Patent Application
20180298436
The present disclosure relates generally to methods of controlling the movement of molecules, such as DNA (Deoxyribonucleic Acid), RNA (Ribonucleic Acid) and proteins as well as other biological molecules passing through nanopores so that they can be detected, characterized and/or sequenced.
Since 454 Life Sciences launched the first 2nd generation DNA sequencing system in 2005, DNA sequencing has become one of the hottest technologies with a rapidly growing market. The major feature of the 2nd generation DNA sequencing is its massive parallel sequencing capacity with super high throughput and short read length. It is much faster and cheaper than the 1st generation technology, i.e., Sanger's method. However, its short read length makes de novo assembly, whole genome phasing, and structural variant analysis very difficult, limiting its capability to resolve complex DNA regions with repetitive or heterozygous sequences. The short read length also makes computations like sequencing entire RNA transcripts or some gene sequences in metagenomics projects difficult or impossible. A significant future application of DNA sequencing is clinical diagnostics, which requires even faster, cheaper and more accurate sequencing technologies. There is tremendous interest in searching for new DNA sequencing technologies capable of long read length (>>1000 bases), fast run time (<1 hour per genome) and low cost (<$300 per genome). Nanopore based DNA sequencing technology is the most promising 3rd generation technology that could satisfy these requirements.
The concept of nanopore sequencing was developed based on the work of John Kasianowicz et al using the α-hemolysin pore in 1996. The α-hemolysin pore has a 1.5 nm diameter at its narrowest point which is sufficiently large to allow a single strand DNA (ssDNA) to pass through it but too small for double strand DNA (dsDNA). If a pore is positioned in a membrane between two pools of ionic buffer and a bias voltage is applied across the membrane, then an ionic current will be detected through the pore. When an ssDNA passes through the pore, the ionic current will be partially blocked. The magnitudes of blockage is distinct for different DNA bases. By measuring the ionic current blockages as the ssDNA passes through the pore the bases can be sequenced. The same principle can be applied to determine the sequences of RNA, polypeptide (amino acid), or other linear molecules. Other nanopore DNA base sensing methods are also under development, such as recognition tunneling (Lindsay and Zhang, 2008, 2016), and nanowire FET (Han et al, 2014).
The first patent describing DNA sequencing using a nanopore was published by Akeson et al in 2001. Since then, it attracted huge interest from both academic research labs and industrial R&D. Nanopores that can be used for DNA sequencing include biological (protein) pores held on lipid bilayer membrane, such as alpha-hemolysin pores (Kasianowicz et al, 1996, Akeson et al, 2001, Stoddart et al, 2015), MspA (Mycobacterium smegmatis porin A) pores (Derrington et al 2010, Pavlenok et at, 2012), and CsgG pores (curli specific genes G) (Goyal et al, 2014), and synthetic nanopores, including solid state nanopores and graphene nanopores (Wanunu, 2012). So far, the most difficult problem for DNA sequencing using a nanopore is that the DNA molecules pass through nanopores very fast, approximately 1 μs per base, which makes reliable base sensing with single base resolution very difficult or impossible. To have a DNA successfully sequenced, the DNA translocation speed has to be slowed down at least 1000 times to about 1 ms per base or longer. The preferred speed range for reliable single base resolution with the current base sensing technologies is 3 ms to 10 ms per base.
A variety of methods for controlling or slowing down DNA translocation speed have been proposed ever since the concept of nanopore sequencing had emerged in 1990's. These methods can be divided into the following six categories: (1) biological methods, such as molecular motors (helicase, polymerase, etc.) (Akeson et al, 2011) and dsDNA hairpin or complementary probe DNA method (Sauer-Budge et al, 2003, Derrington et al, 2010, Wanunu 2012); (2) buffer conditioning methods, such as lowering the buffer temperature (Yeh et al, 2012, Fologea et al 2005), using lithium chloride salt instead of potassium chloride (Kowalczyk et al, 2012) or increasing buffer viscosity (Fologea et al, 2005); (3) chemical methods (for synthetic nanopores), such as nanopore surface charge modification or polymer binding to the nanopore (Wanunu and Meller, 2007, Keyser, 2011); (4) electronic methods, such as DNA transistor technology (Polonsky et al, 2007, 2011) or transverse electric field dragging (Tsutsui et al, 2012); (5) Mechanical methods, such as optical tweezers (Keyser et al, 2006, Keyser 2011), magnetic tweezers (Peng and Ling, 2009) and atomic force microscopy (AFM) (King and Golovchenko, 2005), and (6) Electro-mechanical, such as integrating a piezo layer in the synthetic nanopore fabrication (Peng et al, 2011). All these methods have either problems in controlling DNA movement or difficulties in fabrication and instrumentation. The molecular motor method moves DNA at the speed of specific enzyme's intrinsic processing rate which is not easily controlled. It is suitable for biological pores only and requires complicated biochemistry for the attachment of enzymes to each pore. The dsDNA hairpin/complementary probe methods slow down DNA movement sporadically without effective speed control and require tremendous efforts on sample processing. The buffer conditioning methods can slowdown DNA translocation only five to ten times, far from the required 1000 times. The chemical methods and the transverse electronic field dragging method have no mechanism to realize any accurate DNA translocation speed control. The DNA transistor technology demonstrated a mechanism on how to control the DNA base movement inside a synthetic nanopore computationally, but it is difficult to realize because it requires a very complicated nanopore structure, it is very difficult to fabricate and integrate with base sensing. The optical and magnetic tweezers as well as the AFM methods can control a single DNA molecule passing through nanopores. It is good for academic research but far from sufficient for large scale inexpensive high-throughput DNA sequencing and other commercial applications. The electro-mechanical method proposed by Peng et al (2011) uses a piezoelectric layer in synthetic nanopore fabrication to control the nanopore size inside the nanopore so that the DNA translocation can be slowed down, however, it does not provide a mechanism on how to precisely control the DNA movement.
Thus, an improved system for controlling the movement of DNA as well as other polymers through nanopores is needed.
The present disclosure is directed toward methods and systems for controlling the translocation rate of a molecule through a nanopore with sufficient precision and at an appropriate rate to enable base unit sequencing. This disclosure broadly applies to the base unit sequencing and/or molecular structure analysis of DNA, RNA, protein and other charged biological molecules or non-charged biological molecules with charged tags, both natural and synthesized. Synthetic, non-biological molecules may also be analyzed.
In one embodiment the target molecule (e.g. ssDNA fragment to be sequenced) is attached to a magnetic bead via a linker molecule of the same type of properly chosen length and composition (e.g. a single strand λ-DNA or a synthesized DNA oligo). Electric force pulls the charged target molecule through the nanopore until its progress is impeded by the magnetic bead which is too big to pass through the nanopore. By applying a magnetic field, the magnetic bead and the attached linker can be pulled away from the nanopore toward the surface of a scan plate placed near the nanopore and perpendicular to the nanopore axis. The magnetic bead is then held against the scan plate either solely by the strength of the magnetic field or by a chemical bond or by other means. The DNA and linker are stretched under the electric force acting on the DNA bases inside the nanopore. Intra-molecular tension is built up and a force equilibrium is established between the intra-molecular tension and the electric force.
By moving either the scan plate or the nanopore substrate using a precision linear stage, the target molecule can be pulled out of the nanopore or inserted into the nanopore at the speed required for base unit sequencing. The target molecule does not move freely through the nanopore but rather is held taut under the constant tension from the opposing forces as it progresses. As the target molecule passes through the nanopore its bases are sensed and recorded by an appropriate base sensing method, such as ionic current blockage method, recognition tunneling method or other methods. Part of the linker molecule may be used as a calibration template for the sequencing if desired. Multiple target molecules can be sequenced with a single nanopore or with a plurality of nanopores (nanopore arrays).
In some embodiments of this disclosure, the linker molecule may have a linker node located where the linker attaches to the target DNA. The linker node is a molecular structure that prevents entry into the nanopore and is generally larger than the entrance of the nanopore, and in certain embodiments at least twice as large as the nanopore entrance size. The linker node can be a large protein (such as an antibody, a NeutrAvidin or a streptavidin), or a large polymer complex, or even a non-magnetic bead. The linker molecule is not required to be of the same kind of molecule as the target molecule. It can be a dsDNA, a ssDNA, or a RNA, either from nature or being synthesized, or a cellulose fiber or other flexible linear polymers. When the target DNA is pulled into the nanopore under an electric field, the linker node will function as the stopper or brake for the DNA translocation. With this linker+linker node configuration, a relatively weak magnetic field can be applied initially to lift the magnetic bead attached to one end of the linker molecule while the target molecule and the linker node are still held tight at the nanopore by the electric force. By floating the magnetic bead straight above the nanopore before it contacts the scan plate, a perfect alignment is achieved for the bead, linker molecule and the target molecule, allowing for an accurate sequencing of the target molecule.
In some embodiments of this disclosure, the target molecule is attached to the scan plate directly or via a linker molecule but without a magnetic bead. By placing the scan plate less than one linker molecule length from the nanopore substrate the target molecule can be pulled into the nanopore by the electric field. When the molecule movement is impeded by the attachment to the scan plate, it can be moved out or retracted back into the nanopore at a controlled steady speed that is slow enough for accurate base unit sensing. A plurality of target molecules can be attached laterally across the scan plate. The scan plate and nanopore substrate can be displaced laterally in an area scanning pattern to engage different molecules with the nanopore and such that they can be sequenced.
In some embodiments of this disclosure, the scan plate surface can be patterned with micro-spots or patches for target molecule attachment and these micro-patterns are precisely aligned with nanopores on a nanopore array chip. Each spot corresponds to one nanopore on the nanopore chip. Each spot may contain plurality of target molecules. After each sequencing run, the already sequenced molecule is pulled out from the nanopore and the scan plate or nanopore chip moves laterally in a scan mode to align another target molecule to enter the nanopore to be sequenced. Hence, at the end, all or the majority of the target molecules can be sequenced.
In some embodiments of this disclosure, micro-pillars with either sharp end or flat end are attached or micro-fabricated onto the scan plate surface facing the nanopore substrate. The target molecules are attached to the end of these micro-pillars directly or through a linker molecule or via a magnetic bead. These pillars are aligned with nanopores on the nanopore chip. Target molecules are sequenced with the controlled movement of the scan plate or the nanopore chip plate.
In another embodiment the target molecule (e.g. an ssDNA fragment) is attached to a magnetic bead via a linker molecule of the same type (e.g. a natural or synthesized ssDNA) of properly chosen length and composition. Electric force pulls the charged target molecule through the nanopore until its progress is stopped by the magnetic bead which is too big to pass through the nanopore. By applying a magnetic field, the magnetic bead and the attached DNA molecule can be pulled away from the nanopore toward the surface of a container wall placed near the nanopore with a distance from the nanopore sufficiently larger than the linker molecule and the target molecule combined. By solely controlling the balance of forces acting on the bead and the target DNA molecule (namely the magnetic field strength and the electric force of the nanopore), the DNA molecule can be pulled out at a speed slow enough for base sensing.
It is critical to maintain a constant force balance from the beginning of the DNA movement so that the DNA can be moved at a desired, predictable speed. This can be done by completely eliminating or minimizing the sticking forces acting on the magnetic bead when it is near or in contact with the nanopore entrance. The major source of the sticking force comes from the electric charge on the bead. By making the magnetic bead non-charged, the sticking force can be greatly reduced and a relatively smooth movement of the DNA molecule through the pore can be maintained. As the bead moves, the target molecule will be stretched under force, and an intra molecular tension will be built up. A force equilibrium is established and maintained as the target molecule proceeds through the nanopore at a controlled speed. Thus the target molecule does not move freely through the nanopore but rather is held taut under the tension from the opposing forces as it progresses. As the target molecule passes through the nanopore its bases are sensed and recorded by an appropriate base sensing method. The linker molecule of the same kind may be used as the calibration of the target molecule sequencing. Another function of the linker molecule is to provide a buffer zone so that any possible jitters of the DNA movement at the start can be lessened or dampened out. A plural form of target molecules can be sequenced with a single nanopore or a plural form of nanopores.
In some embodiment of this disclosure, for the magnetic force controlled DNA movement, a linker node is introduced as the connection between the linker molecule and the target molecule. The linker node is generally larger than the nanopore entrance, in some embodiments at least twice as large as the nanopore entrance so that it will function as the stopper or brake as the DNA translocate through the nanopore under the bias voltage. Since now the linker node is at the nanopore, it is required to be non-charged while the magnetic bead is not required to be non-charged. The linker node can be a large protein, such as an antibody, NeutrAvidin, streptavidin, or any polymer complex larger than the nanopore entrance or even a non-magnetic bead.
In another embodiment of this disclosure, the target molecule may be attached to the magnetic bead or the scan plate directly without using a linker molecule either for the mechanical controlled movement or magnetic force controlled movement approaches.
An embodiment is a system for controlling movement of a charged linear molecule comprising a substrate positioned between a cis space and a trans space, a nanopore in the substrate through which at least a portion of the charged linear molecule can pass from the cis space to the trans space, a scan plate located in the cis space to which directly or indirectly a first end of the charged linear molecule is attached, an actuator for controlling the distance between the substrate and the scan plate such that they can be moved with nanometer precision, and a bias source for applying a bias voltage between the cis space and the trans space to direct a second end of the charged linear molecule to enter into the nanopore. In another embodiment the system includes an attachment system that assists the attachment of the charged linear molecule to the scan plate such that the charged linear molecule can move with the scan plate. In another embodiment, the substrate is a nanopore chip comprising a plurality of nanopores positioned in a planar arrangement wherein each nanopore is substantially equidistant from the surface of the scan plate. In another embodiment, the nanopore comprises a biological pore, or a synthetic pore, or a combination thereof. In an embodiment, the biological pore is selected from the group consisting of an alpha-hemolysin pore, a MspA pore, a CsgG pore, a modified version thereof, and a combination thereof. In an embodiment, the synthetic pore is made from silicon nitride (Si3N4), silicon dioxide (SiO2), aluminum oxide (Al2O3), boron nitride (BN), graphene, molybdenum disulfide (MoS2) or a polymer or a hybrid thereof. In an embodiment, the attachment system comprises a chemical bond, either covalent or non-covalent, and either reversible or non-reversible. In an embodiment, the chemical bond is selected from the list comprising a biotin-streptavidin bond, an amide bond; a phosphodiester bond, ester bond, disulfide bond, imine bond, aldehyde bond, hydrogen bond, hydrophobic bonds, and a combination thereof. In an embodiment, the attachment system comprises a magnetic bead, which is attached to the first end of the charged linear molecule, and the magnetic bead is made from one of the following materials: (a) paramagnetic, (b) super-paramagnetic, (c) ferromagnetic, or (d) diamagnetic. In an embodiment, a controllable magnet comprises an electromagnet, an adjustable permanent magnet, a group of magnets, or a combination thereof and wherein the controllable magnet is configured to attract the magnetic bead towards the scan plate and to hold the magnet bead against the scan plate. In an embodiment, the attachment system comprises a flexible linker molecule, and the flexible linker molecule is attached to the first end of the charged linear molecule at one end and attached to the scan plate at other end. In an embodiment, the flexible linker molecule is selected from the group consisting of a single stranded nucleic acid, a double stranded nucleic acid, a polypeptide chain, a cellulose fiber or any flexible linear polymer, either natural, modified or synthesized, and a combination thereof. In an embodiment, the flexible linker molecule is the same kind of molecule as the charged linear molecule. In an embodiment, the attachment system further comprises a linker node which is disposed between the flexible linker molecule and the charged linear molecule; and wherein the linker node is configured to block the linker molecule from entering the nanopore. In an embodiment, the linker node is a protein selected from the group consisting of an antibody, an enzyme, a NeutrAvidin, a streptavidin, and an avidin, or a polymer complex, or a particle or a bead, or a combination thereof. In an embodiment, a flexible linker molecule is disposed between the charged linear molecule and the magnetic bead. In an embodiment, the flexible linker molecule is selected from the group consisting of a single stranded nucleic acid, a double stranded nucleic acid, a polypeptide chain, a cellulose fiber or any flexible linear polymer, either natural, modified or synthesized, and a combination thereof. In an embodiment, the flexible linker molecule is the same kind of molecule as the charged linear molecule. In an embodiment, the attachment system further comprises a linker node which is disposed between the flexible linker molecule and the charged linear molecule; and wherein the linker node is configured to block the linker molecule from entering the nanopore. In an embodiment, the linker node is a protein selected from the group consisting of an antibody, an enzyme, a NeutrAvidin, a streptavidin, an avidin, a polymer complex, a particle, a non-magnetic bead, and a combination thereof. In an embodiment, the system comprises a detector for determining the identity or characteristics of individual base units of the charged linear molecule as they pass through the nanopore, wherein the base units of the charged linear molecule can be detected by their effect on the ionic current blockage, or recognition tunneling, or field-effect transistor, or other base sensing methods, or a combination thereof. In an embodiment, the system comprises a micro-pillar attached or microfabricated onto the scan plate that has either a pointed end or a flat-bottom end, which is configured to allow the attachment of the first end of the charged linear molecule. In an embodiment, the micro-pillar is an array of micro-pillars on the scan plate, laterally positioned to match an array of nanopores on the substrate. In an embodiment, the actuator comprises a precision linear motion stage that is configured to control the distance between the scan plate and the substrate such that the charged linear molecule can be pulled out or inserted into the nanopore at a steady rate that enables accurate base unit sequencing. In an embodiment, the rate is about 0.5 ms per base unit or slower. In an embodiment, the rate is from about 3 ms to about 20 ms per base unit. In an embodiment, the precision linear motion stage comprises a linear stage driven by a piezo-electric effect drive with nanometer or sub-nanometer precision. In an embodiment, the actuator comprises a coarse precision actuator that is coupled to the scan plate or the substrate by mechanical reduction allowing for nanometer or sub-nanometer precision movement of the scan plate or the substrate. In an embodiment, the coarse precision actuator comprises a micrometer or a sub-micrometer servo motor. In an embodiment, the system further comprises an adjustment stage with micrometer precision that is coupled to the scan plate or the substrate that is configured to move the object laterally and/or vertically for pre-sequencing position adjustment. In an embodiment, a plurality of charged linear molecules is attached to the scan plate randomly. In an embodiment, a plurality of charged linear molecules is attached to a patterned area on the scan plate, wherein the plurality of charged linear molecules in the patterned area is laterally aligned with a plurality of nanopores on the substrate. In an embodiment, the system further comprises a secondary adjustable magnet that is configured to remove the magnetic bead from the scan plate. In an embodiment, the charged linear molecule is a nucleic acid sequence or a polypeptide sequence; and wherein the nucleic acid sequence is selected from the list consisting of single stranded DNA, double stranded DNA, single stranded RNA, oligonucleotide, a sequence comprising a modified nucleotide, and a combination thereof.
An embodiment is a method for controlling movement of a charged linear molecule comprising providing a scan plate and a substrate plate placed substantially parallel and aligned laterally with each other; attaching a first end of the charged, linear molecule to the scan plate, either directly or indirectly; aligning the charged linear molecule with a nanopore in the substrate plate by an adjustable mechanical apparatus; directing a second end of the charged linear molecule to the nanopore in the substrate plate by an electric force; moving the charged linear molecule through the nanopore by adjusting the distance between the scan plate and the substrate plate; maintaining an intra-molecular tension in the charged linear molecule by adjusting the electric force during the sequencing process. In an embodiment, the adjustable mechanical apparatus comprises a single axis or a multi-axis linear stage with micrometer or sub micrometer precision. In an embodiment, the adjusting the distance between the scan plate and the substrate plate comprises moving the scan plate and/or the substrate plate with an actuator. In an embodiment, the actuator comprises a linear stage driven by a piezo-electric effect drive with nanometer or sub-nanometer precision. In an embodiment, the actuator comprises a coarse precision actuator that is coupled to the scan plate or the substrate by mechanical reduction providing for nanometer or sub-nanometer precision movement of the scan plate or the substrate plate. In an embodiment, the coarse precision actuator comprises a micrometer or a sub-micrometer precision servo meter. In an embodiment, the electrical force is achieved by an electrical bias apparatus which is configured to apply a bias voltage across the substrate plate allowing a current through the nanopore and is further configured to pull the charged linear molecule through the nanopore. In an embodiment, a flexible linker molecule is disposed between the charged linear molecule and the scan plate; and wherein the flexible linker molecule is selected from the list consisting of a single stranded nucleic acid, a double stranded nucleic acid, a polypeptide chain, a cellulose fiber or any flexible linear polymer, either natural, modified or synthesized, and a combination thereof. In an embodiment, a linker node is disposed between the linker molecule and the charged linear molecule and the linker node is configured to block the linker molecule from entering the nanopore, and wherein the linker node is a protein selected from the list consisting of an antibody, an enzyme, a NeutrAvidin, a streptavidin, and an avidin, or a polymer complex or particle or bead, a portion thereof, and a combination thereof. In an embodiment, the method further comprises attaching the first end of the charged linear molecule to a magnetic bead; wherein the magnetic bead is chosen from the list consisting of a super-paramagnetic bead, a paramagnetic bead, a ferromagnetic bead, and a diamagnetic bead; aligning the charged linear molecule with the nanopore by applying a magnetic field to attract the magnetic bead towards the scan plate while the electric force maintains the engagement of the charged linear molecule with the nanopore; wherein the magnetic field is from an electromagnet or an adjustable permanent magnet, or a group of magnets, or a combination thereof; wherein the magnetic bead contacts the surface of the scan plate substantially orthogonally aligned above the nanopore and is held tightly against the scan plate by the magnetic field such that the magnetic bead and the charged linear molecule move substantially with the scan plate. In an embodiment, a flexible linker molecule is disposed between the charged linear molecule and the magnetic bead; and wherein the flexible linker molecule is selected from the list consisting of a single stranded nucleic acid, a double stranded nucleic acid, a polypeptide chain, a cellulose fiber or any flexible linear polymer, and a combination thereof, either natural, modified or synthesized. In an embodiment, a linker node is disposed between the linker molecule and the charged linear molecule and the linker node is configured to block the linker molecule from entering the nanopore; and wherein the linker node is a protein selected from the list consisting of an antibody, an enzyme, a NeutrAvidin, a streptavidin, and an avidin, or a polymer complex or a non-magnetic particle/bead, or a combination thereof; and wherein aligning the charged linear molecule with a nanopore in the substrate plate further comprises setting a distance between the scan plate and the substrate plate larger than the length of the linker molecule; applying a magnetic field such that the magnetic force on the magnetic bead is sufficient to lift the magnetic bead, but not sufficient to substantially lift the linker node; wherein the linker node is engaged at the nanopore by the electric force, reducing the distance between the scan plate and the substrate plate to be smaller than the length of the linker molecule; wherein the magnetic bead contacts the scan plate and is held by the scan plate substantially orthogonally aligned above the nanopore, resulting in a substantial orthogonal alignment between the bead, the linker molecule and the charged linear molecule. In an embodiment, the charged linear molecule is randomly distributed on the scan plate, either attached directly or indirectly. In an embodiment, a plurality of the charged linear molecules is distributed in a patterned area on the scan plate either attached directly or attached indirectly, wherein the plurality of the charged linear molecules in the patterned area on the scan plate is substantially laterally aligned with a plurality of the nanopores on the substrate plate. In an embodiment, the substrate plate is a nanopore chip comprising a plurality of nanopores positioned in a planar arrangement such that each nanopore is substantially equidistant from the surface of the scan plate. In an embodiment, the scan plate has a micro-pillar facing the nanopore, which has either a pointed end or a flat end; and wherein the first end of the charged linear molecule is attached to the micro-pillar, either directly or indirectly. In an embodiment, the scan plate has an array of micro-pillars that match an array of nanopores on the substrate plate. In an embodiment, the charged linear molecule is a nucleic acid sequence or a polypeptide sequence; and wherein the nucleic acid sequence is selected from the list consisting of single stranded DNA, double stranded DNA, single stranded RNA, oligonucleotide, a sequence comprising a modified nucleotide, and a combination thereof.
This disclosure provides a method to precisely control the movement of a molecule, such as a DNA through a nanopore by a mechanical device, or more specifically, by a nanometer (nm) or sub-nanometer (sub-nm) precision piezo drive or combination of drives. In combination with electric force, it moves DNA into and out of nanopores either continuously or stepwise at a speed sufficient or slow enough for reliable base sensing depending on the base sensing method selected. For example; the ionic current blockage base sensing method using a protein nanopore requires at least 1 ms (millisecond) sensing time per base.
The basic principle is illustrated in
The nanopore (500) is part of a nanopore chip (501). The scan plate (510) is mounted parallel to the nanopore chip. Both the nanopore chip and the scan plate are coupled to the analysis stage (570) that can control their separation distance (571). The analysis stage is an appropriately selected automated precision linear motion stage. The nanopore chip mechanically divides the buffer volume into cis (650) and trans (651) buffer volumes on the opposing sides of the nanopore. The cis and trans buffer volumes are fluidically and electrically isolated by the nanopore substrate with communication through only the passage of the nanopore. An electrical bias source (530) maintains a voltage across the nanopore.
During the sequencing the DNA molecule being analyzed (600) spans the cis and trans buffer volumes by passing through the nanopore. On the cis side of the nanopore the DNA is joined to a flexible linker molecule (602) which is attached to a scan plate (510). The linker attachment to the DNA (i.e. the linker node) (601) and the attachment (610) of the linker to the scan plate are discussed further in a later section.
Since the DNA is negatively charged it is pulled through the nanopore to the trans side by the strong electric field inside the nanopore. When DNA on the cis side is depleted, both the DNA and flexible linker molecule are pulled taut between the scan plate and the nanopore. The linker and the DNA stretch somewhat under the tension and DNA bases continue to pass to the trans side of the nanopore until the tension of the stretched DNA matches the electric force acting on the DNA bases. This equilibrium tension is bias voltage dependent and corresponds to a specific stretched spacing of the DNA bases. If the nanopore and scan plate are moved closer together or moved further apart the tension in the DNA will also change (slightly) causing the DNA to move to restore the equilibrium condition. Provided that the separation speed is adequate and constant, the DNA will remain under constant tension as it moves. The DNA can either be pulled out of the nanopore, or inserted into the nanopore. DNA can therefore be sequenced in either direction without altering the nanopore bias voltage polarity or magnitude.
Maintaining a certain level of tension is required for accurate sequencing:
As described above the controlled motion of DNA through a nanopore is determined by the separation distance (571) between a nanopore and a scan plate. Control of the separation distance is achieved by minimizing vibration between those elements and by implementing an analysis stage with sufficiently precise motion control.
Vibration control is achieved in several ways:
The analysis stage (570) has some requirements:
A mechanism that meets these specifications is a piezo-electric drive (alternately called a piezo-electric stage, piezo-electric stack, piezo-electric actuator or piezo-electric transducer). Piezo-electric devices are extremely stiff, have the necessary precision, and move without vibration.
Alternative mechanisms may also be suitable. Some possible options include less precise actuators combined with mechanical reduction (i.e. leverage) to achieve the necessary precision. Conceivably a servo driven actuator could work if vibration can be minimized. Piero-electric linear motors may also work, if they are controlled to eliminate vibration.
The degree of precision required in the stage motion is certainly attainable with present day technology. Examples of nanometer precision piezo electric drives can be found in scanning tunneling microscopy (STM) and atomic force microscopy (AFM), which are widely used in biological microstructure analyses. King and Golovchenko (2005) demonstrated that they could thread a 105 nm long 5 nm diameter nanotube through a nanopore using an AFM tip. They could move the nanotube in and out the nanopore at a speed around 800 nm/s and measure the ionic current changes. Considering a unit length of 0.7 nm for the single strand DNA, it is equivalent to about 1 ms per base.
Another example of commercially available nanometer precision piezo drives is the P-62x series precision Z-stages from Physik Instrument GmbH & Co., which have 0.1 to 1 nm precision with positioning accuracy 0.02%, traveling range 50 to 400 μm. With the right load and operating frequency, it can easily achieve speeds from 1 ms to 10 ms per base, slow enough for base sensing yet fast enough for rapid DNA sequencing. For example, a 100 kb DNA strand, can be sequenced in about 8 minutes with throughput of 5 ms per base.
One approach to minimizing vibration is to assemble the nanopore and the scan plate into a compact subassembly (579) such as is depicted schematically in
In the layout shown the nanopore chip is bonded to a rigid frame (575) that constrains the motion of the scan plate and determines its relaxed position (i.e. the maximum separation from the nanopore chip). The scan plate can be moved toward the nanopore by squeezing the subassembly (579) together using the analysis actuator (591) which is coupled to a rigid frame (590) that wraps around the subassembly (579)
This design shortens the mechanical path by bridging the gap between the scan plate and the nanopore chip. Although the compressive element (576) can be squeezed vertically it can be chosen such that substantial force is required such that it acts as a strong coupler. The compressive element may also be strongly non-isotropic meaning that although it can be squeezed vertically it may strongly resist lateral shearing deformation (i.e. it may be very stiff laterally). The compressive element can also have dampening properties or be mounted in parallel to a dampening element that further reduces vibration.
One embodiment discloses a subassembly in which the scan plate and the nanopore are pressed together or in near proximity to each other when the subassembly is at rest and are pulled further apart when the subassembly is acted on by an external analysis actuator. That implementation may be advantageous because it allows the subassembly to be fabricated with the scan plate and the nanopore chip to be substantially parallel and separated by a predetermined minimum distance (e.g. use micrometer shims or patches) when the subassembly is in its rest state (i.e. not acted on externally). Procedurally this is convenient for sequencing. It is discussed in a later section.
It is important to consider “compression set” or more generally “non-elastic deformation” when creating this subassembly. In some embodiments, deformable materials such as rubber with restorative force (i.e. elastic force) may be diminished if they are compressed or stretched for a prolonged time. To manage the effect of “set” it is best to design the subassembly such that during operating conditions the moving elements are further from equilibrium than it during storage. Alternatively, a material that doesn't degrade such as spring steel can be chosen.
In
In both
The scan plate and the nanopore chip may require adjustment of their relative position in addition to the analysis-stage/analysis-actuator motion required for DNA sequencing. These adjustments may be required for sample loading, or for extending the motion of the analysis stage. They may also be required to implement certain sequencing protocols described in a later section.
Additional stage(s) used for adjustment etc. do not necessarily require the same precision as the analysis stage. Stages with coarser precision motion (i.e. μm precision) may be sufficient and may offer longer ranges of motion. These stages do not need to be implemented together as shown in the figure. For example, the X and Y axis could be implemented to move the nanopore chip (501) with respect to the rigid frame (574) and the Z axis could be implemented to move the analysis stage (and therefore the scan plate) with respect to the rigid frame (574). Also, since it is only the relative separation of the scan plate and the nanopore chip that is essential, the analysis stage could be implemented on the nanopore chip as well.
It should also be noted that although the illustrations indicate the nanopore chip surface oriented horizontally this convention is used for ease of understanding and is not a requirement. Some embodiments may orient the nanopore chip surface and the scan plate vertically, at an intermediate oblique angle, or even inverted and orient the stage motions accordingly.
The above paragraphs explain the flexibility in adjustment of the relative positions of scan plate and the nanopore chip. It is important to remember that the mechanical stiffness/rigidity of the assembly should not be compromised. It is possible to eliminate unnecessary adjustment stages that would otherwise extend the mechanical path from the nanopore chip to the scan plate.
At times during the alignment procedure the scan plate must be brought in close proximity to the nanopore chip. Prior to performing a sequencing procedure it may be necessary to calibrate the position of the analysis stage or actuator such that the minimum separation distance and the coordinates are known, i.e. the numerical position in the positioning system driver that corresponds to closest contact between the scan plate and the nanopore chip surface. The position should be known with an accuracy of a few microns.
Calibration can be performed by several means:
Optical—This type of calibration requires a window or an optical path that allows the gap between the scan plate and the nanopore to be observed and measured.
Electrical Contact—This type of calibration requires that the scan plate and the nanopore chip be filled with fluid, and it would require some portion of each of the scan plate and the nanopore chip to be made of conductive materials. These conductors could interfere with sequencing measurements. If the manufacturing is sufficiently precise the electrical contact point or points could be made at locations that are sealed away from the buffer solution.
Force—The analysis stage slowly brings the scan plate and the nanopore chip closer together. A sensitive force transducer determines when they make contact. Alternatively, raised features of known height on either the scan plate or the nanopore chip or both make the first contact to avoid possible damage to the DNA plate or the nanopore chip. This is a practical solution since the force sensor can be added to the mechanical actuator and no further changes are required to the plate or nanopore or access requirements. The force sensor layout can be designed such that minimal force is applied to the nanopore chip and the scan plate.
Separation Feedback—Assuming that the nanopore chip and the scan plate are pushed close together in a subassembly without surface contact such as the “raised features” described above. This could be achieved by a passive spring element in the assembly, such as in
The methods described in this disclosure for precise mechanical control of DNA translocation through nanopores apply to any types of nanopores without limitation, either synthetic nanopores (
The nanopore chip mentioned in this disclosure may contain a single pore or a plurality of pores or an array of pores. The pattern of nanopores on the chip can be in any shape, such as square, rectangular, linear, elongated rectangle, split rectangle, circular, elliptic or annular see
Certain base sensing methods such as ionic current sensing require electrical measurements that span the nanopore (i.e. one electrode is on the trans side of the nanopore, one electrode is on the cis side of the nanopore). To make these measurements for a plurality of nanopores it may be necessary to electrically isolate the buffer surrounding the electrical contact on at least one side of each nanopore from all the other nanopores. These various permutations of common and isolated wells on either side of the nanopore are illustrated in
In an embodiment, DNA molecules can be attached to the scan plate with or without a linker molecule. The simplest way is to attach DNA onto the scan plate surface randomly (
Although utilizing a flat scan plate is an exemplary embodiment, some configurations of the wells and of the DNA attachment require micro-pillars to be included on the scan plate (
The micro-pillars can be short or tall depending on the required function. The attachment surface can be rounded or flat depending on method of attachment. The different methods for attachment of the DNA are discuss in a later section.
Micro-pillars require precise alignment to the corresponding nanopores. This can be accomplished with a precisely manufactured subassembly or by using motorize lateral adjustment drives combined with feedback from the nanopore sensors.
The number of strands of DNA that are attached to the micro-pillar is largely determined by the manufacturing method that determines the area for DNA attachment. This area can be sized for any number of DNA stands from a single strand to hundreds or more depending of the sequencing method desired. The density of DNA is also influenced by the concentration of the DNA in solution when the attachment is made.
The sequencing procedure can be divided into two phases for the purpose of discussion:
The Engaging DNA phase has a few significant variations depending on the geometry of the scan plate, the spatial distribution of the DNA on the scan plate, the presence or absence of a flexible linker molecule between the DNA and its attachment to the scan plate or micro-pillar.
The DNA can be lengthened by adding a flexible linker molecule to one end and attaching the linker molecule to the scan plate or to the micro-pillar. This embodiment allows some degree of misalignment between the attachment position on the scan plate and the nanopore position while sequencing the entire length of the DNA. It also allows the DNA to engage with the nanopore while the scan plate and the nanopore chip are not touching.
The scan attachment (610) is the attachment of the DNA or the linker molecule either directly to the scan plate (510) or to the micro-pillar.
The linker node (601) is the location of the connection between the DNA strand (600) and the flexible linker molecule (602). It can be a protein, such as Streptavidin or Neutravidin or antibody, or a non-magnetic bead or just simply a chemical bond, such as phosphodiester bond when the target DNA is ligated to a linker λ-DNA.
Although a permanent attachment is acceptable, the DNA/linker attachment to the scan plate (610) can also be a reversible non-covalent bond such as biotin-streptavidin coupling or a covalent bond breakable under certain buffer conditions or catalysts so that the sequencing can be repeated by detaching the sequenced DNA and re-attaching a new DNA. The biotin-streptavidin bond is very strong, having enough strength to hold the DNA onto the scan plate during sequencing, however, it is reversible by incubating a short time in non-ionic aqueous solutions at temperatures above 70° C. (Holmberg et al, 2005). Covalent bond is usually much stronger than non-covalent bond. An example of reversible covalent bond is the amide bond formed between a carboxylic acid and an amine. For the attachment of DNA, one can functionalize the scan plate surface with carboxylic acid and attach amine-modified DNA or linker molecule to the surface through an amide bond. The amide bond can be broken by hydrolysis under strong acid (such as HCl) or strong base (such as NaOH) when the sequenced DNA needs to be removed later. The ester bond formed between a carboxyl group and a hydroxyl group behaves the same, which can be broken by strong acids and bases as well as temperatures. Other methods regarding DNA or protein attachment to solid surfaces, either metal, glass, or plastic can be found in the review articles of Singh et al (2011) and Sassolas et al (2008), and in the articles of Liu and Rauch (2003) and Fixe et al (2004), as well as on the websites of some biotechnology companies, such as ThermoFisher Scientific and Integrated DNA technologies.
The scan plate and nanopore chip surfaces are substantially parallel to each other. These DNA attachment surfaces (i.e. the scan plate, the surfaces of the blunt micro-pillar, or tips of pointed micro-pillar) must be brought close together, typically within a few microns, for the DNA to have sufficient reach to engage in the nanopores. The DNA can be attached to the scan plate in various patterns for reasons of optimization etc. These layouts dictate the required lateral positioning of the scan plate with respect to the nanopore chip: (
In an embodiment, the cis and trans reservoirs (650 and 651) are generally filled with electrically conductive salt buffer (e.g. 1M KCl 10 mM Hepes buffer, pH8), see
Once the target DNA fragment(s) is engaged within the nanopore(s) it can be translocated in and out as previously described. The DNA (600) can be sequenced as it is translocated through the nanopore and recorded with an appropriate base sensing method, such as ionic current blockage, recognition tunneling or Nanowire FET.
In some embodiments, the DNA may need to be sequenced multiple times in order to achieve the required accuracy. A common scheme is to record the base sensing of the entire DNA by pulling the DNA completely out of and then insert it back into the nanopore several times. For an array of nanopores, numerous DNA fragments of different, lengths need to be sequenced at the same time. Some DNA fragments will finish much sooner than others during each sequencing run. Sometimes, during the insertion process, some DNAs may not be able to get into the pore and miss the repeat of sequencing.
Here, we introduce a piecewise repeated sequencing scheme that guarantees each DNA fragment will receive the same number of repeat recordings, which is illustrated in
Continue repeating step 5. As illustrated in
The base-sensing can be recorded both ways while the DNA is being pulled out and while it is being inserted into the pore. It may be more convenient for data analysis to record only while pulling the DNA out. The same base sensing method can be used in both directions, or a different method could be used during the insertion. A faster or slower speed may be used during the insertion if this results in a useful change in the base-sensing contrast or simply to perform the insertion more rapidly without base sensing.
In the example, each section of the DNA is sequenced three times. When a DNA fragment is completely pulled out of the pore, only the last partial section is sequenced a single time. The majority of the DNA fragment is sequenced three times. If more repeats are needed, the pulling and insertion lengths can be adjusted to record each section more times. It may be advantageous to insert several extra bases to such that adjacent sections overlap to insure sufficient repeat recording of the bases at the boundaries.
This disclosure also provides a method for automatic alignment of DNA with nanopores by using an adjustable magnet and magnetic beads. Aligning the DNA means to pull the DNA in a substantially straight line manner away from the nanopore, normal to the surface of the nanopore chip, and in line with the motion direction of the analysis stage. This places the end of the DNA (or places the end of the attached linker) against the scan plate at a location directly in line with the nanopore in the direction of the analysis stage motion such that it is pulled straight away from the nanopore. This alignment of the DNA insures that the length of the stretched DNA passing through the nanopore is exactly equal to the distance the stage moves, either in or out. If the attachment location is misaligned, as in the case of randomly attached DNA, the speed changes as a function of the separation distance and the force required to bond or hold the DNA against the scan plate is greater.
The purpose of the magnet is to pull the end of the DNA or linker that is on the cis side of the nanopore toward the scan plate. The magnetic field must therefore be effective in the space between the nanopore chip and the scan plate. The force of a magnet acting on a volume of magnetic material such as a magnetic bead, {right arrow over (Fm)} is roughly proportional to the gradient of the magnetic field {right arrow over (H0)}, the magnetization of the material {right arrow over (M)}, and the volume of the magnetic material in the bead VBEAD as given by the formulas below.
{right arrow over (Fm)}=μ0*VBEAD*({right arrow over (M)}·∇){right arrow over (H0)} (complete formula)
For strong magnetic fields the magnetization of the magnetic beads approaches its saturation limit and is no longer proportional to the driving magnetic field. The force formula can be simplified to:
{right arrow over (Fm)}≈VBEAD*MSaturation*{right arrow over (G)} (simplified formula for saturated magnetic materials)
In practical application this means the magnetic field must be strong in the gap between the scan plate and the nanopore chip to saturate the magnetic bead magnetization and the field must have a strong gradient increasing toward the scan plate.
This field condition can be achieved by placing a magnet directly behind the scan plate with a pole facing toward the nanopore chip as illustrated in
Although there are several variations for the alignment procedure, they all utilize some variation of magnetic beads. The beads can be super-paramagnetic, i.e. they can be magnetized in the presence of a magnetic field but they will lose their magnetism when the magnetic field is removed. They should be as small and as light as possible to avoid hindering the DNA movement toward the nanopore but sufficiently large to prevent the bead from entering the nanopore and have enough magnetic content to generate sufficient magnetic force to hold and move the target DNA molecule. In one embodiment, the size range is about 200 nm to 3 μm. In another embodiment, the size range is about 50 nm to about 10 μm. In some embodiments, the size range may be about 10 nm to 50 μm. The required bead size is dictated by the amount of force required. Flexible linker molecules can be attached to the magnetic beads via covalent bonds or non-covalent bonds, similar to the attachment of the DNA/linker molecules to the scan plate described in Part I.
The alignment can be performed with several different preparations of DNA and magnetic beads: These preparations are illustrated in
A flexible linker molecule (605) is attached to the magnetic bead (620) at one end and is linked to the sample DNA (600) through an enlarged linker node (601) which is larger than the entrance of the nanopore and functions as a brake or stopper when the DNA translocates through the nanopore (
The DNA is tagged with the magnetic beads as follows:
[magnetic bead]+[flexible linker molecule]+[linker node]+[optional calibration DNA oligo]+[ssDNA sample]
A specific example of this is a magnetic bead tagged DNA assembly below which uses a double stranded λ-DNA as the flexible linker. The double stranded λ-DNA is about 50 kilobases and has an unstretched length of about 16 μm.
[1 μm DynaBead® MyOne™ Carboxylic Acid bead]+[amine & biotin modified ds λ-DNA]+[NeutrAvidin]+[biotinylated ssDNA sample]
In one embodiment, the amine & biotin modified ds λ-DNA is shown in
Alternatively, an amine functionalized bead can be used with a crosslinker, such as BS3 crosslinker, to bind the amine modified ds λ-DNA to replace the carboxylic acid functionalized bead for a neutral charge bead surface.
The alignment procedure is as follows:
6. Alternatively, the magnetic beads can be chemically bonded to the scan plate at the initial contact to guarantee a firm contact between the bead and the scan plate surface so that the bead therefore the linker molecule and the attached DNA can be moved precisely with the scan plate movement. This may be needed in some special cases where the required maximum magnetic force is compromised, e.g. if smaller magnetic beads have to be used.
The magnetic bead (620) is attached by a flexible linker molecule (606) which is linked to the sample DNA (600) by ligation or other means (
The tagged DNA is constructed as follows:
[magnetic bead]+[flexible linker molecule][ligation][DNA sample]
A specific example of this is the magnetic bead tagged DNA assembly below which uses a single stranded λ-DNA (ss λ-DNA) as the flexible linker. The ss λ-DNA is about 50 kilobases and has a length of about 34 um when fully stretched.
[1 μm DynaBead® MyOne™ Carboxylic Acid bead]+[amine modified ss λ-DNA]+[end modified ssDNA sample]
Briefly, the steps involved in the sample processing are shown in
The alignment procedure is as follows:
This method has an identical procedure as “Alignment with single stranded DNA Linker” method. The DNA assembly is illustrated in
[magnetic bead]+[ssDNA sample]
A more specific example is:
[1 μm DynaBead® MyOne™ Carboxylic Acid bead]+[amine end modified ssDNA sample]
Another example is:
[1 μm DynaBead® MyOne™ Streptavidin bead]+[Biotinylated ssDNA sample]
The automatic alignment method of this disclosure applies to scan plates without micro-pillars (
This magnetic bead assisted DNA attachment to the scan plate makes in-device DNA detaching and reattaching much easier without complicated attaching and detaching chemistry or reagents. The magnetic automated DNA-nanopore alignment makes complicated high precision instrument alignment unnecessary, greatly simplifying the instrument design. Also, the perfect alignment allows all DNA molecules move through the pores at a constant and predictable bases-per-second rate, greatly simplifying the base sensing algorithms.
A requirement of the magnetic alignment method is that the force the magnet applies to the magnetic bead in the scan direction is greater than the electric force acting on the DNA bases inside the nanopore. This may require a large electro-magnet, a large and movable permanent magnet or even an array of permanent magnets. This requirement may dictate the minimum size for the magnetic beads.
Magnetic alignment could be combined with chemical attachment and detachment of the beads and the scan plate. This could be used to minimize the size of the magnetic beads which allows them to remain in suspension longer. Such a procedure could require the nanopore bias voltage to be reduced after the DNA is engaged such that the DNA can be pulled out of the nanopore with the reduced force of a smaller bead. After chemical attachment to the scan plate the nanopore bias voltage could be increased to add to the tension. After the sequencing is completed the DNA could be detached or destroyed.
Another means that allows the use of smaller magnetic beads or less strong magnet is to make the magnetic beads un-charged or weakly charged so to minimize non-essential electric force acting on the magnetic beads, especially when the magnetic beads get engaged with the nanopore (
It should be noted in the
For the above described magnetic bead assisted DNA-nanopore alignment and sequencing approach, a single magnetic bead attached by a single linker molecule attached by a single sample DNA is an embodiment. However, in reality it is difficult to achieve due to the plurality of binding sites on the magnetic bead as well as the linker node. If a linker node of multiple binding sites is used, especially if the linker node is a bead, complicated bead/DNA cross-link network may form, which need be avoided by all means. The following are methods suggested to minimize the creation of complex linker networks:
This disclosure also provides a method for controlling DNA, RNA and other biological molecules passing through nanopores with a controllable magnet as illustrated in
Assuming the scan plate and nanopore chip, which are parallel to each other, are in a horizontal position and the bead moves vertically from the nanopore toward the scan plate, the pulling force is the sum of Fm & Fb, and the opposing force is the sum of Fe, Fbe, Fw, Ff, and Fd. By gradually increasing the magnetic force, the pulling force will eventually surpass the opposing force, see below, so that the DNA can be pulled out of the nanopore.
F
m
+F
b
>=F
e
+F
be
+F
w
+F
f
+F
d
For successful base sequencing, the movement of the DNA needs to be slow and controllable. That means the resulting force balance should be near equilibrium and stable. Among all the forces, Fw and Fb are constant; Fe is dependent on the bias voltage, buffer conditions, nanopore conditions and number of DNA bases inside the nanopore and is usually constant; Fd is a passive force that exists only when the bead is moving, which stabilizes and dampens out DNA jittering movement; Fm is determined by the magnitude of the controllable magnetic field.
The remaining two forces, Fbe and Ff, are location specific and therefore are problematic for achieving the goal of slow and controllable DNA movement. The electric field is very strong near and at the pore but very weak further away from the pore, Fbe may be strong before the DNA moves but drop to near zero when the bead moves away from the pore. Also, the friction Ff, if any, is non-zero at the pore but drops to zero immediately when the bead leaves the pore. As the magnetic bead leaves the immediate vicinity of the nanopore, the sudden imbalance of the forces will cause a sudden accelerated DNA movement.
In order to move the DNA at a slow and smooth predictable speed, the sticking forces (Fbe+Ff) must be completely eliminated or greatly minimized. This can be done by choosing a non-sticking magnetic bead and making the bead non-charged. By reducing the sticking force to zero or nearly zero, the force balance can be precisely controlled, so can the DNA movement.
There are several ways to make a bead non-charged. One is to use NeutrAvidin (or other neutral complex) coupled magnetic beads. Since the isoelectric point of NeutrAvidin is 6.3, it behaves almost neutral under normal buffer pH. Another solution is to use the carboxylic acid functionalized magnetic bead. After the reaction of coupling amine-modified DNA, quench the reaction with excessive amount of ethylamine instead of Tris-HCl buffer or ethanolamine, a common suggestion from bead manufacturers. The resulted beads are non-charged but yet hydrophilic. See
There will always be a slight imbalance of the forces that causes acceleration of the DNA. This is especially true for a large quantity of beads with a plurality of pores on a nanopore array where the magnetic force Fm may vary across the array. The key to keep the DNA movement slow and predictable is to estimate the speed of the DNA from analysis of the base sensing signals and adjust the magnitude of the magnetic field or the bias voltage accordingly. Hence, DNA sequencing can be done with a proper base sensing method and a well-designed computer program and calibration mechanism.
Brownian motion may cause instability of DNA movement. To solve this problem, one option is to lower the buffer temperature and increase buffer viscosity to reduce the magnitude of the Brownian motion. Another option is to increase the electric force Fe by using higher bias voltage as long as the electric force is kept below the maximum magnetic force that can be achieved. As the bead moves, the target DNA molecule will be stretched under force, and an intra-molecular tension will be built up, thus the target molecule does not move freely through the nanopore but rather is held taut under the tension from the opposing forces as it progresses, similar to the mechanical control approach.
Furthermore, a linker molecule of the same kind of the target molecule can be used to link the target molecule to the bead. For example, a single strand λ-DNA can be used as the linker and ligated to the sample ssDNA, which forms a long continuous ssDNA, as shown in
As an alternative, a linker node (633) is introduced as the connection between the linker molecule (632) and the target molecules (600) (
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| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2016/059794 | 10/31/2016 | WO | 00 |
| Number | Date | Country | |
|---|---|---|---|
| 62248756 | Oct 2015 | US |
