Method for Processing Blood Sample
20220170913 · 2022-06-02
Assignee
Inventors
Cpc classification
International classification
G01N33/50
PHYSICS
Abstract
A method for processing a blood sample is provided that can improve the recovery rate of deformable rare cells that would easily pass through a filter and small rare cells while reducing the filtration area of the filter, and that can recover the rare cells alive.
In one aspect, the present disclosure relates to a method for separating or detecting rare cells in a blood sample using a filter including holes with a hole density of at least 200 holes/mm.sup.2 to 40000 holes/mm.sup.2, wherein the holes are in the form of an ellipse with a minor axis diameter of 3.0 μm to 15 μm and a major axis diameter of 1.1 times to 3 times as long as the minor axis diameter, or the holes have a shape that contains the ellipse and is in contact with the ellipse on at least two points including both ends of the major axis of the ellipse. The method includes separating or detecting rare cells by filtering the blood sample in a volume of 6 μl/hole or less with respect to a hole of the filter.
Claims
1-24. (canceled)
25. A filter for separating or detecting rare cells in a blood sample comprising holes with a hole density of 200 holes/mm.sup.2 to 40000 holes/mm.sup.2, wherein the holes are in the form of an ellipse with a minor axis diameter of 3.0 μm to 15 μm and a major axis diameter of 1.1 times to 3 times as long as the minor axis diameter, or the holes have a shape that contains the ellipse and is in contact with the ellipse on at least two points including both ends of the major axis of the ellipse.
26. The filter according to claim 25, comprising holes with a hole density of at least 200 holes/mm.sup.2 to 40000 holes/mm.sup.2, wherein the holes are in the form of an ellipse with a minor axis diameter of 3.0 μm to 15 μm and a major axis diameter of 1.2 times to 3 times as long as the minor axis diameter, or the holes have a shape that is in contact with the ellipse on at least two points including both ends of the major axis of the ellipse.
27. The filter according to claim 25, comprising more than 10000 holes, wherein the filter allows 1 ml to 5 ml of blood to be processed.
28. The filter according to claim 25, comprising 29000 holes or more, wherein the filter allows 5 ml to 10 ml of blood to be processed.
29. The filter according to claim 25, comprising 60000 holes or more, wherein the filter allows more than 10 ml of blood to be processed.
30. A device for capturing rare cells that captures rare cells in a sample, comprising: an inlet; an outlet; and a flow path connecting the inlet and the outlet, wherein a separation portion that includes the filter according to claim 25 and a filter holder is provided in a position corresponding to a part of the flow path.
Description
BRIEF DESCRIPTION OF THE DRAWINGS
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[0055]
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DETAILED DESCRIPTION OF THE INVENTION
[0060] Analysis of rare cells such as circulating tumor cells (CTCs) in blood is expected to continue actively in the future, and there is a growing demand for a simple efficient method. In general, tens of billions of red blood cells and tens of millions of white blood cells are contained in 10 ml of blood, but the number of CTCs only ranges from about zero to several thousands. Therefore, if CTCs are directly analyzed, they will pose many technical problems. Thus, e.g., concentration and separation of CTCs are necessary. It is expected that technology will be developed to concentrate and separate CTCs from blood more efficiently and/or simply.
[0061] In one or more embodiments, the present disclosure is based on the findings that rare cells (including relatively small cells and deformable cells) that may be present in a blood sample can be captured alive when the blood sample is filtered by: (i) adjusting the shape and size of the holes in the filter and determining the number of the holes in the filter by the formula: “Hole number (holes)=Total volume of blood sample to be processed (nl)/170 to Total volume of blood sample to be processed (nl)/10” or the formula: “Total hole area (μm.sup.2)=Total volume of blood sample to be processed (nl)/3.4 (nl/μm.sup.2) to Total volume of blood sample to be processed (nl)/0.2 (nl/μm.sup.2)”; or (ii) adjusting the volume of the blood sample passing through the holes in the filter by the formula: “Total volume of blood sample to be processed (nl)=Total hole area (μm.sup.2)×0.2 (nl/μm.sup.2) to Total hole area (μm.sup.2)×3.4 (nl/μm.sup.2)”.
[0062] In one aspect, the present disclosure relates to a method for processing a blood sample that includes filtering the blood sample (also referred to as a “processing method of the present disclosure” in the following).
Blood Sample
[0063] In the present disclosure, the “blood sample” means a sample that contains blood components and can be applied to the processing method of the present disclosure. Examples of the blood sample include blood, a blood-derived material containing red blood cell components, a body fluid or urine mixed with blood or a blood-derived material, and a sample prepared from these specimens. In the present disclosure, the volume of the blood sample passing through a hole of the filter is set on the basis of blood taken from the human body, i.e., blood containing 1000 to 20000 white blood cells per 1 μl. Therefore, when the blood sample is diluted, the diluted blood sample can be converted into the volume of the blood sample before dilution based on the white blood cell count. For example, when a 10-times diluted blood sample is processed in a volume of “X” μl/hole, it is equivalent to processing the diluted blood sample in a volume of “X/10” μl/hole. The blood can be taken from the living organisms such as humans or animals (e.g., mammals) other than humans. The blood-derived material containing the red blood cell components can be materials that are separated or prepared from blood and contain the red blood cell components, or dilutions/concentrates of these materials. Examples of the blood-derived material include the following: a blood cell fraction from which plasma has been removed; a blood cell concentrate; freeze-dried blood or freeze-dried blood cells; a sample obtained by hemolyzing whole blood to remove the red blood cell components or a hemolytic sample; centrifuged blood; sedimented blood; washed blood cells; and a specific fraction. Among them, in one or more non-limiting embodiments, the blood sample is preferably blood or blood-derived blood cells containing blood cell components so as to perform simple and rapid processing of the blood sample and to reduce damage to the rare cells in blood.
Rare Cell
[0064] In the present disclosure, the “rare cells” that may be present in blood or the blood sample mean cells other than the cell components (red blood cells, white blood cells, and platelets) that may be contained in blood of humans or animals other than humans. The rare cells include tumor cells and/or cancer cells. In general, tumor cells or cancer cells circulating in blood are called CTCs. The number of the rare cells in blood depends on the sample, and can be several to several tens and at most several hundreds to several thousands in 10 ml of blood. In one or more embodiments, the “rare cells” are selected from the group consisting of cancer cells, circulating tumor cells, vascular endothelial cells, vascular endothelial precursor cells, cancer stem cells, epithelial cells, hematopoietic stem cells, mesenchymal stem cells, embryonal cells, and a combination of these cells.
[0065] The rare cells and/or CTCs in the blood sample may include large cells, small cells, and deformable cells. The large cells can be captured by a filter with a hole diameter of about ϕ10 μm. The small cells can pass through holes having the above hole size (i.e., a diameter of about ϕ10 μm). The deformable cells can be deformed to pass through holes with a diameter of ϕ5 μm to ϕ6.5 μm when whole blood is transferred at 5 nl/min to 20 nl/min per hole. In one or more embodiments, the present invention relates to a processing method that uses a predetermined filter to separate and/or capture either or both of large deformable rare cells and small rare cells that may be present in the blood sample.
Filter Capacity
[0066] In the filtration in the processing method of the present disclosure, the number of the holes in a filter or the filter capacity (i.e., the amount of the blood sample passing through the filter, which is referred to as “the total volume of the blood sample to be processed”) can be defined by “Hole number (holes)=Total volume of blood sample to be processed (nl)/170 to Total volume of blood sample to be processed (nl)/10” or “Total hole area (μm.sup.2)=Total volume of blood sample to be processed (nl)/3.4 (nl/μm.sup.2) to Total volume of blood sample to be processed (nl)/0.2 (nl/μm.sup.2)”. In one or more embodiments, the filter capacity per hole of the filter is 0.005 μl/hole or more, 0.01 μl/hole or more, 0.014 μl/hole or more, 0.015 μl/hole or more, or 0.02 μl/hole or more in terms of maintaining the capture rate of rare cells. In one or more embodiments, the filter capacity per hole of the filter is 1 μl/hole or less, 0.2 μl/hole or less, 0.170 μl/hole or less, 0.163 μl/hole or less, 0.108 μl/hole or less, 0.054 μl/hole or less, 0.028 μl/hole or less, or 0.014 μl/hole or less in terms of processing a large amount of sample at a time, reducing the filtration area of the filter, and capturing deformable cells and small cells without clogging of the filter. In this case, the filter includes many holes, and the amount of the blood sample per hole of the filter means an average value obtained by dividing the amount of the blood sample to be processed through the filter by the number of the holes in the filter. The present inventor found that the deformable cells could be captured by adjusting the filter capacity.
[0067] In the filtration in the processing method of the present disclosure, the filter capacity can be defined by “Total volume of blood sample to be processed (nl)=Hole number (holes)×10 to Hole number (holes)×170” or “Total volume of blood sample to be processed (nl)=Total hole area (μm.sup.2)×0.2 (nl/μm.sup.2) to Total hole area (μm.sup.2)×3.4 (nl/μm.sup.2)”. In one or more embodiments, the filter capacity is 0.07 ml or more, 0.25 ml or more, 0.5 ml or more, 1 ml or more, more than 1 ml, 2 ml or more, 3 ml or more, or 4 ml or more with respect to a filtration area of 5 mm.sup.2 to 10000 mm.sup.2. In one or more embodiments, the filter capacity is 6 L or less, 4 L or less, 2 L or less, 400 ml or less, 200 ml or less, 100 ml or less, 80 ml or less, 50 ml or less, 30 ml or less, 25 ml or less, 12 ml or less, 11 ml or less, 10 ml or less, 9 ml or less, or 8 ml or less with respect to a filtration area of 5 mm.sup.2 to 10000 mm.sup.2 in terms of maintaining the capture rate of rare cells. Alternatively, in one or more embodiments, the filter capacity is in the range of more than 0.2 ml to 130 ml, in the range of 0.8 ml to 90 ml, in the range of 0.8 ml to 60 ml, in the range of 2 ml to 50 ml, or in the range of 2 ml to 40 ml with respect to a filtration area of 15 mm.sup.2 to 200 mm.sup.2 in terms of processing a large amount of sample at a time, capturing deformable cells, and maintaining the capture rate of rare cells.
Filter Hole
[0068] The hole shape of a filter used in the filtration in the processing method of the present disclosure is not particularly limited. In one or more embodiments, the hole shape is selected from the group consisting of a circle, an ellipse, a rectangle, a symmetrical polygon, an asymmetrical polygon, an irregular shape, and a combination of these shapes. In one or more embodiments, the hole shape of the filter is an ellipse with a minor axis diameter of 3.0 μm to 15 μm and a major axis diameter of 1.1 times to 3 times as long as the minor axis diameter, or a shape that contains the ellipse and is in contact with the ellipse on at least two points joining the major axis of the ellipse in terms of improving the capture rate of rare cells. In one or more embodiments, the “shape that contains the ellipse and is in contact with the ellipse on at least two points including both ends of the major axis of the ellipse” may be an ellipse-like shape that is circumscribed about the ellipse so as to touch at least two points including both ends of the major axis of the ellipse, and that is selected from the group consisting of a circle, a rectangle, a symmetrical polygon, an asymmetrical polygon, an irregular shape, and a combination of these shapes. In one or more embodiments of the present disclosure, the major axis or the major axis diameter of a hole indicates the length of the major axis when the hole is elliptical, and the minor axis or the minor axis diameter of a hole indicates the length of the minor axis when the hole is elliptical. If the major axis and the minor axis of a hole are the same, the hole may be circular or may seem to be circular. Unless otherwise noted in the present disclosure, “ϕa×b” means that the hole shape is an ellipse with a major axis of a μm and a minor axis of b μm, and “ϕc” means that the hole shape is a circle with a diameter of c μm (see
[0069] In one or more embodiments, the minor axis diameter of the ellipse as a hole of the filter is 3.0 μm or more, 4.0 μm or more, or 5.0 μm or more and 15.0 μm or less, 8.0 μm or less, less than 8.0 μm, 7.5 μm or less, 7.0 μm or less, or 6.5 μm or less in terms of improving the capture rate of small rare cells. In one or more embodiments, the small rare cells are small enough to pass through true circular holes with a diameter of about 10 μm.
[0070] In one or more embodiments, the major axis diameter of the ellipse as a hole of the filter is 1.1 times to 3 times, 1.2 times to 2.8 times, or 1.3 times to 2.6 times as long as the minor axis diameter in terms of improving the capture rate of large deformable rare cells and increasing the filter capacity. In one or more embodiments, when the minor axis diameter and the major axis diameter of the ellipse are controlled within the above ranges, respectively, the capture rate of rare cells can be improved by adjusting the filter capacity. The present disclosure is based on this surprising effect. In other words, the capture rate of small rare cells can be maintained by controlling the minor axis diameter of the ellipse within the above range, and the capture rate of deformable rare cells can be improved by extending the ellipse in the major axis direction so as to adjust the filter capacity.
[0071] In one or more embodiments, the filter used in the filtration in the processing method of the present disclosure may include holes that do not meet the above requirements as long as the holes do not affect the filtration. Alternatively, in one or more embodiments, the filter may include substantially uniform holes.
Membrane Filter
[0072] In one or more embodiments, the filter used in the filtration in the processing method of the present disclosure is a membrane filter. In one or more embodiments, the membrane filter includes holes that are in the form of an ellipse with the minor axis diameter and the major axis diameter that fall in the above ranges, respectively, or holes that have a shape that contains the ellipse and is in contact with the ellipse on at least two points joining the major axis of the ellipse in terms of maintaining the capture rate of small rare cells, improving the capture rate of deformable rare cells, and reducing the filtration area. In one or more embodiments, the area of a hole in the membrane filter is 15 μm.sup.2 to 250 μm.sup.2, 20 μm.sup.2 to 150 μm.sup.2, 30 μm.sup.2 to 100 μm.sup.2, or 40 μm.sup.2 to 80 μm.sup.2 in terms of maintaining the capture rate of small rare cells, improving the capture rate of deformable rare cells, and reducing the filtration area.
[0073] Based on the volume of the blood sample to be processed, the number of the holes in the membrane filter can be defined by “Hole number (holes)=Total volume of blood sample to be processed (nl)/170 to Total volume of blood sample to be processed (nl)/10” or “Total hole area (μm.sup.2)=Total volume of blood sample to be processed (nl)/3.4 (nl/μm.sup.2) to Total volume of blood sample to be processed (nl)/0.2 (nl/μm.sup.2)”. In one or more embodiments, the number of the holes is not particularly limited, and can be appropriately set in accordance with the amount of blood per hole in a region through which the sample passes.
[0074] When 0.1 ml of blood is processed, the number of the holes may be 600 holes or more, and preferably 900 holes or more, 1200 holes or more, or 1800 holes or more. When 1 ml of blood is processed, the number of the holes may be 6000 holes or more, and preferably 9000 holes or more, 10000 holes or more, 12000 holes or more, or 18000 holes or more. When 5 ml or more of blood is processed, the number of the holes may be 29400 holes or more, and preferably 46000 holes or more, 92000 holes or more, or 178000 holes or more. When 10 ml of blood is processed, the number of the holes may be 61000 holes or more, and preferably 92000 holes or more, 120000 holes or more, 185000 holes or more, or 357500 holes or more. When 100 ml of blood is processed, the number of the holes may be 610000 holes or more, and preferably 920000 holes or more, 1200000 holes or more, or 1850000 holes or more. The number of the holes can be appropriately selected in accordance with the probability of the rare cells being contained in blood. When 1 ml or less of blood is processed, it is desirable that at least 80% of the rare cells can be captured. When the amount of blood is increased to 1 ml or more, the number of the holes may be set so that the capture rate is 80% to 50%.
[0075] In one or more embodiments, the membrane filter has a hole density of 300 holes to 40000 holes, 300 holes to 7000 holes, 500 holes to 4000 holes, 700 holes to 4000 holes, 800 holes to 3999 holes, 900 holes to 3900 holes, or 1000 holes to 3900 holes per 1 mm.sup.2 in terms of maintaining the capture rate of small rare cells, improving the recovery rate of deformable rare cells, and reducing the filtration area. In one or more embodiments, the membrane filter has a thickness of 1 μm to 100 μm, 1 μm to 50 μm, 1 μm to 30 μm, preferably 1 μm to 20 μm, and more preferably 1 μm to 10 μm.
[0076] The shape, number, density, and area of the holes in the membrane filter can be measured, e.g., by an optical microscope, a laser microscope, or an electron microscope. Specifically, they can be measured using the method described in the following example. For example, the hole size can be measured by a laser microscope at an objective lens magnification of 10× to 100×.
[0077] In one or more embodiments, the type of the membrane filter used in the filtration in the processing method of the present disclosure is preferably a filter composed of a sheet material having substantially uniform through holes. In this case, any type of the material is available Examples of the filter include a polycarbonate (PC) filter, a parylene membrane filter, and a metal filter such as nickel (Ni). It is desirable that materials such as plastic, metal, and glass are selected in accordance with a dye or fluorescent staining used for the observation of cells on the filter. A combination of these materials may also be used.
Filtering Condition
[0078] In one or more embodiments, the filtration in the processing method of the present disclosure is capable of capturing CTCs by introducing blood into a flow path that incorporates the above filter. The filtration is not particularly limited as long as it employs a driving force to transfer a fluid. For example, blood can be introduced into the flow path by applying pressure from the direction of an inlet of the flow path, by reducing pressure from the direction of an outlet of the flow path, or by using a syringe pump or a peristaltic pump. In order to introduce blood into the flow path, e.g., the blood sample is transferred at a flow velocity of 5 μm/min to 600 μm/min (i.e., at a flow rate of 0.25 nl/min to 30 nl/min) per hole of the filter. Thus, the rare cells can be appropriately captured in a short time compared to the conventional examples.
[0079] Under the fluid transfer conditions of the blood sample, the flow velocity is preferably 5 μm/min to 600 μm/min (i.e., the flow rate is 0.25 nl/min to 30 nl/min), more preferably the flow velocity is 10 μm/min to 480 μm/min (i.e., the flow rate is 0.5 nl/min to 24 nl/min), even more preferably the flow velocity is 20 μm/min to 360 μm/min (i.e., the flow rate is 1 nl/min to 18 nl/min), and further preferably the flow velocity is 20 μm/min to 120 μm/min (i.e., the flow rate is 1 nl/min to 7 nl/min).
[0080] There is no particular limitation to a difference in pressure applied to the system of the filter device and the entire flow path (i.e., a pressure difference from the inlet to the outlet of the system) (ΔP.sub.1). The pressure difference is preferably 3.7 kPa or less, more preferably 2.6 kPa or less, and even more preferably 1.3 kPa or less.
[0081] Under the fluid transfer conditions of the blood sample, a pressure difference (ΔP.sub.2) between the upper surface and the lower surface of the filter is 110 Pa or less, preferably 100 Pa or less, more preferably 70 Pa or less, 50 Pa or less, and even more preferably 30 Pa or less, 15 Pa or less. In the case of a true circle, a pressure difference is given by ΔP.sub.2=Q×8 ηL/(πd.sup.4×N.sub.0), where Q represents the total hole number average flow rate, d represents the radius, L represents the length of the flow path in a hole, η represents the viscosity of the fluid to be transferred, π represents the ratio of the circumference of a circle to its diameter, and N.sub.0 represents the number of the holes. The pressure difference can be determined by a known calculation method based on the hole shape. Blood is a non-Newtonian fluid, and thus the average flow velocity differs depending on the viscosity due to a difference in hematocrit (Hct) even if the pressure difference is the same. Therefore, the average flow velocity has a certain range. When the pressure difference ΔP.sub.2 is set for the use of whole blood, the fluid transfer or pressure may be defined so that the pressure difference ΔP.sub.2 is numerically within the above range using η=4.5 mPa.Math.S for convenience. If the hematocrit (Hct) of the blood sample is less than 20 because of dilution or the like, the pressure difference ΔP.sub.2 may be set numerically within the above range using η=1 mPa.Math.S to 2 mPa.Math.S. Alternatively, if the blood sample is diluted to the extent that the effect of the viscosity by plasma or hematocrit (Hct) is not small (e.g., whole blood is diluted 4 to 10 times), the pressure difference ΔP.sub.2 may be calculated in accordance with the viscosity of the diluted fluid. When the flow rate is constant by using a syringe pump or the like, the blood sample may be transferred so that the pressure difference ΔP.sub.2 is within the above range. The above fluid transfer conditions can be accomplished by a mechanism that can transfer a fluid at constant pressure or a mechanism that can transfer a fluid at a constant flow rate, which are well known to those skilled in the art.
Method for Separating or Detecting Rare Cell in Sample Containing Blood Component
[0082] As a result of the filtration in the processing method of the present disclosure, rare cells (if any) remain on the filter after the sample containing blood components has been filtered, so that the rare cells can be separated or detected. Therefore, in another aspect, the present disclosure relates to a method for separating or detecting rare cells in a sample containing blood components, which includes separating or detecting rare cells by processing a blood sample by the processing method of the present disclosure.
Labeling Process of Rare Cell in Blood
[0083] In the processing method of the present disclosure, a labeling process of rare cells in blood may be performed either before, in parallel with, or after the separation of the rare cells. The labeling of rare cells is useful not only for the separation or detection method of the present disclosure, but also for a CTC enumeration method, as will be described later. Moreover, the labeling of rare cells may be useful for the analysis of the rare cells after the separation. Therefore, in one or more embodiments, the processing method of the present disclosure includes the labeling process. The labeling of rare cells is useful for a CTC enumeration method, as will be described later, and may also be useful for the analysis of the rare cells after the separation. Therefore, in one or more embodiments, the separation or detection method of the present disclosure includes the labeling process.
[0084] The labeling process can be performed, e.g., by bringing a known labeling reagent into contact with the rare cells. Typically, the labeling reagent may be mixed with the blood sample. The labeling is not particularly limited. In one or more embodiment, examples of the labeling include radioactive labeling, fluorochrome labeling, dye staining or labeling, magnetic labeling, charge labeling, and a combination of these processes, and each of them may use a suitable labeling reagent.
[0085] In other words, the labeling process of rare cells can be performed by a labeling method associated with a detection method selected from the group consisting of a detection method using a radioactive substance, a detection method using a luminous phenomenon, a detection method using a dye, a detection method using magnetic properties, an electrical detection method, an optical detection method, and a combination of these methods.
[0086] In the processing method of the present disclosure, the separation or detection of rare cells can also be achieved by detecting a change in the filter electrically, gravimetrically, or optically.
Method for Analyzing Rare Cell in Sample Containing Blood Component
[0087] In another aspect, the present disclosure relates to a method for analyzing rare cells in a sample containing blood components, which includes separating or detecting rare cells by the separation or detection method of the present disclosure, and then analyzing the rare cells by a method including kinetic observation or activity measurement of the rare cells. In the present disclosure, since the cells can be captured alive, the rare cells can be separated or detected by the separation or detection method of the present disclosure, and then analyzed by the method including kinetic observation or activity measurement of the rare cells.
Method for Enumerating CTC
[0088] It has been reported that there is a relationship between the number of CTCs in blood and metastasis and prognosis of cancer. Many studies have been conducted to find indicators of diagnosis, prognosis, and the prediction or evaluation of a therapeutic effect of cancer, and the enumeration of CTCs in blood has been known. The processing method and/or the separation or detection method of the present disclosure can separate CTCs (rare cells) while suppressing damage to the CTCs. Moreover, the nucleic acids of CTCs may be measured. Therefore, in another aspect, the present disclosure relates to a method for enumerating CTCs in a blood sample, which includes separating or detecting rare cells by processing the blood sample by the processing method of the present disclosure and/or separating CTCs from the blood sample by the separation or detection method of the present disclosure. The enumeration of CTCs or the measurement of the nucleic acids of CTCs may be performed, e.g., by flow cytometry at the same time as the separation after appropriate labeling, or by observing and counting the separated cells under a microscope, or by using the fluorescent values in view of the morphology or the amount of DNA or RNA of cancer cells.
Filter
[0089] In yet another aspect, the present disclosure relates to a filter used in the processing method, the separation or detection method, and/or the CTC enumeration method of the present disclosure. The filter includes holes with a hole density of at least 200 holes/mm.sup.2 to 40000 holes/mm.sup.2, wherein the holes are in the form of an ellipse with a minor axis diameter of 3.0 μm to 15 μm and a major axis diameter of 1.1 times to 3 times as long as the minor axis diameter, or the holes have a shape that contains the ellipse and is in contact with the ellipse on at least two points joining the major axis of the ellipse. The hole shape or the like of the filter of the present disclosure is the same as those of the filter used in the processing method of the present disclosure.
Device for Capturing Rare Cell
[0090] In yet another aspect, the present disclosure relates to a device for capturing rare cells that captures rare cells in a sample. In one or more embodiments, the device for capturing rare cells of the present disclosure includes an inlet, an outlet, and a flow path connecting the inlet and the outlet, wherein a separation portion that includes a filter holder for holding the filter of the present disclosure is provided in a position corresponding to a part of the flow path. The device for capturing rare cells of the present disclosure can use the filter of the present disclosure to perform the method for processing a blood sample of the present disclosure.
[0091] The present disclosure can relate to the following one or a plurality of embodiments.
<1> A method for separating or detecting rare cells in a blood sample using a filter including holes with a hole density of 200 holes/mm.sup.2 to 40000 holes/mm.sup.2, wherein the holes are in the form of an ellipse with a minor axis diameter of 3.0 μm to 15 μm and a major axis diameter of 1.1 times to 3 times as long as the minor axis diameter, or the holes have a shape that contains the ellipse and is in contact with the ellipse on at least two points including both ends of the major axis of the ellipse,
[0092] the method comprising:
[0093] separating or detecting rare cells by filtering the blood sample so that a filter capacity per hole of the filter is 6 μl/hole or less expressed in terms of blood.
<2> The method according to <1>, wherein the blood sample is filtered in a volume of 1 μl/hole or less expressed in terms of blood with respect to a hole of the filter.
<3> The method according to <1> or <2>, wherein the blood sample is filtered in a volume of 0.2 μl/hole or less expressed in terms of blood with respect to a hole of the filter.
<4> The method according to any one of <1> to <3>, wherein the filter has a hole density of 300 holes/mm.sup.2 to 7000 holes/mm.sup.2.
<5> The method according to any one of <1> to <4>, wherein the filter has a hole density of 300 holes/mm.sup.2 to 5000 holes/mm.sup.2.
<6> The method according to any one of <1> to <5>, wherein the filter has a hole density of 500 holes/mm.sup.2 to 4000 holes/mm.sup.2.
<7> The method according to any one of <1> to <6>, wherein the filter has a hole density of 800 holes/mm.sup.2 to 4000 holes/mm.sup.2.
<8> The method according to any one of <1> to <7>, wherein the holes are in the form of an ellipse with a minor axis diameter of 4.0 μm to 10 μm and a major axis diameter of 1.1 times to 3 times as long as the minor axis diameter, or the holes have a shape that is in contact with the ellipse on at least two points including both ends of the major axis of the ellipse.
<9> The method according to any one of <1> to <8>, wherein an area of a hole in the filter is 15 μm.sup.2 to 250 μm.sup.2.
<10> The method according to any one of <1> to <9>, wherein the area of a hole in the filter is 20 μm.sup.2 to 100 μm.sup.2.
<11> The method according to any one of <1> to <10>, wherein the area of a hole in the filter is 25 μm.sup.2 to 80 μm.sup.2.
<12> The method according to any one of <1> to <11>, wherein the holes are in the form of an ellipse with a minor axis diameter of 5.0 μm to 8 μm and a major axis diameter of 1.1 times to 3 times as long as the minor axis diameter, or the holes have a shape that is in contact with the ellipse on at least two points including both ends of the major axis of the ellipse.
<13> The method according to any one of <1> to <12>, comprising:
[0094] separating or detecting rare cells by filtering the blood sample so that the filter capacity with respect to the holes in the filter is defined by “Total volume of blood sample to be processed (nl)=Hole number (holes)×10 to Hole number (holes)×170” or “Total volume of blood sample to be processed (nl)=Total hole area (μm.sup.2)×0.2 (nl/μm.sup.2) to Total hole area (μm.sup.2)×3.4 (nl/μm.sup.2)”, expressed in terms of blood.
<14> The method according to any one of <1> to <13>, comprising:
[0095] separating or detecting rare cells by processing the blood sample in an amount indicated by “Total volume of blood sample to be processed (nl)” using a filter in which a number of the holes is defined by “Hole number (holes)=Total volume of blood sample to be processed (nl)/170 to Total volume of blood sample to be processed (nl)/10” or a total area of the holes is defined by “Total hole area (μm.sup.2)=Total volume of blood sample to be processed (nl)/3.4 (nl/μm.sup.2) to Total volume of blood sample to be processed (nl)/0.2 (nl/μm.sup.2).”
<15> The method according to any one of <1> to <14>, comprising:
[0096] separating or detecting rare cells by filtering the blood sample so that the filter capacity per hole of the filter is 10 nl/hole to 108 nl/hole expressed in terms of blood.
<16> The method according to any one of <1> to <15>, wherein the blood sample is filtered in a volume of 0.1 μl/hole or less expressed in terms of blood with respect to a hole of the filter.
<17> The method according to any one of <1> to <16>, wherein the blood sample is filtered in a volume of 0.06 μl/hole or less expressed in terms of blood with respect to a hole of the filter.
<18> The method according to any one of <1> to <17>, wherein a number of the holes in the filter is more than 10000 holes.
<19> The method according to any one of <1> to <18>, wherein as a fluid transfer condition for filtration, pressure is set so that blood is transferred at a flow velocity of 5 μm/min to 600 μm/min per hole.
<20> The method according to any one of <1> to <19>, wherein as a fluid transfer condition for filtration, pressure is set so that blood is transferred at 0.05 nl/min to 30 nl/min per hole.
<21> The method according to any one of <1> to <20>, wherein the blood sample is transferred so that a pressure difference between an upper surface and a lower surface of the filter during filtration is 4 Pa to 110 Pa.
<22> The method according to any one of <1> to <21>, wherein the filter is made of at least one selected from the group consisting of glass, plastic, metal, and a combination thereof.
<23> The method according to any one of <1> to <22>, wherein the rare cells are selected from the group consisting of cancer cells, circulating tumor cells, vascular endothelial cells, vascular endothelial precursor cells, cancer stem cells, epithelial cells, hematopoietic stem cells, mesenchymal stem cells, embryonal cells, and a combination thereof.
<24> A method for analyzing rare cells in a blood sample comprising:
[0097] separating or detecting rare cells by the method according to any one of <1> to <23>, and then
[0098] analyzing the rare cells by a method including kinetic observation or activity measurement of the rare cells.
<25> A filter used in the method according to any one of <1> to <24>, comprising holes with a hole density of at least 200 holes/mm.sup.2 to 40000 holes/mm.sup.2,
[0099] wherein the holes are in the form of an ellipse with a minor axis diameter of 3.0 μm to15 μm and a major axis diameter of 1.2 times to 3 times as long as the minor axis diameter, or the holes have a shape that is in contact with the ellipse on at least two points including both ends of the major axis of the ellipse.
<26> A filter used in the method according to any one of <1> to <24>, comprising more than 10000 holes,
[0100] wherein the filter allows 1 ml to 5 ml of blood to be processed.
<27> A filter used in the method according to any one of <1> to <24>, comprising 29000 holes or more,
[0101] wherein the filter allows 5 ml to 10 ml of blood to be processed.
<28> A filter used in the method according to any one of <1> to <24>, comprising 60000 holes or more,
[0102] wherein the filter allows more than 10 ml of blood to be processed.
<29> A device for capturing rare cells that captures rare cells in a sample, comprising:
[0103] an inlet;
[0104] an outlet; and
[0105] a flow path connecting the inlet and the outlet,
[0106] wherein a separation portion that includes the filter according to any one of
<25> to <28> and a filter holder is provided in a position corresponding to a part of the flow path.
EXAMPLES
[0107] Hereinafter, the present disclosure will be described in more detail by way of examples, which are for illustrative purposes only, but the present disclosure is not limited to the examples.
[0108] Using the filters and the fluid transfer conditions shown in Table 1 and
TABLE-US-00001 TABLE 1 Filter Filtration conditions Pressure P.sub.1 Pressure P.sub.1 in entire Blood flow in entire system rate per system (inlet-outlet) Pitch Opening hole in (inlet-outlet) during Major axis Hole between Hole ratio per Filtration Total transfer of during blood- washing- diameter/ area centers density area area hole 8 ml blood filtration filtration Shape Minor axis μm.sup.2 of holes hole/mm.sup.2 (%) Thickness Material mm.sup.2 number nl/min kPa kPa Circle 8 × 8 50 19 × 14 3759 19 5 μm nickel 20 73816 4~7 nl/min 1.3 kPa-0.1 0.4 kPa-0.1 (metal) Ellipse 9.8 × 6.5 50 19 × 14 3759 19 5 μm nickel 20 73816 4~7 nl/min 1.3 kPa-0.1 0.4 kPa-0.1 (metal) Ellipse 12.8 × 5 50 19 × 14 3759 19 5 μm nickel 20 73816 4~7 nl/min 1.3 kPa-0.1 0.4 kPa-0.1 (metal) Ellipse 8 × 6.5 41 19 × 14 3759 15 5 μm nickel 20 73816 4~7 nl/min 1.3 kPa-0.1 0.4 kPa-0.1 (metal) Circle 6.5 × 6.5 33 19 × 14 3759 12 5 μm nickel 20 73778 4~7 nl/min 1.3 kPa-0.1 0.4 kPa-0.1 (metal) Ellipse 8 × 5 31 19 × 14 3759 12 5 μm nickel 20 73778 4~7 nl/min 1.3 kPa-0.1 0.4 kPa-0.1 (metal) Circle 5 × 5 20 random 3534 8 8 μm PC (resin) 20 69390 clogging 1.3 kPa-0.1 0.4 kPa-0.1 Circle 4 × 4 13 19 × 19 2770 3 5 μm nickel 20 54390 clogging 1.3 kPa-0.1 0.4 kPa-0.1 (metal)
[0109] Filters were produced by designing the pitch in the major axis direction and the pitch in the minor axis direction of various holes. Apolycarbonate track-etched membrane with a hole diameter of ϕ5 μm or ϕ8 μm (manufactured by GE Healthcare Japan Corporation) was used as a plastic filter. The hole diameter of the filters can be measured, e.g., by a pore size distribution evaluation apparatus using a bubble point method or a mercury intrusion method, or by a known measurement method with an optical microscope such as a fluorescence microscope, a laser microscope, or an electron microscope. Specifically, the number of holes was directly counted or the number of holes per area was determined with a microscope, and then the filtration area to be used was calculated.
Method for Preparing Cancer Cell
[0110] According to the ordinary method, human mammary epithelial cancer cells (cell line name: MCF-7), human colon adenocarcinoma cells (cell line name: SW620), human prostate cancer cells (cell line name: PC3-9), human alveolar epithelial cancer cells (cell line name: NCI-H358), human gastric cancer cells (cell line name: MKN-7), and sarcoma (HT-1080) were cultured in petri dishes. After removal of the supernatant, each culture medium was washed with PBS (-), and the supernatant was further removed. Then, the cells were treated with trypsin (Invitrogen) at 37° C. for 3 minutes, suspended in a culture medium including serum, and placed in a 15 ml centrifuge tube. The cells were centrifuged with a centrifuge (CR20F: Hitachi, Ltd.) to remove the supernatant. Subsequently, the cells were resuspended in a culture medium including serum and collected. A human gastric cancer cell line (cell line name: SNU-1) and a human colon adenocarcinoma cell line (cell line name: SNU-C1), both of which were suspended, were placed in 15 ml centrifuge tubes without the trypsin treatment. Some of human colon adenocarcinoma cells (cell line name: Colo320DM) adhered to suspended cells. Therefore, suspended cells were placed in a 15 ml centrifuge tube, while the cells adhered to the suspended cells were treated with trypsin in the same manner as the other adherent cells, and then placed in the 15 ml centrifuge tube. The cells were centrifuged, suspended in a culture medium including serum, and collected.
Preparation of Cell Count
[0111] As cancer cell samples, SNU-1, MKN-7, MCF-7, SW620, Colo320DM, SNU-C1, PC3-9, NCI-H358, and HT-1080, which were derived from gastric cancer cells, breast cancer cells, colon cancer cells, prostate cancer cells, lung cancer cells, and sarcoma and were previously stained, were prepared to have any number of cells such as 0.5×10.sup.5 cells/ml or 1×10.sup.5 cells/ml. The SNU-1 cells were used as a model of deformable cells, since they easily passed through 8 μm holes compared to the other cell suspensions. The SW620 cells were used as a model of small cells, since they were the smallest in the above cells. The deformability of the cells was evaluated in the following manner. Using a track-etched membrane (polycarbonate (PC), circular hole: ϕ8 μm, filtration size: ϕ10 mm), a cell suspension containing an excessive number of the cells, which was more than the number of the holes in the membrane, was supplied and clogged the membrane. Then, a negative pressure was created in an airtight bottle that was located under the filter and communicated with the discharge flow path. At this time, when the clogging was eliminated and the cell suspension started to flow swiftly, the cells with relatively low pressure were selected as highly deformable cells (see Table 2).
TABLE-US-00002 TABLE 2 SNU-1 SW620 HT-1080 NCI-H358 PC3-9 MCF-7 Pressure (kPa) at the time of 0.6-1 35 2-2.2 6.5-6.7 3.5-3.8 5-8 eliminating clogging of filter with cells
Capturing Process of Rare Cell
[0112] Cell separation experiments were conducted using a device for capturing rare cells shown in
[0113] The device includes an inlet 1 for supplying a sample, a cleaning fluid, a stain solution, or the like to a filter, an outlet 2, and a flow path 3 connecting the inlet 1 and the outlet 2. A separation portion that includes a filter 4 and a filter holder 5 for holding the filter 4 is provided in a position corresponding to a part of the flow path 3. Specifically, the filter 4 is disposed on a base 6, an O ring 7 is put on the upper surface of the filter 4, and a cover 8 is placed to fix the separation portion, thus producing a filter device including holes, as shown in Table 1. In this example, a plurality of filters having a filtration area of 5 mm.sup.2 to 80 mm.sup.2 were used. A connection portion and a three way stopcock that allows the flow of a fluid to be switched were attached to the upper portion of the filter device, and the flow path was formed by a Safeed extension tube (manufactured by Terumo Corporation). The inlet 1 was located at the end of the flow path 3 that was opposite to the filter 4, and a pressure means 9 was provided between the inlet 1 and the filter 4 (as a mechanism that can transfer a fluid at constant pressure or a mechanism that can transfer a fluid at a constant flow rate). The fluid transfer conditions were set by adjusting the filtration pressure or using a syringe pump. The discharge flow path was formed by coupling the Safeed extension tube to a tube with an inner diameter of 2 mm, and the outlet 2 was located at the end of this tube.
Setting Transfer Condition
[0114] The flow path was filled with PBS (-) (composition: 1 L distilled water containing 8000 mg of sodium chloride, 200 mg of potassium chloride, 1150 mg of sodium monohydrogen phosphate (anhydrous), and 200 mg of potassium dihydrogen phosphate (anhydrous)). By adjusting the pressure or using a syringe pump, blood was filtered at 30 nl/min or less (i.e., 600 μm/min or less) per hole of the filter. After the separation of the cancer cells from the blood, the flow path was washed with PBS (-) at about 1000 μl/min (14 nl/min per hole). Table 7 shows the relationship between the flow rate and each of ϕ8 μm holes and ϕ9.8×6.5 μm holes. Based on the results in Table 7, the flow rate per hole was set to be 4 nl/min to 7 nl/min when the filtration pressure in the entire system was 1.3 kPa±0.1 or the amount of blood per hole was 108 nl. Such filtration conditions were regarded as basic conditions. A comparison between the filters was performed under the basic conditions at the same pressure. The conditions were appropriately set in accordance with the number of the holes.
Performing Sample Processing
[0115] Apart of blood (white blood cell count: 3000 to 10000 cells/μl) that had been drawn into a blood collection tube (EDTA-2K) was placed in a syringe, and then 10 μl of cancer cell suspension with a desired concentration was added to the blood in the syringe. Subsequently, the residual blood was added and mixed, so that a blood sample was prepared. When this blood sample was supplied to the inlet of the device for capturing rare cells, the pressure means applied pressure shown in the following Table 4 so as to meet the fluid transfer conditions for each hole of the filter, and thus the blood sample was filtered. After completion of the filtration, the device was washed with PBS (-) and the three way stopcock and the connection portion, which were connected to the portion above the separation portion, were slowly removed. Then, a glass slide was gradually put on the filter and an observation plane was formed. This was placed in a fluorescence microscope, and fluorescent stained cancer cells remaining on the filter were enumerated. The cancer cells recovered by the processing of this example were able to be cultured.
[0116] In the above processing, the cancer cells were stained in the following manner. The prepared cancer cells were collected from the culture medium, and then centrifuged with a centrifuge (CR20F: Hitachi, Ltd.) at 1500 rpm at room temperature (24° C.) for 3 minutes. After removal of the supernatant, PBS (-) was added to suspend the cells. The cells suspended in PBS (-) were fluorescent stained. In this case, CellTracker (Invitrogen) was used as a fluorescent dye. The CellTracker (Invitrogen) is a reagent that can diffuse through the cell membrane of live cells, and reacts with an intracellular substance and is converted into a fluorescent substance.
[0117] The CellTracker was dissolved in DMSO to 10 mM and used so that the final concentration in the reaction was 0.5 μM to 0.25 μM. The CellTracker was allowed to react in PBS (-) for 30 to 40 minutes. The cancer cells were appropriately stained with CellTracers that emit green fluorescence (CellTracker Green CMFDA), orange fluorescence (CellTracker Orange CMRA), and blue fluorescence (CellTracker Blue CMF2HC).
[0118] The recovery rate of cancer cells was calculated in the following manner. A cancer cell suspension was added to blood and filtered. Then, the fluorescent stained cancer cells on the filter surface were counted. On the other hand, the cancer cell suspension was added to a microplate well in the same amount as that added to the blood, and the number of the cancer cells was counted by a fluorescence microscope. The capture rate was calculated, where the number of the cells in the microplate well was used as a denominator and the number of the cells remaining on the filter was used as a numerator.
Cell Staining and Activity on Filter
[0119] PC3 cells were processed in the above manner except that the PC3 cells were not previously stained with the CellTracker. After the PC3 cells were separated from blood, 1 mM 5-aminolevulinic acid (ALA) prepared with PBS was added from the inlet and allowed to react with the PC3 cells. Then, fluorescent staining was performed by the conversion and accumulation of protoporphyrin IX due to ALA metabolism using the activity of the enzyme in the PC cells on the filter. In addition, white blood cells were stained with an antibody against CD45 or the like, and hoechst (which can stain even live cells) was used to stain nuclei to be examined. Consequently, 81% of the PC3 cells were observed to emit fluorescence derived from the protoporphyrin IX, and the activity was confirmed. In the cancer cells, the protoporphyrin IX (red fluorescent substance) may be produced immediately before it is metabolized into heme, since metabolism is suppressed in the synthetic and metabolic pathway of heme that is used in the citric acid cycle. With this method, it is known that 5-aminolevulinic acid (ALA), which is a precursor of protoporphyrin IX, is added to cancer cells so that the protoporphyrin IX (red fluorescent substance) is accumulated, and thus the fluorescent stained cancer cells can be specifically detected.
[0120] Tables 3 to 9 show the results of the capturing process of rare cells.
[0121] Tables 3 to 7 confirm that when a blood sample is processed with the filter capacity of the present disclosure by controlling the hole shape, a predetermined hole area, the amount of blood per hole, and the blood flow rate per hole, instead of simply reducing the hole diameter, small cells and deformable cells can be captured alive. Moreover, as can be seen from Table 8, it is surprising that the effect of capturing the deformable cells can be achieved no matter how the filtration area, the hole density, the number of the holes, and the amount of the blood sample are different.
[0122] Table 8 shows data indicating the differences in the number of the holes, the hole density, the filtration area, and the amount of blood to be processed.
Example 1
[0123] In the following examples, using filters having the same number of holes and the same filtration area, blood samples were processed in a volume of 14 nl per hole (the total volume of the blood sample to be processed: 1 ml). Consequently, the recovery rate of small cells that would pass through 10 μm holes was generally high as long as the holes were smaller than the cells regardless of the hole shape. On the other hand, the recovery rate of deformable cancer cells was low when the holes were small. Table 3 and
TABLE-US-00003 TABLE 3 <Small cancer cells> Amount Total Hole of blood volume of area per hole blood sample SW620 μm.sup.2 14 nl processed ϕ 8 50 92% 1 ml ϕ 9.8 × 6.5 50 95% 1 ml ϕ 12.7 × 5 50 103% 1 ml ϕ 8 41 89% 1 ml ϕ 6.5 33 100% 1 ml ϕ 8 × 5 31 91% 1 ml ϕ 5 20 84% 0.971 ml ϕ 4 13 clogging 0.776 ml <Highly deformable cells> Amount Total Hole of blood volume of area per hole blood sample SNU-1 μm.sup.2 14 nl processed ϕ 8 50 91% 1 ml ϕ 9.8 × 6.5 50 95% 1 ml ϕ 12.7 × 5 50 101% 1 ml ϕ 8 × 6.5 41 83% 1 ml ϕ 6.5 33 56% 1 ml ϕ 8 × 5 31 41% 1 ml ϕ 5 20 57% 0.971 ml ϕ 4 13 clogging 0.776 ml
Example 2
[0124] The amount of a blood sample to be processed through each of the filters was considered. If a large amount of blood can be processed with the same filtration area, it is possible to reduce the filtration area of the filter to be used, to suppress the bulk of the filtration portion in the device, and to ensure cost effectiveness, as compared to the conventional examples. Tables 4 and 5 show average data of the capture rates of SW620 cells and SNU-1 cells, respectively. The average data are also plotted in
TABLE-US-00004 TABLE 4 <Small cancer cells> Amount of blood per hole (nl) 14 54 108 163 339 SW620 Capture rate ϕ 8 92% 86% 86% 86% 66% ϕ 9.8 × 6.5 96% 99% 91% 89% 77% ϕ 12.7 × 5 103% 102% 90% 84% 67% ϕ 8 × 6.5 89% 92% 96% 89% ϕ 6.5 100% 93% 101% ϕ 8 × 5 91% Total volume 1 ml 4 ml 8 ml 12 ml 25 ml of blood sample processed ϕ 5 84% — clogging — — Total volume 0.971 ml 6.9 ml of blood sample processed ϕ 4 clogging — clogging — — Total volume of blood 0.776 ml 6 ml sample processed
[0125] Since the SW620 cells were little affected by the amount of blood, the capture capabilities were maintained. However, the capture rate of the SNU-1 cells, which were relatively deformable cancer cells, was reduced with an increase in the amount of blood (see Table 5). If blood is filtered by relying solely on the cell size without taking into account the amount of the blood sample to be processed per hole, the capture capabilities cannot be obtained from blood containing deformable cancer cells. The present inventor found that there is an appropriate amount of the blood sample to be processed with respect to the number of the holes, even if no clogging (blockage) occurs, when the rare cells are to be captured. Moreover, the present inventor found that a high capture rate of deformable cells can be achieved by appropriately setting the number of the holes and the amount of the blood sample to be processed per hole in the range of 10 nl to 170 nl in view of the capture rate and the amount of the blood sample to be processed. The capture rates for each of the filters with different holes are plotted in
TABLE-US-00005 TABLE 5 <Highly deformable cells> Amount of blood per hole (nl) 14 54 108 163 339 SNU-1 Capture rate ϕ 8 91% 77% 72% 52% 28% ϕ 9.8 × 6.5 93% 81% 71% 57% 25% ϕ 12.7 × 5 95% 76% 57% 21% 22% ϕ 8 × 6.5 83% 74% 61% 39% ϕ 6.5 56% 46% 29% ϕ 8 × 5 41% 47% 31% Total volume 1 ml 4 ml 8 ml 12 ml 25 m1 of blood sample processed ϕ 5 57% — clogging — — Total volume 0.971 ml 6.9 ml of blood sample processed ϕ 4 clogging — clogging — — Total volume 0.776 ml 6 ml of blood sample processed
TABLE-US-00006 TABLE 6 Amount of blood per hole (nl) COLO320 54 nl 108 nl Type of filter Capture rate ϕ 8 100% 84% ϕ 9.8 × 6.5 93% 77% ϕ 12.7 × 5 101% 64% ϕ 8 × 6.5 97% 77% ϕ 6.5 73% 37% ϕ 8 × 5 43% 58% Total volume 4 ml 8 ml of blood sample processed Amount of blood per hole (nl) <ϕ 12.7 × 5 filter> 14 nl 54 nl 108 nl 163 nl Type of cell Capture rate SNU-1 101% 76% 52% 22% Colo320DM 101% 64% SW620 102% 97% 87% SNU-C1 117% 107% 87% Total volume 1 ml 4 ml 8 ml 12 ml of blood sample processed
Example 3
[0126] Next, data of the capture rates of cells when the filtration pressure was varied during filtration will be shown in the following. In general, high pressure would make it easy for cells to pass through the holes of a filter, and thus degrade the capture capabilities, and low pressure would make it difficult for cells to pass through the holes of a filter, and thus be expected to improve the capture rate. However, as shown in Table 7-1, when the amount of blood per hole was 108 nl, the capture rate was not stable and reduced particularly on the lower pressure side of the ϕ8 filter and the ϕ9.8×6.5 filter. It is considered that since the filtration time was too long, the cells passed through the filters due to their viscoelasticity.
[0127] Next, data obtained by varying the filtration pressure with respect to 108 nl of a blood sample to be processed per hole (the total volume of the blood sample to be processed: 8 ml) and 14 nl of a blood sample to be processed per hole (the total volume of the blood sample to be processed: 1 ml) will be shown in the following. As shown in Table 7-2, even under a high flow rate and high pressure, the cells can be captured by reducing the volume of the blood sample to be processed per hole. The fluid transfer conditions may be appropriately determined in accordance with the volume of the blood sample to be processed per hole. In other words, when the fluid transfer conditions are appropriately set so that the flow rate per hole is 30 nl/min or less or the pressure difference is 3.7 kPa or less (or ΔP.sub.2 is 100 Pa or less) in accordance with 14 nl to 108 nl of the blood sample to be processed per hole, a high capture rate of cells can be achieved. For example, when the volume of the blood sample to be processed per hole is 14 nl, 1 ml of blood can be filtered for about 1 minute with a pressure difference of 1.3 kPa in the entire system (i.e., the flow rate per hole is 14 nl/min to 17 nl/min). Thus, high capture rates of both small cancer cells and deformable cancer cells can be achieved. By appropriately setting the volume of the blood sample to be processed per hole, the rare cells can be recovered from a larger volume of the blood sample in a shorter time compared to the conventional method (in which 1 ml of a blood sample is processed for about 5 minutes, and 8 ml of a blood sample is processed for about 40 minutes). Since blood deteriorates over time, the faster it can be processed, the better. Thus, fresh rare cells can be acquired and have a favorable effect on analysis.
[0128] Table 7 and
TABLE-US-00007 TABLE 7-1 Capture conditions for 108 nl per hole PBS (—) flow rate μl/sec Blood sample Average Pressure difference between Pressure difference Total hole Average Total hole Average flow upper surface and lower in entire system number average flow rate number average flow rate velocity per surface of filter ΔP.sub.1 flow rate per hole flow rate per hole hole Filtration time ΔP.sub.2(true circile ϕ 8 μm) (kPa) μl/min nl/min μl/min nl/min μm/min of 8 ml blood ΔP.sub.2 = Q*8 ηL/(πd.sup.4*N.sub.0) within 3.7 ± 0.1 7500 102 1600~2000 22~27 440~540 4~5 min ΔP.sub.2 = 80~100 Pa within 2.6 ± 0.1 6000 81 1100~1300 15~18 300~360 6~7 min ΔP.sub.2 = 50~70 Pa within 1.3 ± 0.1 3000 41 300~500 4~7 80~120 15~25 min ΔP.sub.2 = 16~30 Pa within 0.4 ± 0.1 1000 14 88~130 1~2 20~40 60~90 min ΔP.sub.2 = 4~7 Pa Capture rate of (1)Φ8 and Φ9.8 × 6.5 (108 nl per hole) Pressure difference in entire system Average flow Capture rate SD ΔP.sub.1 rate per hole SW620 SNU1 SW620 SNU1 (kPa) nl/min ϕ 8 ϕ 9.8 × 6.5 ϕ 8 ϕ 9.8 × 6.5 ϕ 8 ϕ 9.8 × 6.5 ϕ 8 ϕ 9.8 × 6.5 within 3.7 ± 0.1 22~27 66% 63% 30% 21% within 2.6 ± 0.1 15~18 77% 77% 47% 52% 5% 15% 14% 3% within 1.3 ± 0.1 4~7 86% 96% 72% 71% 6% 6% 13% 17% within 0.4 ± 0.1 1~2 75% 93% 63% 72% 12% 12% 25% 19% ※Q: total hole number average flow rate, a: radius, L: flow path length, η: blood viscosrly, N.sub.0: hole number (all are expressed in SI unit)
TABLE-US-00008 TABLE 7-2 Comparison of 14 nl and 108 nl per φ 9.8 × 6.5 hole Capture rate Pressure difference in SW620 SNU1 entire system φ 9.8 × 6.5 φ 9.8 × 6.5 φ 9.8 × 6.5 φ 9.8 × 6.5 (inlet-outlet) ΔP.sub.1(kPa) (14 nl) (108 nl) (14 nl) (108 nl) within 2.6 ± 0.1 100% 72% 80% 50% within 1.3 ± 0.1 96% 96% 88% 71% within 0.4 ± 0.1 95% 93% 96% 72%
[0129] Tables 7-1 and 7-2 confirm that, under the fluid transfer conditions of the present disclosure, when the flow rate is set so that the pressure difference in the entire system is 3.7 kPa or less, or the pressure difference between the upper surface and the lower surface of the filter is 100 Pa or less, or the flow rate per hole is 30 nl/min or less in accordance with the amount of blood per hole, i.e., 14 nl to 108 nl of blood per hole, a high capture rate can be achieved.
[0130] Using filters that differ in the filtration area, the number of holes, and the hole density, under the filtration conditions shown in Table 8-1, when the volume of the blood sample to be processed per hole was 14 nl to 108 nl, the capture rate of the SNU-1 cells was compared among the filters. Table 8-2 shows the comparative data. The comparative data are also plotted in
TABLE-US-00009 TABLE 8-1 Filter Pitch Major axis between Hole Filtration conditions diameter/ Hole centers of density Opening Filtration Minor axis area holes hole/mm.sup.2 Thickness ratio per area Shape diameter μm.sup.2 μm kPa μm area (%) Material mm.sup.2 Ellipse 9.8 × 6.5 50 19 × 14 3759 5 19 nickel 79 (metal) Circle 8 50 Random 890 8 4 PC (resin) 79 Circle 8 50 19 × 14 3759 5 19 nickel 20 (metal) Ellipse 12.7 × 5 50 19 × 14 3759 5 19 nickel 20 (metal) Ellipse 9.8 × 6.5 50 19 × 14 3759 5 19 nickel 20 (metal) Ellipse 9.8 × 6.5 50 19 × 19 2770 5 14 nickel 20 (metal) Ellipse 9.8 × 6.5 50 19 × 14 3759 5 19 nickel 5 (metal) Filtration conditions Pessure difference Pessure difference ΔP.sub.1 in entire ΔP.sub.1 in entire system system Blood flow rate (inlet-outlet) (inlet-outlet) Filter Total hole per hole in during blood during washing Shape number blood transfer filtration kPa filtration kPa Ellipse 295262 1~3 nl/min 1.3 kPa ± 0.1 0.4 kPa ± 0.1 Circle 69900 4~7 nl/min 1.3 kPa ± 0.1 0.4 kPa ± 0.1 Circle 73816 4~7 nl/min 1.3 kPa ± 0.1 0.4 kPa ± 0.1 Ellipse 73816 4~7 nl/min 1.3 kPa ± 0.1 0.4 kPa ± 0.1 Ellipse 73816 4~7 nl/min 1.3 kPa ± 0.1 0.4 kPa ± 0.1 Ellipse 54390 4~7 nl/min 0.7 kPa ± 0.1 0.4 kPa ± 0.1 Ellipse 19960 5 nl/min Flow rate in entire Flow rate in entire syringe system 100 μl/min system 200 μl/min pump fluid syringe pump syringe pump transfer fluid transfer fluid transfer
TABLE-US-00010 TABLE 8-2 295,262 69,900 73,816 73,816 54,390 19,960 holes/filtration holes/filtration size 73,816 holes/filtration holes/filtration holes/filtration holes/filtration Amount of size ϕ 10 mm ϕ 10 mm holes/filtration size ϕ 5 mm size ϕ 5 mm size ϕ 5 mm size ϕ 2.6 mm blood per (metal filter track-etched size ϕ 5 mm (metal filter (metal filter (metal filter (metal filter hole (n1) ϕ 9.8 × 6.5) membrane (PC ϕ 8) (metal filter ϕ 8) ϕ 9.8 × 6.5) ϕ 12.7 × 5) ϕ 9.8 × 6.5) ϕ 9.8 × 6.5) 14 — — 91% 93% 95% 91% — 28 88% 91% 96% 86% — 95% 91% 54 92% 85% 77% 81% 76% 74% — 108 — 62% 72% 71% 57% 62% — 339 — — 28% 25% 22% — —
[0131] Table 9 and
TABLE-US-00011 TABLE 9 Capture rate of cells for 108 nl of blood sample per hole Suspended cell Adherent cell Gastric Suspended, partially adhered Gastric Lung Breast Prostate cancer Colon cancer cancer cancer Sarcoma cancer cancer Size at peak 17 19 14 13 19 18 17 19 21 position in size distribution (μm) Type of cell SNU-1 SNU-C1 Colo320DM SW620 MKN-7 NCI-H358 HT-1080 MCF-7 PC-3 ϕ 9.8 × 6.5 71% 103% 75% 89% 89% 101% 86% 90% 97% SD 17% 6% 11% 8% 4% 5% 3% 5% 8%
[0132] Table 9 and
[0133] The present disclosure is useful in the field of recovery, measurement, and analysis of rare cells in blood, e.g., in the academic field of medicine and pharmacy and/or in the medical field of treatment, diagnosis, or the like.
[0134] The invention may be embodied in other forms without departing from the spirit or essential characteristics thereof. The embodiments disclosed in this application are to be considered in all respects as illustrative and not limiting. The scope of the invention is indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are intended to be embraced therein.
[0135] The embodiments have been described, hereinabove. It will be apparent to those skilled in the art that the above methods and apparatuses may incorporate changes and modifications without departing from the general scope of the present disclosure. It is intended to include all such modifications and alterations insofar as they come within the scope of the appended claims or the equivalents thereof. Although the description above contains much specificity, this should not be construed as limiting the scope of the disclosure, but as merely providing illustrations of some of the embodiments of the present disclosure. Various other embodiments and ramifications are possible within its scope.
[0136] Furthermore, notwithstanding that the numerical ranges and parameters setting forth the broad scope of the disclosure are approximations, the numerical values set forth in the specific examples are reported as precisely as possible. Any numerical value, however, inherently contain certain errors necessarily resulting from the standard deviation found in their respective testing measurements.