Patent Application
20200003691
The present invention relates to an analysis device, an analysis kit, and an analysis system.
Recently, diagnostic approaches based on detection of biomarkers are gaining attention. In these approaches, biomarkers (e.g., nucleic acids such as DNA and RNA, or proteins) contained in a patient's body fluids, such as blood, are detected to diagnose cancers or Alzheimer's disease, or other diseases, such as gene disorders, or infectious disorders due to bacteria or the like.
As methods of measuring biomarkers, there are known biomarker assays based on a digital counting method, such as digital ELISA, digital PCR assay, and digital Invader assay. The digital counting method refers to a method of detecting a concentration of biomarkers by distributing biomarkers into a number of fine wells (e.g., each having a dimension of several micrometers) on a one-to-one basis and counting the wells holding the biomarkers.
The digital counting method may be a method in which target substances (objects to be detected), i.e. biomarkers, are respectively bound to particles and a number of such particles are encapsulated in respective wells to detect the number of target substances (the number of wells holding the target substances).
For example, PTL 1 describes that target substances are respectively bound to magnetic beads (particles), and a sample fluid containing a number of such magnetic beads is supplied into a channel in which a number of fine wells are open so that the magnetic beads are respectively distributed to the number of wells. PTL 1 also describes that, after distributing the magnetic beads to the wells, a reagent fluid (detection reagent), such as a fluorogenic substrate (RGP), is supplied to the channel. The reagent in the fluid is an enzyme fluid or the like that reacts with target substances to create a fluorescence phenomenon, and is used for counting wells holding the target substances.
PTL 1: JP 2014-503831 T
According to an aspect of the present invention, a device includes a well array including wells in which a target substance is detected based on a biochemical reaction thereof. Each of the wells has an aspect ratio of 1 or more as calculated by Formula (1) such that the biochemical reaction of the target substance is detected,
Aspect ratio=Depth of each well/Diameter of largest circle among circles included in a region enclosed by a rim of each well Formula (1).
A more complete appreciation of the invention and many of the attendant advantages thereof will be readily obtained as the same becomes better understood by reference to the following detailed description when considered in connection with the accompanying drawings, wherein:
The embodiments will now be described with reference to the accompanying drawings, wherein like reference numerals designate corresponding or identical elements throughout the various drawings.
With reference to
Firstly, an analysis device of the present embodiment will be described. This analysis device is a microfluidic device 1 which is used for a digital counting method that uses liquid biopsy.
As shown in
The microwell array 4 has a flat surface in which the plurality of wells 3 are open (aperture surface 6). The plurality of wells 3 may be formed on the overall aperture surface 6 of the microwell array 4. In the present embodiment, however, the plurality of wells 3 are formed in a region (well-forming region 8), excepting a perimeter region 7, of the aperture surface 6 of the microwell array 4. The well-forming region 8 may have any contour. In the present embodiment, the contour is rectangular.
As shown in
Accordingly, the well 3 may have a constant cross-sectional area or different cross-sectional areas in planes perpendicular to the depth direction of the well. Also, the well 3 may have a circular cross-sectional shape or any other cross-sectional shape in a plane perpendicular to the depth direction of the well. Moreover, in planes perpendicular to the depth direction of the well, the well 3 may have a constant cross-sectional shape throughout the depth of the well, or may have different cross-sectional shapes depending on the depth.
As shown in
In other words, each well 3 has an aspect ratio of 1 or more as calculated from the following Formula (1).
Aspect ratio=Well depth/Diameter of the largest circle among the circles in a region enclosed by the rim of the well in plan view (1)
As mentioned above, in planes perpendicular to the depth direction of the well, the wells 3 may each have a constant cross-sectional shape throughout the depth of the well, or may have different cross-sectional shapes depending on the depth. In the present specification, in either of the cases, the diameter used for calculating an aspect ratio is the diameter of the largest circle among the circles in a region enclosed by the rim of the well in plan view of the aperture of the well. The term rim herein refers to an edge of the aperture of each well.
For example, if each well has a cylindrical shape, the “diameter of the largest circle among the circles in a region enclosed by the rim of the well in plan view” can be the diameter of the aperture of the well.
As will be described later in examples, if each well configuring the well array of the analysis device has an aspect ratio of 1 or more, low-concentration target substances can be favorably detected. The expression “favorably detected” refers to that, for example, the signal/noise ratio is high. The term signal refers to a signal generated by an intended biochemical reaction, while the term noise refers to a signal generated by a negative control biochemical reaction that does not generate a signal. For example, the noise may be a signal generated by reaction of a detection reagent containing no objects to be detected, and may be termed background in other words.
The wells configuring the well array of the analysis device may each have an aspect ratio, for example, of 1 or more, or 1.3 or more, or 1.7 or more, or 2 or more, or 3 or more, or 3.5 or more, or 4 or more, as calculated from Formula (1) set forth above. However, higher aspect ratio may make the production of the well array more difficult. Therefore, the aspect ratio may have an upper limit which is, for example, 10 or 5 or 4.
In the following description, the “diameter of the largest circle among the circles in a region enclosed by the rim of the well in plan view” expressed in Formula (1) may be referred to as an “aperture diameter of the well”.
Each well 3 has an aperture diameter Wd, for example, of 100 μm or less. The well depth Wh refers to a largest distance between a rim 3a and the bottom 9 of the well 3, in a direction perpendicular to the aperture surface 6. The aperture diameter Wd refers to the diameter of a largest circle among the circles in a region enclosed by the rim 3a in plan view. Since the well 3 has a cylindrical shape in the present embodiment, the well depth Wh corresponds to the length of the cylindrical shape in the axial direction, and the aperture diameter Wd corresponds to the diameter of the cylindrical shape. For example, if the well 3 has an inverse three-sided pyramidal shape, the well depth Wh corresponds to the height of the inverse three-sided pyramid, i.e. a distance between the triangular bottom and the vertex that is not included in the bottom, in the direction perpendicular to the bottom, and the aperture diameter Wd corresponds to the diameter of the circle inscribing the triangle of the bottom.
The well depth Wh may be larger than the depth of field of a detector, which will be described later, used for the microfluidic device 1, and 100 times or less the depth of field of the detector. Preferably, the well depth Wh may be 3 time or more and 10 times or less the depth of field of the detector.
The well 3 preferably has a volume that is 100 fL (femtoliter) or more. The upper limit of the volume of the well 3 may, for example, be 5,000 fL. The well 3 preferably has a volume of 4,000 fL or less, more preferably 3,000 fL or less, even more preferably 2,500 fL or less, and most preferably 2,000 fL.
Although not limited to, the microwell array 4 may be configured to transmit light. A hydrophilic or hydrophobic material may be selected as a material for forming the microwell array 4, considering properties desired to be imparted to the well 3 (to the inner surface of the well 3 in particular). The material for forming the microwell array 4 may, for example, be at least one of glass, resin and metal, or a mixture of these materials.
The configuration of the microwell array 4 of the present embodiment will be described in detail. As shown in
In the bottom layer 11, the surface on which the wall layer 12 is disposed configures the bottom 9 of each well 3. More specifically, in the surface of the bottom layer 11 on which the wall layer 12 is disposed, regions where the wall layer 12 is not disposed configure the bottoms 9 of the respective wells 3. For example, the bottom layer 11 may be made of glass or a resin. The wall layer 12 has a plurality of holes passing through the wall layer 12 in the thickness direction and arranged in an array pattern as viewed in the thickness direction. Each hole has an inner surface configuring an inner peripheral surface 10 of a well 3. For example, the wall layer 12 may be made of a resin.
As shown in
As shown in
The cover member 5 includes a plurality of through holes 15 passing therethrough in the thickness direction. The through holes 15 communicate with the channel 2 of the microfluidic device 1 to each serve as an inlet for charging fluid into the channel 2 or as an outlet for discharging fluid therefrom. In the present embodiment, the cover member 5 has two through holes 15A and 15B (first through hole 15A and second through hole 15B). The two through holes 15A and 15B are respectively disposed at two diagonally opposite corners of the rectangular well-forming region 8.
In the present embodiment, each through hole 15 includes a small hole 16 and a large hole 17 which is larger than the small hole 16 as viewed in a direction in which the through hole is formed. The small hole 16 and the large hole 17 are aligned in a direction in which the through hole 15 is formed. The small hole 16 is open on the channel 2 side of the microfluidic device 1 to configure an opening end of the through hole 15. The large hole 17 is open on a side facing away from the channel 2 of the microfluidic device 1 to configure another opening end of the through hole 15. The large hole 17 serves, for example, as a fluid pool for pooling fluid that has flowed out of the channel 2 of the microfluidic device 1. The plurality of through holes 15 may, for example, be formed with the same shape and size, or may be formed with different shapes and sizes.
Although not limited thereto, the cover member 5 may, for example, be configured to transmit light. For example, in the case where an optical method is used for detecting fluorescence signals or the like caused by the presence of objects to be detected, such as particles or biomarkers, which are held in the wells 3, at least one of the cover member 5 and the microwell array 4 may be configured to transmit light. For example, in the case where a method other than an optical method is used for detecting fluorescence signals or the like caused by the presence of objects to be detected, such as particles or biomarkers, which are held in the wells 3, the cover member 5 and the microwell array 4 do not have to be configured to transmit light.
The material for forming the cover member 5 may, for example, be at least one of glass, resin and metal, or a mixture of these materials. The cover member 5 may have a rigidity for not being deformed by the flow of fluid or the like in the channel 2.
Between the microwell array 4 and the cover member 5, a spacer 18 is provided, surrounding the well-forming region 8 of the microwell array 4. The spacer 18 defines the gap between the microwell array 4 and the cover member 5 and configures the channel 2 of the microfluidic device 1 together with the microwell array 4 and the cover member 5.
The spacer 18 may, for example, be formed integrally with the microwell array 4 or the cover member 5. In the present embodiment, however, the spacer 18 is formed separately from them. Examples of the material for the spacer 18 include, but are not particularly limited to, a double-sided adhesive tape formed by laminating a tackifier (e.g., acrylic tackifier) on both surfaces of a core film made of silicone rubber or an acrylic foam, and paper in which an adhesive is applied to both surfaces.
A usage example of the microfluidic device 1 mentioned above will be described.
First of all, a particle-containing fluid 20 and a sealing liquid 24 are prepared. The particle-containing fluid 20 contains particles 21 as target substances. The particle-containing fluid 20 comprises the particles 21, a solvent fluid 22, and a detection reagent 23. The detection reagent 23 causes a biochemical reaction of target substances and is appropriately selected depending on the target substances. The sealing liquid 24, for example, is an oil. An analysis kit of the present embodiment includes the microfluidic device 1, the detection reagent 23, and the sealing liquid 24 mentioned above.
The particles 21 as target substances, which are objects to be analyzed, may, for example, be DNA, RNA, proteins, viral particles, bacteria, cells, or exosomes. The particles 21 may be trapped materials, such as beads, in which objects to be analyzed, such as DNA, RNA, proteins, viral particles, bacteria, cells, or exosomes, mentioned above are trapped. When viral particles, bacteria, cells, or exosomes are concerned, the reagent reacting in each well 3 can detect not only a protein or a sugar chain of the outer skin, but also DNA, RNA or a protein contained inside. Beads trapping objects to be analyzed may each have a surface that contains a substance identifying a protein or a sugar chain of the outer skin of a viral particle, a bacterium, a cell, an exosome, or the like.
Subsequently, the microfluidic device 1 is placed such that the flow of the particle-containing fluid 20 and the sealing liquid 24 in the channel 2 is directed in the horizontal direction and that the apertures of the wells 3 are oriented upward in the vertical direction. Then, the particle-containing fluid 20 is injected into the channel 2 from the first through hole 15A of the microfluidic device 1 by using a pipette.
After that, as shown in
The biochemical reaction may be an enzymatic reaction. The enzymatic reaction may be an isothermal reaction or may be an anisothermal reaction, such as PCR, that requires heat cycles. However, from the perspective of simplifying the device structure or the analysis procedure, the enzymatic reaction may preferably be an isothermal reaction. Comparing with anisothermal reaction, isothermal reaction can achieve a stable enzymatic reaction and is likely to have high reproducibility.
Specific examples of assays based on isothermal reaction may include, but are not limited to, invasive cleavage assay (ICA), loop-mediated isothermal amplification (LAMP) and SmartAmp.
After reaction, signals, as objects to be measured, are generated in the wells 3 of the microwell array 4. These signals may be fluorescence, light emission, phosphorescence, and the like. These signals have wavelength ranges observable as electromagnetic waves, such as visible light, ultraviolet light or infrared light. Accordingly, a detector including a device that can measure such wavelength ranges can be used as a detector of the present embodiment. Specifically, in the present embodiment, a fluorescence microscope 40 is used as a detector for detecting a reaction.
If the microwell array 4 is configured to transmit light, the microfluidic device 1 is disposed so as to be observable from the microwell array 4 side by the fluorescence microscope 40.
A relationship between the depth Wh of the wells 3 and a depth of field DOF of the fluorescence microscope 40 will be described in more detail. The term depth of field refers to a range in which the focus is sharp when observing or imaging a sample surface using the microscope, even when the distance between the objective lens and the sample surface is changed from the point of focus. In the present specification, the length of this range is taken to be a depth of field.
As shown in
In this regard, as shown in
The example set forth above uses the particle-containing fluid 20 that contains the particles 21 as target substances. However, the fluid is not limited to this. As long as the fluid contains target substances, any fluid may be used, i.e. the fluid does not have to contain the particles 21.
The detector may include an analysis unit 41 that analyzes a measured fluorescence value or other values (measured values). As the analysis unit 41, for example, a plate reader, a spectrophotometer, or the like may be used. The analysis system of the present embodiment includes the microfluidic device 1, the fluorescence microscope (detector) 40, and the analysis unit 41 described above.
According to the present embodiment, the microfluidic device 1 is an analysis device that detects a biochemical reaction by using the fluorescence microscope 40. The microfluidic device 1 is provided with the microwell array 4 in which a plurality of wells 3 are formed. Each well 3 may have a volume of 100 fL or more. The depth Wh of each well 3 may be larger than the depth of field DOF of the fluorescence microscope 40 and 100 times or less the depth of field DOF thereof.
In the microfluidic device 1 described above, if the depth Wh of the well 3 is larger than the depth of field DOF of the fluorescence microscope 40, more signals such as of fluorescence generated by biochemical reaction of target substances, if any, can be accumulated in a direction of the depth Wh compared to the conventional configuration. Thus, target substances having low concentration can be reliably detected.
In the following, the present invention will be described in detail by way of examples; however the present invention should not be limited by these examples.
In the present example, the effects of accumulating fluorescence signals were researched by changing the depth of the wells.
The wells of the microfluidic device were all formed into a cylindrical shape. Each well had a diameter (aperture diameter) of 5 μm and a depth of 20 μm (designed values). A microfluidic device having the wells of the above configuration was prepared from a thermoplastic resin by injection molding.
For a reagent 1, a liquid mixture of fluorescein, MOPS (3-morpholinopropanesulfonic acid), MgCl2, Tween, and DDW (purified water) was prepared. More specifically, the liquid mixture prepared as a reagent 1 contained 20 μM fluorescein, 10 mM MOPS, 10 mM MgCl2, 0.05% Tween 20, and DDW. As a sealing liquid 24, an oil (FC40 manufactured by Sigma-Aldrich) was used.
First, the reagent 1 (20 μL) prepared as described above was supplied to the first through hole of the microfluidic device by using a pipette. After that, the oil (150 μL) was supplied to the first through hole of the microfluidic device for sealing. Then, the device was observed by a fluorescence microscope (manufactured by Keyence Corporation). The fluorescence microscope had a depth of field of 3 μm (±1.5 μm).
The microfluidic device used in the present comparative example had wells each having a depth 3 μm, which was the only change in conditions compared to those of Example 1. The procedure is the same as in Example 1.
As can be seen from the results set forth above, the microfluidic device of Example 1 could accumulate 3 times or more the fluorescence values compared to Comparative Example 1.
In the present example, detectable low-concentration target substances were researched by changing the depth of the wells.
The wells of the microfluidic device were all formed into a cylindrical shape. Each well had a diameter (aperture diameter) of 5 μm and a depth of 20 μm (designed values). A microfluidic device having the wells of the above configuration was prepared from a thermoplastic resin by injection molding.
For a reagent 2, a liquid mixture of two types of allele probes, one type of Invader oligo, two types of FRET cassettes, MOPS, MgCl2, flap endonuclease, Tween, DDW, and two types of targets was prepared. More specifically, the liquid mixture prepared as a reagent 2 contained 1 μM of allele probe 1, 1 μM of allele probe 2, 1 μM of Invader oligo, target nucleic acid 1, target nucleic acid 2, which are shown in the following Table 1, and two types of FRET cassettes for detection (final concentration of 2 μM), 10 mM MOPS, 10 mM MgCl2, 1,000 U/μL flap endonuclease, 0.05% Tween 20, and DDW. Five types of reagent 2 were prepared so that the target nucleic acids 1 and 2 therein would each have concentrations 0 fM, 0.2 fM (200 aM), 2 fM, 20 fM and 200 fM. As a sealing liquid 24, an oil (FC40 manufactured by Sigma-Aldrich) was used.
In Table 1, the only difference between the target nucleic acid 1 (SEQ ID NO: 1) and the target nucleic acid 2 (SEQ ID NO: 2) as objects to be detected lies in the decapitalized g (guanine) and a (adenine) of the base sequences.
The allele probe 1 (SEQ ID NO: 3) has a sequence that is complementary to the target nucleic acid 1 and forms a duplex. However, the decapitalized part 5′-cgcgccgagg-3′ (SEQ ID NO: 6) does not form a base pair, but forms a flap and is cut out as a nucleic acid fragment by the flap endonuclease.
The allele probe 2 (SEQ ID NO: 4) has a sequence that is complementary to the target nucleic acid 2 and forms a duplex. However, the decapitalized part 5′-acggacgcggag-3′ (SEQ ID NO: 7) does not form a base pair, but forms a flap and is cut out as a nucleic acid fragment by the flap endonuclease.
Subsequently, each cut-out nucleic acid fragment is hybridized with a FRET cassette to form a flap and become a substrate of the flap endonuclease, and is cut off. As a result, a fluorescence signal is detected.
First, the reagent 2 (20 μL) prepared as described above was supplied to the first through hole of the microfluidic device by using a pipette. After that, the oil (150 μL) was supplied to the first through hole of the microfluidic device for sealing. Then, the microfluidic device was heated for isothermal reaction to generate fluorescence signals. Then, the wells were observed by a fluorescence microscope (manufactured by Keyence Corporation). The fluorescence microscope had a depth of field of 3 μm (±1.5 μm).
In Example 2, the wells formed in the microfluidic device were arbitrarily brought into a field of view of the fluorescence microscope and five images were captured for the respective target concentrations. Finally, in the captured five images, the wells that had generated fluorescence signals (which may be termed fluorescence wells hereinafter) were counted to calculate an average value.
The results are shown in Table 2. As shown in Table 2, invader reactions were confirmed in the reagents 2 respectively having target concentrations of 0 fM, 0.2 fM, 2 fM, 20 fM and 200 fM. As will be understood, as the target concentration decreases from 200 fM to 0.2 fM at a ratio of 1/10, the average value of the counts of the fluorescence wells also decreases at a ratio of about 1/10. It should be noted that, the average value of the counts of the fluorescence wells being 1 or less means that fluorescence wells cannot be confirmed. Accordingly, it was confirmed that targets were detectable for the concentration as low as 2 fM.
The microfluidic device used in the present comparative example had wells each having a depth 3 μm, which was the only change in conditions compared to those of Example 2. Six types of reagent 2 were prepared so that the target nucleic acids 1 and 2 therein would each have concentrations 0 fM, 20 fM, 200 fM, 2,000 fM (2 pM), 20,000 fM (20 pM) and 200,000 fM (200 pM).
First, the reagent 2 (20 μL) prepared as described above was supplied to the first through hole of the microfluidic device by using a pipette. After that, oil (150 μL) was supplied to the first through hole of the microfluidic device for sealing. Then, the microfluidic device was heated to perform the fluorescence reaction. Then, the wells were observed by a fluorescence microscope (manufactured by Keyence Corporation). The fluorescence microscope had a depth of field of 3 μm (±1.5 μm).
As in Example 2, the wells formed in the microfluidic device were arbitrarily brought into a field of view of the fluorescence microscope and five images were captured for the respective target concentrations. Finally, in the captured five images, fluorescence wells were counted to calculate an average value.
The results are shown in Table 3. As shown in Table 3, invader reactions were confirmed in the reagents 2 in which the target nucleic acids 1 and 2 each had the concentrations of 0 fM, 20 fM, 200 fM, 2,000 fM, 20,000 fM and 200,000 fM. As will be understood from Table 3, as the target concentration decreases from 2,000 fM to 20 fM at a ratio of 1/10, the average value of the counts of the fluorescence wells also decreases at a ratio of about 1/10. However, since the average value of the counts of the fluorescence wells at 20 fM is 7.4, the average value of the counts of the fluorescence wells is assumed to be 1 or less when the target concentration is reduced to 1/10 thereof, i.e. 2 fM, which means that no fluorescence wells can be confirmed. Accordingly, it is considered that, in Comparative Example 2, target substances cannot be appropriately detected at a concentration of 2 fM or less.
As will be understood from the results set forth above, the microfluidic device of Example 2 could achieve detection sensitivity that is about 10 times that of the microfluidic device of Comparative Example 2.
As a result of researches conducted by the inventors, the following findings were obtained in addition to those of the examples described above.
When fluorescence wells in a predetermined range are counted after increasing volumes of the wells, low-concentration target substances may be detected. In this case, if target substances at a concentration, for example, of 10 fM are to be detected, count per field (e.g., region including 100×100 wells if the wells are arrayed in a square lattice pattern) will be about 6. Therefore, it is preferable that each well has a volume of 100 fL or more. Furthermore, each well preferably has a large aspect ratio (ratio of the well depth to the aperture diameter of the well).
When each well has a larger depth, more light can be collected. Each well preferably has a depth that is larger than the depth of field of the detector, such as a microscope. When each well has a large depth, light from the fluorescent substances outside the focal length can be accumulated.
When one molecule of DNA is an object to be detected and if the number F of fluorescent molecules produced per unit time due to enzymatic reaction is constant, each well having a volume V (the volume herein is based on a cylindrical well with a diameter a and a depth h) will hold the fluorescent molecules therein at a concentration Da which is expressed by the following Formula (2).
Da=F/(π×a2×h/4) (2)
The fluorescence signals, which can be accumulated by a fluorescence microscope, are fluorescent molecules that are present in the observation direction (depth direction of wells) within a range that is shorter than 100 times of the depth of field, while fluorescent brightness (fluorescence intensity) to be detected corresponds to the number of fluorescent molecules per unit volume on a plane that is perpendicular to the observation direction. A fluorescence brightness Q in this case can be expressed by the following Formula (3).
Q=F/(π×a2/4) (3)
Accordingly, if the volume V of a well is unchanged, it is preferable that the diameter a is decreased and the depth h is increased to accumulate fluorescence signals (to increase the amount of fluorescence to be measured). The ratio between the diameter a and the depth h may preferably be h/a≥1, and more preferably h/a≥1.5.
The volume of the wells per unit volume, which can be imaged by one exposure of the microscope, may be increased to increase the probability for the target molecules to enter the wells. With this configuration, low-concentration samples can be detected. To increase the volume of the wells, it is necessary not only to arrange the wells so as to be close to each other, but also to increase the volume of each well. For closely arranging the wells, each well may preferably have a smaller diameter, with the depth being increased accordingly for increase of the volume.
If the volume of the wells per surface area is increased, reactivity of the enzymatic reaction may improve. For example, if the diameter of each well is changed, or if the aspect ratio of each well is changed, reactivity may improve. The enzymatic reaction occurring in a fine space such as of a well will receive a non-negligible influence from the surface of the solid layer. Therefore, the surface area of the inner wall of each well per volume of the well may be reduced to reduce the influence from the surface of the inner wall of the well due to adsorption or the like of enzymes or targets thereto. To reduce the surface area ratio of the reaction volume (volume of each well), the volume of each well is required to be increased, which means that the diameter of each well is required to be increased. Therefore, this increase of diameter is required to be adjusted with the accumulation of light by increasing the depth of each well as described above. Thus, if the reaction volume is 5,000 fL or more, each well may preferably have a surface area ratio (surface area of well/volume of well) of 0.4 or less. If the reaction volume is 5,000 fL or less, each well may preferably have a surface area ratio of 1 or less.
The oil used as a sealing liquid has a high probability of inhibiting the enzymatic reaction. Thus, if the volume of each well is unchanged, the diameter thereof may preferably be reduced to reduce the area contacting the oil. Alternatively, the depth of each well may be increased to increase the distance between the bottom and the oil to thereby prevent the reaction from being inhibited. The distance between the bottom and the oil is preferably 20 μm or more, and more preferably 100 μm or more. If the distance between the bottom and the oil is 3 μm or less, the probability of inhibiting the reaction is high.
If the biochemical reaction is a heating reaction, it is necessary to consider evaporation of the very small quantity of reaction liquid held in the wells. If the wells each have a reaction volume of 100 fL, or less, biochemical reaction may be considered to have ceased due to evaporation of the reaction liquid from the wells.
Analysis devices (microfluidic devices) including well arrays of Examples 3 to 5 and Comparative Examples 3 and 4 were prepared. These devices had wells with different depths and different aperture diameters. Each analysis device had the same shape as the device shown in
Subsequently, using the nucleic acid fragments shown in Table 1, nucleic acids were detected based on an invasive cleavage assay under the conditions set forth below.
Specifically, as a reagent 3, a liquid mixture was prepared, which contained 0.1 μM allele probe 1, 0.1 μM allele probe 2, 1 μM Invader oligo, and 10 fM target nucleic acid 1 shown in Table 1, and two types of FRET cassettes for detection (final concentration of 2 μM), 10 mM MOPS, 20 mM MgCl2, 0.03 mg/mL flap endonuclease, 0.05% Tween 20, and DDW. As a sealing liquid 24, an oil (FC40 manufactured by Sigma-Aldrich) was used.
Although the target nucleic acid 2 was not used for the reagent 3, the allele probe 2 and the FRET cassettes conforming to the allele probe 2 were also mixed to create experimental conditions approximate to those for actually detecting a base mutation.
Then, the reagent 3 (20 μL) prepared as described above was supplied to the first through hole of each microfluidic device by using a pipette. Then, 150 μL of oil (FC40 manufactured by Sigma-Aldrich) was supplied to the first through hole of each microfluidic device for sealing. Then, each microfluidic device was heated to produce an isothermal reaction to generate fluorescence signals. Furthermore, the well array of each microfluidic device was observed by a fluorescence microscope (manufactured by Keyence Corporation) to measure the fluorescence intensity (relative value) of the signals.
More specifically, the wells formed in each microfluidic device were observed by a fluorescence microscope to capture an image by arbitrarily bringing the wells into a field of view. In the captured image, fluorescence intensities (relative values) of the wells that had generated significant signals were measured to calculate an average value thereof as a signal value. At the same time, fluorescence intensities (relative values) of the wells that had not generated significant signals were measured to calculate an average value thereof as a noise value. The fluorescence microscope had a depth of field of 3 μm (±1.5 μm).
The series of experiments mentioned above were conducted for the analysis devices having well arrays of Examples 3 to 5 and Comparative Examples 3 and 4 to measure fluorescence intensities (relative values) of signals and noises.
The analysis devices having well arrays of Examples 3 to 5 and Comparative Examples 3 and 4 were each cut along a plane, which was parallel to the depth direction of the wells and included centers of the wells, for observation by a scanning electron microscope to actually measure the aperture diameters and depths of the wells. The aperture diameter of each well was the diameter at the aperture of the well.
Table 4 below shows measurements of the well arrays of the analysis devices of Examples 3 to 5 and Comparative Examples 3 and 4, in terms of aperture diameter, well depth, aspect ratio, well volume, average signal (relative values), average noise (relative value) and signal/noise ratio (S/N ratio).
From the results, it was obvious that the analysis devices of Examples 3 to 5 having an aspect ratio of 1 or more showed high signal/noise ratio and could favorably detect low-concentration target substances.
The present application addresses the following. The digital counting method using liquid biopsy uses a patient's body fluids, such as blood. In this method, target substances are less likely to be detected as the concentration of the target substances becomes lower. Therefore, a method with which such low-concentration target substances can be detected has been sought.
The present invention has an aspect to provide an analysis device, an analysis kit, and an analysis system with which low-concentration target substances can be detected.
The present invention has the following aspects.
[1] An analysis device for detecting a biochemical reaction by using a detector, wherein the device includes a well array in which a plurality of wells are formed; and each of the wells has an aspect ratio of 1 or more as calculated by the following Formula (1):
Aspect ratio=Depth of each well/Diameter of largest circle among circles included in a region enclosed by the rim of each well Formula (1)
[2] The analysis device according to [1], wherein each of the wells has a volume of 100 fL to 5,000 fL.
[3] The analysis device according to [1] or [2], wherein the biochemical reaction is an isothermal reaction.
[4] The analysis device according to any one of [1] to [3], wherein each of the wells has a depth that is larger than a depth of field of the detector and 100 times or less the depth of field.
[5] The analysis device according to [4], wherein the depth of each of the wells is 3 times or more the depth of field and 10 times or less the depth of field.
[6] An analysis kit including the analysis device according to any one of [1] to [5], a detection reagent, and a sealing liquid.
[7] An analysis system including the analysis kit according to [5], the detector, and an analysis unit that analyzes values measured by the detector.
The present invention may be construed to include the following aspects.
In an aspect, the present invention is an analysis device for detecting a biochemical reaction by using a detector. The device includes a well array (microwell array) in which a plurality of wells are formed. Each of the wells has a volume that is 100 fL or more, and a depth that is larger than a depth of field of the device and 100 times or less the depth of field.
In the analysis device, the depth of each of the wells may be 3 times or more the depth of field and 10 times or less the depth of field.
In the analysis device, each of the wells may have a depth/aperture diameter ratio of 1 or more.
In the analysis device, the biochemical reaction may be a heating reaction.
In an aspect, the present invention is an analysis kit including the analysis device set forth above, a detection reagent, and a sealing liquid.
In an aspect, the present invention is an analysis system including the analysis kit set forth above, the detector, and an analysis unit that analyzes values measured by the detector.
The analysis device, the analysis kit and the analysis system set forth above can detect low-concentration target substances.
Some preferred embodiments of the present invention have been described so far, but the present invention should not be limited to the embodiments described above. Addition, omission, substitution, and other changes of a configuration can be made without departing from the spirit of the invention.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2017-048601 | Mar 2017 | JP | national |
The present application is a continuation of International Application No. PCT/JP2018/009629, filed Mar. 13, 2018, which is based upon and claims the benefits of priority to Japanese Application No. 2017-048601, filed Mar. 14, 2017. The entire contents of all of the above applications are incorporated herein by reference.
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/JP2018/009629 | Mar 2018 | US |
| Child | 16570628 | US |
