalassemiamutations. Gene 188:45-52.
Ebersole, R. C., Miller, J. A., Moran, J. R. and Ward, M. D. (1990) Spontaneously formed functionally activeavidin monolayers on metal surfaces: a strategy for immobilizing biological reagents and design ofpiezoelectric biosensors. J Am Chem Soc 112:3239-3241.
Eriksson, M. and Nielsen, P. E. (1996) PNA-nucleic acid complexes. Structure, stability and dynamics. Q RevBiophys 29:369-394.
Fawcett, N. C., Evans, J. A., Chien, L.-C. and Flowers, N. (1988) Nucleic acid hybridization detected bypiezoelectric resonance. Anal Lett 21:1099-1114.
Fischer, S. G. and Lerman, L. S. (1983) DNA fragments differing by single base-pair substitutions areseparated in denaturing gradient gels: correspondence with melting theory. Proc Natl Acad SciUSA 80:1579-1583.
Fotin, A. V., Drobyshev, A. L., Proudnikov, D. Y., Perov, A. N. and Mirzabekov, A. D. (1998) Parallelthermodynamic analysis of duplexes on oligodeoxyribonucleotide microchips. Nucleic Acids Res26:1515-1521.
50
Garland, P. (1996) Optical evanescent wave methods for the study of biomolecular interactions. Q Rev Biophys29:91-117.
Gotoh, M., Hasegawa, Y., Shinohara, Y., Shimizu, M. and Tosu, M. (1995) A new approach to determine theeffect of mismatches on kinetic parameters in DNA hybridization using an optical biosensor. DNARes 2:285-293.
Gotoh, M., Hasebe, M., Ohira, T., Hasegawa, Y., Shinohara, Y., Sota, H., Nakao, J. and Tosu, M. (1997a)Rapid method for detection of point mutations using mismatch binding protein (MutS) and anoptical biosensor. Genet Anal 14:47-50.
Gotoh, M., Hasebe, M., Ohira, T. and Tosu, M. (1997b) Gene diagnosis with an affinity sensor, BIACORE--principle and applications. Rinsho Byori 45:224-228.
Griffiths, D. and Hall, G. (1993) Biosensors - what real progress is being made? Trends Biotechnol 11:122-130.
Hacia, J. G., Brody, L. C., Chee, M. S., Fodor, S. P. and Collins, F. S. (1996) Detection of heterozygousmutations in BRCA1 using high density oligonucleotide arrays and two-colour fluorescenceanalysis. Nat Genet 14:441-447.
Haruki, M., Noguchi, E., Kanaya, S. and Crouch, R. J. (1997) Kinetic and stoichiometric analysis for thebinding of Escherichia coli ribonuclease HI to RNA-DNA hybrids using surface plasmonresonance. J Biol Chem 272:22015-22022.
Hashimoto, K., Ito, K. and Ishimori, Y. (1994) Sequence-specific gene detection with a gold electrode modifiedwith DNA probes and an electrochemically active dye. Anal Chem 66:3830-3833.
Healey, B. G., Matson, R. S. and Walt, D. R. (1997) Fiberoptic DNA sensor array capable of detecting pointmutations. Anal Biochem 251:270-279.
Heller, A. (1996) Amperometric biosensors. Curr Opin Biotechnol 7:50-54.
Hutchinson, A. M. (1995) Evanescent wave biosensors. Real-time analysis of biomolecular interactions. MolBiotechnol 3:47-54.
Ito, K., Hashimoto, K. and Ishimori, Y. (1996) Quantitative analysis for solid-phase hybridization reaction andbinding reaction of DNA binder to hybrids using a quartz crystal microbalance. Anal Chim Acta327:29-35.
Jensen, K. K., Ørum, H., Nielsen, P. E. and Nordén, B. (1997) Kinetics for hybridization of peptide nucleicacids (PNA) with DNA and RNA studied with the BIAcore technique. Biochemistry 36:5072-5077.
Jin, G., Tengvall, P., Lundström, I. and Arwin, H. (1995) A biosensor concept based on imaging ellipsometryfor visualization of biomolecular interactions. Anal Biochem 232:69-72.
Jordanova, A., Kalaydjieva, L., Savov, A., Claustres, M., Schwarz, M., Estivill, X., Angelicheva, D., Haworth,A., Casals, T. and Kremensky, I. (1997) SSCP analysis: a blind sensitivity trial. Hum Mutat 10:65-70.
Jönsson, U., Fägerstam, L., Ivarsson, B., Johnsson, B., Karlsson, R., Lundh, K., Löfås, S., Persson, B., Roos,H., Rönnberg, I., Sjölander, S., Stenberg, E., Urbaniczky, C., Östlin, H. and Malmqvist, M. (1991)Real-time biospecific interaction analysis using surface plasmon resonance and a sensor chiptechnology. BioTechniques 11:620-627.
Jönsson, U. and Malmqvist, M. (1992) Real-time biospecific interaction analysis. The integration of surfaceplasmon resonance detection, general biospecific interface chemistry and microfluidics into oneanalytical system. Adv Biosensors 2:291-236.
51
Kinjo, M. and Rigler, R. (1995) Ultrasensitive hybridization analysis using fluorescence correlationspectroscopy. Nucleic Acids Res 23:1795-1799.
Kinjo, M., Nishimura, G., Koyama, T., Mets and Rigler, R. (1998) Single-molecule analysis of restriction DNAfragments using fluorescence correlation spectroscopy. Anal Biochem 260:166-172.
Kleinjung, F., Bier, F. F., Warsinke, A. and Scheller, F. W. (1997) Fibre-optic genosensor for specificdetermination of femtomolar DNA oligomers. Anal Chim Acta 350:51-58.
Kozal, M. J., Shah, N., Shen, N., Yang, R., Fucini, R., Merigan, T. C., Richman, D. D., Morris, D., Hubbell,E., Chee, M. and Gingeras, T. R. (1996) Extensive polymorphisms observed in HIV-1 clade Bprotease gene using high-density oligonucleotide arrays. Nat Med 2:753-759.
Kretschmann, E. (1971) Die Bestimmung optischer Konstanten von Metallen durch Anregung vonOberflächenplasmaschwingungen. Z Phys 241:313-324.
Landegren, U., Kaiser, R., Sanders, J. and Hood, L. (1988) A ligase-mediated gene detection technique.Science 241:1077-1080.
Lashkari, D. A., McCusker, J. H. and Davis, R. W. (1997a) Whole genome analysis: experimental access to allgenome sequenced segments through larger-scale efficient oligonucleotide synthesis and PCR.Proc Natl Acad Sci USA 94:8945-8947.
Lashkari, D. A., DeRisi, J. L., McCusker, J. H., Namath, A. F., Gentile, C., Hwang, S. Y., Brown, P. O. andDavis, R. W. (1997b) Yeast microarrays for genome wide parallel genetic and gene expressionanalysis. Proc Natl Acad Sci USA 94:13057-13062.
Liedberg, B., Nylander, C. and Lundström, I. (1983) Surface plasmon resonance for gas detection andbiosensing. Sens Actuators 4:299-304.
Liedberg, B., Lundström, I. and Stenberg, E. (1993) Principles of biosensing with an extended coupling matrixand surface plasmon resonance. Sens Actuators B 11:63-72.
Lockhart, D. J., Dong, H., Byrne, M. C., Follettie, M. T., Gallo, M. V., Chee, M. S., Mittmann, M., Wang, C.,Kobayashi, M., Horton, H. and Brown, E. L. (1996) Expression monitoring by hybridization tohigh-density oligonucleotide arrays. Nat Biotechnol 14:1675-1680.
Lorenzo, E., Pariente, F., Hernandez, L., Tobalina, F., Darder, M., Wu, Q., Maskus, M. and Abruna, H. D.(1998) Analytical strategies for amperometric biosensors based on chemically modified electrodes.Biosens Bioelectron 13:319-332.
Lukosz, W. (1995) Integrated optical chemical and direct biochemical sensors. Sens Actuat B 29:37-50.
Lundbäck, T., Hansson, H., Knapp, S., Ladenstein, R. and Härd, T. (1998) Thermodynamic characterization ofnon-sequence-specific DNA-binding by the Sso7d protein from Sulfolobus solfataricus. J Mol Biol276:775-786.
Lundström, I. (1994) Real-time biospecific interaction analysis. Biosens Bioelectron 9:725-736.
Lysov, Y. P., Florentiev, V. L., Khorlyn, A. A., Khrapko, K. R., Shick, V. V. and Mirzabekov, A. D. (1988)Determination of the nucleotide sequence of DNA using hybridization with oligonucleotides. Anew method. Dokl Akad Nauk SSSR 303:1508-1511.
Löfås, S. and Johnsson, B. (1990) A novel hydrogel matrix on gold surfaces in surface plasmon resonancesensors for fast and efficient covalent immobilization of ligands. J Chem Soc Chem Commun21:1526-1528.
Löfås, S., Malmqvist, M., Rönnberg, I., Stenberg, E., Liedberg, B. and Lundström, I. (1991) Bioanalysis withsurface plasmon resonance. Sens Actuators B 5:79-84.
52
Malmqvist, M. and Karlsson, R. (1997) Biomolecular interaction analysis: affinity biosensor technologies forfunctional analysis of proteins. Curr Opin Chem Biol 1:378-383.
McKusick, V. A. (1997) Genomics: structural and functional studies of genomes. Genomics 45:244-249.
Mikkelsen, S. R. (1996) Electrochemical biosensors for DNA sequence detection. Electroanal 8:15-19.
Millan, K. M., Saraullo, A. and Mikkelsen, S. R. (1994) Voltammetric DNA biosensor for cystic fibrosis basedon a modified carbon paste electrode. Anal Chem 66:2943-2948.
Milner, N., Mir, K. U. and Southern, E. M. (1997) Selecting effective antisense reagents on combinatorialoligonucleotide arrays. Nat Biotechnol 15:537-541.
Minunni, M., Sklàdal, P. and Mascini, M. (1994) A piezoelectric quartz crystal biosensor as a direct affinitysensor. Anal Lett 27:1475-1487.
Moser, I., Schalkhammer, T., Pittner, F. and Urban, G. (1997) Surface techniques for an electrochemical DNAbiosensor. Biosens Bioelectron 12:729-737.
Mullis, K., Faloona, F., Scharf, S., Saiki, R., Horn, G. and Erlich, H. (1986) Specific enzymatic amplificationof DNA in vitro: the polymerase chain reaction. Cold Spring Harb Symp Quant Biol 51:263-273.
Mullis, K. B. and Faloona, F. A. (1987) Specific synthesis of DNA in vitro via a polymerase-catalyzed chainreaction. Methods Enzymol 155:335-350.
Myers, R. M., Larin, Z. and Maniatis, T. (1985) Detection of single base substitutions by ribonuclease cleavageat mismatches in RNA:DNA duplexes. Science 230:1242-1246.
Napier, M. E., Loomis, C. R., Sistare, M. F., Kim, J., Eckhardt, A. E. and Thorp, H. H. (1997) Probingbiomolecule recognition with electron transfer: electrochemical sensors for DNA hybridization.Bioconjug Chem 8:906-913.
Newton, C. R., Graham, A., Heptinstall, L. E., Powell, S. J., Summers, C., Kalsheker, N., Smith, J. C. andMarkham, A. F. (1989) Analysis of any point mutation in DNA. The amplification refractorymutation system (ARMS). Nucleic Acids Res 17:2503-16.
Nickerson, D. A., Kaiser, R., Lappin, S., Stewart, J., Hood, L. and Landegren, U. (1990) Automated DNAdiagnostics using an ELISA-based oligonucleotide ligation assay. Proc Natl Acad Sci USA87:8923-8927.
Nicolini, C., Erokhin, V., Facci, P., Guerzoni, S., Ross, A. and Paschkevitsch, P. (1997) Quartz balance DNAsensor. Biosens Bioelectron 12:613-618.
Nilsson, P., Persson, B., Uhlén, M. and Nygren, P-Å., (1997). Analysis of DNA sequence using biosensors, inLaboratory methods for the detection of mutations and polymorphisms in DNA, Taylor, G. R. (ed),CRC Press Inc, Boca Raton, FL, USA. pp. 253-261.
Nolan, J. P., Shen, B., Park, M. S. and Sklar, L. A. (1996) Kinetic analysis of human flap endonuclease-1 byflow cytometry. Biochemistry 35:11668-11676.
Nolan, J. P. and Sklar, L. A. (1998) The emergence of flow cytometry for sensitive, real-time measurements ofmolecular interactions. Nat Biotechnol 16:633-638.
Okahata, Y., Kawase, M., Niikura, K., Ohtake, F., Furusawa, H. and Ebara, Y. (1998) Kinetic Measurementsof DNA Hybridization on an Oligonucleotide-Immobilized 27-MHz Quartz Crystal Microbalance.Anal Chem 70:1288-1296.
Okayama, H., Curiel, D. T., Brantly, M. L., Holmes, M. D. and Crystal, R. G. (1989) Rapid, nonradioactivedetection of mutations in the human genome by allele-specific amplification. J Lab Clin Med114:105-113.
53
Olson, J. D., Panfili, P. R., Zuk, R. F. and Sheldon, E. L. (1991) Quantitation of DNA hybridization in a siliconsensor-based system: application to PCR. Mol Cell Probes 5:351-358.
Orita, M., Iwahana, H., Kanazawa, H., Hayashi, K. and Sekiya, T. (1989) Detection of polymorphisms ofhuman DNA by gel electrophoresis as single-strand conformation polymorphisms. Proc Natl AcadSci USA 86:2766-2770.
Panayotou, G. (1998a) Surface plasmon resonance. Measuring protein interactions in real time. Methods MolBiol 88:1-10.
Panayotou, G., Brown, T., Barlow, T., Pearl, L. H. and Savva, R. (1998b) Direct measurement of the substratepreference of uracil-DNA glycosylase. J Biol Chem 273:45-50.
Pastinen, T., Kurg, A., Metspalu, A., Peltonen, L. and Syvänen, A. C. (1997) Minisequencing: a specific toolfor DNA analysis and diagnostics on oligonucleotide arrays. Genome Res 7:606-614.
Pease, A. C., Solas, D., Sullivan, E. J., Cronin, M. T., Holmes, C. P. and Fodor, P. A. (1994) Light-generatedoligonucleotide arrays for rapid DNA sequence analysis. Proc Natl Acad Sci USA 91:5022-5026.
Piunno, P. A. E., Krull, U. J., Hudson, R. H. E., Damha, M. J. and Cohen, H. (1995) Fiber-optic DNA sensorfor fluorometric nucleic acid determination. Anal Chem 67:2635-2643.
Plum, G. E. and Breslauer, K. J. (1995) Calorimetry of proteins and nucleic acids. Curr Opin Struct Biol5:682-690.
Pockrand, I., Swalen, J. D., Gordon, J. G. and Philpott, M. R. (1978) Surface plasmon spectroscopy of organicmonolayer assemblies. Surface Sci 74:237-244.
Polzius, R., Dießel, E., Bier, F. F. and Bilitewski, U. (1997) Real-time observation of affinity reactions usinggrating couplers: determination of the detection limit and calculation of kinetic rate constants.Anal Biochem 248:269-276.
Proudnikov, D., Timofeev, E. and Mirzabekov, A. (1998) Immobilization of DNA in polyacrylamide gel for themanufacture of DNA and DNA-oligonucleotide microchips. Anal Biochem 259:34-41.
Ramsden, J. J. (1997) Optical biosensors. J Mol Recognit 10:109-120.
Ratilainen, T., Holmen, A., Tuite, E., Haaima, G., Christensen, L., Nielsen, P. E. and Norden, B. (1998)Hybridization of peptide nucleic acid. Biochemistry 37:12331-12342.
Ronaghi, M., Uhlén, M. and Nyrén, P. (1998) Real-time pyrophosphate detection for DNA sequencing.Science 281:363-365.
Rutigliano, C., Bianchi, N., Tomassetti, M., Pippo, L., Mischiati, C., Feriotto, G. and Gambari, R. (1998)Surface plasmon resonance for real-time monitoring of molecular interactions between a triplehelix forming oligonucleotide and the Sp1 binding sites of human Ha-ras promoter: Effects of theDNA-binding drug chromomycin. Int J Oncol 12:337-343.
Saiki, R. K., Scharf, S., Faloona, F., Mullis, K. B., Horn, G. T., Erlich, H. A. and Arnheim, N. (1985)Enzymatic amplification of beta-globin genomic sequences and restriction site analysis fordiagnosis of sickle cell anemia. Science 230:1350-1354.
Saiki, R. K., Bugawan, T. L., Horn, G. T., Mullis, K. B. and Erlich, H. A. (1986) Analysis of enzymaticallyamplified beta-globin and HLA-DQ alpha DNA with allele-specific oligonucleotide probes. Nature324:163-166.
Saiki, R. K., Gelfand, D. H., Stoffel, S., Scharf, S. J., Higuchi, R., Horn, G. T., Mullis, K. B. and Erlich, H. A.(1988) Primer-directed enzymatic amplification of DNA with a thermostable DNA polymerase.Science 239:487-491.
54
Saiki, R. K., Walsh, P. S., Levenson, C. H. and Erlich, H. A. (1989) Genetic analysis of amplified DNA withimmobilized sequence-specific oligonucleotide probes. Proc Natl Acad Sci USA 86:6230-6234.
Sanger, F., Nicklen, S. and Coulson, A. R. (1977) DNA sequencing with chain-terminating inhibitors. ProcNatl Acad Sci USA 74:5463-5467.
Sauerbrey, G. (1959) Verwendung von schwingquarzen zur wägung dunner schichten und zur mikrowägung.Z Phys 155:206-222.
Schena, M., Heller, R. A., Theriault, T. P., Konrad, K., Lachenmeier, E. and Davis, R. W. (1998) Microarrays:biotechnology's discovery platform for functional genomics. Trends Biotechnol 16:301-306.
Sjölander, S. and Urbaniczky, C. (1991) Integrated fluid handling system for biomolecular interaction analysis.Anal Chem 63:2338-2345.
Smith, J. and Modrich, P. (1996) Mutation detection with MutH, MutL, and MutS mismatch repair proteins.Proc Natl Acad Sci USA 93:4374-4379.
Sommer, S. S., Cassady, J. D., Sobell, J. L. and Bottema, C. D. (1989) A novel method for detecting pointmutations or polymorphisms and its application to population screening for carriers ofphenylketonuria. Mayo Clin Proc 64:1361-1372.
Southern, E. M. (1975) Detection of specific sequences among DNA fragments separated by gelelectrophoresis. J Mol Biol 98:503-517.
Southern, E. M., Maskos, U. and Elder, J. K. (1992) Analyzing and comparing nucleic acid sequences byhybridization to arrays of oligonucleotides: evaluation using experimental models. Genomics13:1008-1017.
Stenberg, E., Persson, B., Roos, H. and Urbaniczky, C. (1991) Quantitative determination of surfaceconcentration of protein with surface plasmon resonance using radiolabeled proteins. J ColloidInterface Sci 143:513-526.
Stimpson, D. I., Hoijer, J. V., Hsieh, W. T., Jou, C., Gordon, J., Theriault, T., Gamble, R. and Baldeschwieler,J. D. (1995) Real-time detection of DNA hybridization and melting on oligonucleotide arrays byusing optical wave guides. Proc Natl Acad Sci USA 92:6379-6383.
Storri, S., Santoni, T., Minunni, M. and Mascini, M. (1998) Surface modifications for the development ofpiezoimmunosensors. Biosens Bioelectron 13:347-357.
Su, H. and Thompson, M. (1995) Kinetics of interfacial nucleic acid hybridization studied by acoustic networkanalysis. Biosens Bioelectron 10:329-340.
Syvänen, A.-C., Aalto-Setälä, K., Harju, L., Kontula, K. and Söderlund, H. (1990) A primer-guided nucleotideincorporation assay in the genotyping of apolipoprotein E. Genomics 8:684-692.
Szabo, A., Stolz, L. and Granzow, R. (1995) Surface plasmon resonance and its use in biomolecular interactionanalysis (BIA). Curr Opin Struct Biol 5:699-705.
Thorp, H. H. (1998) Cutting out the middleman: DNA biosensors based on electrochemical oxidation. TrendsBiotechnol 16:117-121.
Tiefenthaler, K. (1992) Integrated optical couplers as chemical waveguide sensors. Adv Biosensors 2:261-289.
Turbadar, R. (1959) Complete adsorption of light by thin metal films. Proc Phys Soc 73:40-44.
Venter, J. C., Adams, M. D., Sutton, G. G., Kerlavage, A. R., Smith, H. O. and Hunkapiller, M. (1998)Shotgun sequencing of the human genome. Science 280:1540-1542.
55
Wallace, R. B., Johnson, M. J., Hirose, T., Miyake, T., Kawashima, E. H. and Itakura, K. (1981) The use ofsynthetic oligonucleotides as hybridization probes. II. Hybridization of oligonucleotides of mixedsequence to rabbit beta- globin DNA. Nucleic Acids Res 9:879-894.
Wang, D. G., Fan, J. B., Siao, C. J., Berno, A., Young, P., Sapolsky, R., Ghandour, G., Perkins, N.,Winchester, E., Spencer, J., Kruglyak, L., Stein, L., Hsie, L., Topaloglou, T., Hubbell, E.,Robinson, E., Mittmann, M., Morris, M. S., Shen, N., Kilburn, D., Rioux, J., Nusbaum, C., Rozen,S., Hudson, T. J., Lipshutz, R., Chee, M. and Lander, E. S. (1998) Large-scale identification,mapping, and genotyping of single- nucleotide polymorphisms in the human genome. Science280:1077-1082.
Wang, J., Cai, X., Rivas, G., Shiraishi, H., Farias, P. A. M. and Dontha, N. (1996) DNA electrochemicalbiosensor for the detection of DNA sequences related to the human immunodeficiency virus. AnalChem 68:2629-2634.
Wang, J., Nielsen, P. E., Jiang, M., Cai, X., Fernandes, J. R., Grant, D. H., Ozsoz, M., Beglieter, A. andMowat, M. (1997a) Mismatch-sensitive hybridization detection by peptide nucleic acidsimmobilized on a quartz crystal microbalance. Anal Chem 69:5200-5202.
Wang, J., Rivas, G., Cai, X., Chicharro, M., Parrado, C., Dontha, N., Begleiter, A., Mowat, M., Palecek, E.and Nielsen, P. E. (1997b) Detection of point mutation in the p53 gene using a peptide nucleic acidbiosensor. Anal Chim Acta 344:111-118.
Ward, M. D. and Buttry, D. A. (1990) In situ interfacial mass detection with piezoelectric transducers. Science249:1000-1007.
Watson, J. D. and Crick, F. H. C. (1953) Molecular structure of nucleic acids. A structure for deoxyribosenucleic acid. Nature 171:737-738.
Watts, H. J., Yeung, D. and Parkes, H. (1995) Real-time detection and quantification of DNA hybridization byan optical biosensor. Anal Chem 67:4283-4289.
Welford, K. (1991) Surface plasmon-polaritons and their uses. Opt Quant Electron 23:1-27.
White, M. B., Carvalho, M., Derse, D., O'Brien, S. J. and Dean, M. (1992) Detecting single base substitutionsas heteroduplex polymorphisms. Genomics 12:301-306.
Wilchek, M. and Bayer, E. A. (1988) The avidin-biotin complex in bioanalytical applications. Anal Biochem171:1-32.
Winzeler, E. A., Richards, D. R., Conway, A. R., Goldstein, A. L., Kalman, S., McCullough, M. J., McCusker,J. H., Stevens, D. A., Wodicka, L., Lockhart, D. J. and Davis, R. W. (1998) Direct allelic variationscanning of the yeast genome. Science 281:1194-1197.
Wodicka, L., Dong, H., Mittmann, M., Ho, M. H. and Lockhart, D. J. (1997) Genome-wide expressionmonitoring in Saccharomyces cerevisiae. Nat Biotechnol 15:1359-1367.
Wood, S. J. (1993) DNA-DNA hybridization in real-time using BIAcore. Microchem J 47:330-337.
Wu, D. Y., Ugozzoli, L., Pal, B. K. and Wallace, R. B. (1989) Allele-specific enzymatic amplification of beta-globin genomic DNA for diagnosis of sickle cell anemia. Proc Natl Acad Sci USA 86:2757-2760.
Yang, M. S., McGovern, M. E. and Thompson, M. (1997) Genosensor technology and the detection ofinterfacial nucleic acid chemistry. Anal Chim Acta 346:259-275.
Yershov, G., Barsky, V., Belgovskiy, A., Kirillov, E., Kreindlin, E., Ivanov, I., Parinov, S., Guschin, D.,Drobishev, A., Dubiley, S. and Mirzabekov, A. (1996) DNA analysis and diagnostics onoligonucleotide microchips. Proc Natl Acad Sci USA 93:4913-4918.
56
Youil, R., Kemper, B. W. and Cotton, R. G. (1995) Screening for mutations by enzyme mismatch cleavagewith T4 endonuclease VII. Proc Natl Acad Sci USA 92:87-91.
Zhai, J. H., Cui, H. and Yang, R. F. (1997) DNA based biosensors. Biotechnol Adv 15:43-58.