Patent Application
20240377310
The present invention is in the field of biomedical research and clinical diagnostics. In particular, the invention relates to a method for detecting cell aggregates of biological cells using a quantitative phase-contrast microscope, to a device for detecting cell aggregates of biological cells, to a method for detecting cellular and/or molecular biological objects using a quantitative phase-contrast microscope and to a device for detecting cellular and/or molecular biological objects.
Conventional blood counts determine parameters such as the numbers of red blood cells, platelets, white blood cells and subtypes thereof in a blood sample of a patient, which may be used for diagnosing many different diseases. Recent studies suggest that aggregates of blood cells such as leukocyte-platelet aggregates and leukocyte aggregates may also serve as useful biomarkers for a variety of pathological conditions such as cardiovascular diseases and bacterial or viral infections, see e.g. M. Finsterbusch et al., Platelets. 2018 November; 29(7):677-685, J. G. Burel et al., eLife 2019; 8:e46045, and Michelson et al, Circulation. 2001; 104:1533-1537.
A reliable detection of blood cell aggregates, however, is challenging since the aggregates are fragile objects and may disintegrate easily. This prevents an analysis using traditional methods for performing blood counts such as Mie scattering or fluorescence-based flow cytometry, which may require a complex and time-consuming sample preparation involving a selective lysis of erythrocytes, a staining of cell constituents and/or a fluorescent labeling. The sample preparation as well as the measurement itself may affect cell morphology and may lead to a disintegration of cell aggregates, e.g. due to mechanical forces exerted thereon during centrifugation or flow cytometry at high flow rates (typically 1-10 m/s) required for sufficient statistics on individual cells.
Digital holographic microscopy uses interference between an imaging beam and a reference beam to obtain phase as well as amplitude information of light transmitted by a sample and for example allows for reconstructing a quantitative phase shift image of the sample, see e.g. EP 1 524 491 A1 and EP 2 357 539 A1. In recent years, digital holographic microscopes have successfully been employed for biomedical applications such as live cell imaging. Phase shift images of cells may be used to reliably identify cell types based on the analysis of morphological parameters and/or using machine learning classifiers. In combination with microfluidic systems, this for example allows for performing high-throughput label-free blood sample analyses such as blood counts, see e.g. US 2019/0195774 A1, facilitating the diagnosis of diseases like malaria, leukemia, and myeloproliferative neoplasms, see for example M. Ugele et al., Adv. Sci. 1800761 (2018), WO 2019/063548 A1 and M. Ugele et al., Proc. SPIE 11060, Optical Methods for Inspection, Characterization, and Imaging of Biomaterials IV, 110600V (2019). Furthermore, digital holographic microscopy has already been used to perform a quantitative analysis of platelet aggregates adhering to a surface, see e.g. WO 2016/170180 A1. The currently known methods, however, either do not allow for a reliable detection of cell aggregates or are not suitable for performing automated high-throughput analyses in a clinical setting. Moreover, these methods only provide limited information regarding the composition of the cell aggregates and may thus not be suitable for obtaining clinically relevant information, which may e.g. require an analysis of single platelets as well as large platelet-platelet aggregates at the same time.
It is thus an object of the invention to provide a method that allows for a fast and reliable detection of biological cells and cell aggregates and is suitable for performing automated high-throughput analyses in a clinical setting.
This object is met by a method for detecting cell aggregates of biological cells using a quantitative phase-contrast microscope according to claim 1 and a device for detecting cell aggregates of biological cells according to claim 19. Embodiments thereof are detailed in the corresponding dependent claims.
According to a first aspect of the invention, a method for detecting cell aggregates of biological cells using a quantitative phase-contrast microscope is provided. The method according to the first aspect of the invention comprises preparing a suspension comprising biological cells from a sample and a viscoelastic fluid. The viscoelastic fluid comprises a shear-thinning polymer having a molecular weight between 2 MDa and 10 MDa, wherein a mass fraction of the shear-thinning polymer in the suspension is less than 0.2%. The method further comprises generating a flow of the suspension along a microfluidic channel to viscoelastically focus cell aggregates in the suspension in a focal plane of the quantitative phase-contrast microscope. One or more phase shift images of the biological cells in the suspension are taken using the quantitative phase-contrast microscope and cell aggregates in the one or more phase shift images are identified.
The method may for example be performed using a device for detecting cell aggregates of biological cells according to any one of the embodiments according to the first aspect of the invention described below. The sample may be a sample extracted from a patient, in particular a liquid sample such as a blood sample. Accordingly, the biological cells may for example be or comprise blood cells, e.g. red blood cells (erythrocytes), white blood cells (leukocytes) and/or platelets (thrombocytes), and/or rare cells such as circulating tumor cells and/or circulating endothelial cells.
The suspension may be prepared by adding the viscoelastic fluid to the sample or to cells extracted from the sample or vice-versa. The viscoelastic fluid is a fluid that has both viscous and elastic properties, i.e. may exhibit properties of a viscous fluid as well as properties of an elastic solid. The viscoelastic fluid may be a non-Newtonian fluid exhibiting a viscosity that depends on the applied shear rate, in particular a shear-thinning fluid exhibiting a viscosity that decreases with the applied shear rate. The viscoelastic properties of the viscoelastic fluid may result from the shear-thinning polymer contained therein at least in part. The viscoelastic fluid may for example be an aqueous solution comprising the shear-thinning polymer, e.g. a solution consisting of water or phosphate buffered saline and the shear-thinning polymer.
The viscoelastic properties of the viscoelastic fluid may lead to viscoelastic focusing of objects such as cells and/or cell aggregates contained in the suspension when generating a flow of the suspension. The objects in the flow may for example migrate towards regions in which the shear rate is low, e.g. a center region of the flow of the suspension, in which the suspension has the highest flow velocity. In the microfluidic channel, this may for example be in the vicinity of a central plane between two opposing sidewalls of the microfluidic channel or in the vicinity of a centerline between two pairs of opposing sidewalls of the microfluidic channel.
The viscoelastic focusing of cells and/or cell aggregates within the flow of the suspension is adapted such that cells and/or cell aggregates in the suspension are focused in the focal plane of the quantitative phase-contrast microscope. For example, the viscoelastic fluid may lead to viscoelastic focusing of cells and/or cell aggregates at the center of the flow of the suspension, e.g. in the vicinity of the central plane or the centerline of the microfluidic channel. In some embodiments, the central plane and/or the centerline of the microfluidic channel may lie in the focal plane of the quantitative phase-contrast microscope. The cell aggregates in the suspension may be focused such that centers of the cell aggregates are confined to within a confinement range in a direction perpendicular to the focal plane of the microscope. For example, at least 90% of the cell aggregates, in one example at least 95% of the cell aggregates may be confined to within the confinement range. Preferably, the confinement range is less than 20 μm, in some examples less than 10 μm, in one example less than 5 μm. The confinement range may in particular be equal to or less than two times a depth of field of the microscope, in one example equal to or less than the depth of field of the microscope. In a preferred embodiment, single cells are also focused in the focal plane of the microscope, e.g. such that at least 80% of single cells, in some examples at least 90% of single cells, in one example at least 95% of single cells are confined to within the confinement range.
The viscoelastic focusing with a shear-thinning polymer having a molecular weight between 2 MDa and 10 MDa at a mass fraction in the suspension of less than 0.2% may allow for a reliable focusing of cell aggregates as well as single cells while reducing mechanical stress on the cell aggregates and preventing a polymer-induced aggregation of cells. Focusing cell aggregates and in particular a combination of cell aggregates and single cells is challenging due to the different sizes that the cell aggregates and the cells may have. A size of the cell aggregates may e.g. range from 1 μm to 50 μm, while a size of the cells may range from 1 μm to 20 μm. Human platelets for example typically have a size between 1 μm and 3 μm, while white blood cells typically have a size between 7 μm and 15 μm. Forces acting on objects in a viscoelastic fluid may depend on the size of the object such that objects of different sizes may be focused at different points/locations or objects of a certain size may not be focused at all. At the same time, shear stress within a fluid flow may act on the cell aggregates and may break cell aggregates apart, in particular at higher flow velocities. This may limit a range of flow velocities that can be used, making it even more difficult to focus cell aggregates. Furthermore, shear-thinning polymers may affect cell morphology, see e.g. J. Gonzalez-Molina et al., Sci Rep 9, 8505 (2019), and may even induce the formation of “artificial” cell aggregates in some cases, e.g. for red blood cells as described in J. K. Armstrong et al., Biophysical Journal 87 (2004), 4259-4270. Surprisingly, the present inventors have found that adding a shear-thinning polymer with a molecular weight between 2 MDa and 10 MDa at a mass fraction of less than 0.2% induces a viscoelasticity in the suspension that enables sufficient confinement of cell aggregates in the suspension using viscoelastic focusing at reduced flow velocities to prevent disintegration of cell aggregates while at the same time not inducing a formation of “artificial” cell aggregates. Thereby, the present invention allows for studying cell aggregates and in particular aggregates of blood cells by quantitative phase-contrast microscopy without the need for cell fixation and red blood cell lysis. Furthermore, aggregates testing can be performed with standard blood draw procedures using conventional blood collection tubes.
For detecting cell aggregates, the method further comprises taking one or more phase shift images of the biological cells in the suspension using the quantitative phase-contrast microscope. The quantitative phase-contrast microscope may for example be a ptychographic imaging device or a digital holographic microscope, e.g. as detailed below for the device according to the first aspect of the invention. Taking the one or more phase shift images may for example comprise capturing a sequence of images of a measurement volume along the microfluidic channel while the suspension flows along said microfluidic channel. As used herein, a phase shift image may encode a phase shift of light at one or more wavelengths as a function of position, e.g. a phase shift of light reflected off or propagating through an imaging sample such as the flow of the suspension as a function of the position in the imaging sample. In a preferential setting and contrary to conventional flow cytometry with serial cell measurements, multiple cells and/or cell aggregates are imaged in parallel to compensate for a reduced throughput due to the lower flow rates.
The one or more phase shift images may be analyzed to identify cell aggregates therein, e.g. to distinguish cell aggregates from single cells. Cell aggregates may for example be identified based on one or more morphological parameters pertaining to their size, shape and/or structure, for example a mean diameter (equivalent diameter) and/or a phase shift (optical height), e.g. by defining one or more thresholds for the respective parameters. Additionally or alternatively, cell aggregates may also be identified using classical and/or artificial intelligence-based (AI-based) computer vision techniques, e.g. using a neural network-based classifier. Identifying cell aggregates in the one or more phase shift images may in particular comprise determining a total number or fraction of cell aggregates in the one or more phase shift images, wherein the fraction of cell aggregates may e.g. be the ratio of the total number of cell aggregates to the total number of single cells and cell aggregates.
In a preferred embodiment, identifying the cell aggregates in the one or more phase shift images comprises determining a number of cells in the respective cell aggregate and/or a cell type of some or all of the cells in the respective cell aggregate. This may for example comprise performing an image segmentation on a portion of a phase shift image associated with the cell aggregate, e.g. a region-of-interest containing only the cell aggregate but no other single cells or cell aggregates, to identify constituents of the cell aggregate. The image segmentation may for example be performed using a thresholding algorithm, e.g. based on one or more thresholds for the phase shift to assign portions of the phase shift image to a respective constituent, and/or using a watershed algorithm, e.g. by interpreting the phase shift as a topographic height and identifying “basins” within the resulting topographic map as constituents of the cell aggregate. Additionally or alternatively, the image segmentation may also be performed using an edge-based method such as geodesic active contours, see e.g. P. Marquez-Neila, L. Baumela, and L. Alvarez, “A morphological approach to curvaturebased evolution of curves and surfaces”, In: IEEE Transactions on Pattern Analysis and Machine Intelligence 36.1 (2013), pp. 2-17, a region-based method such as the Chan-Vese algorithm, see e.g. T. Chan and L. Vese, “An active contour model without edges”. In: International Conference on Scale-Space Theories in Computer Vision, Springer, 1999, pp. 141-151, and/or a graph-based method such as the Felzenszwalb algorithm, see e.g. P. F. Felzenszwalb and D. P. Huttenlocher, “Efficient graph-based image segmentation”, In: International journal of computer vision 59.2 (2004), pp. 167-181. Additionally or alternatively, the image segmentation may also be performed using AI-based computer vision techniques, e.g. using a neural network such as the U-Net, see e.g. O. Ronneberger, P. Fischer, and T. Brox, “U-Net: Convolutional networks for biomedical image segmentation”, In: International Conference on Medical image computing and computerassisted intervention, Springer, 2015, pp. 234-241, the Mask R-CNN, see e.g. K. He, G. Gkioxari, P. Dollár, and R. Girshick, “Mask RCNN”, In: Proceedings of the IEEE international conference on computer vision, 2017, pp. 2961-2969, and/or a pulse-coupled neural network, see e.g. M. Chen, X. Yu, and Y. Liu, “PCNN: Deep convolutional networks for short-term traffic congestion prediction”, In: IEEE Transactions on Intelligent Transportation Systems 19.11 (2018), pp. 3550-3559. Depending on the depth-of-field of the quantitative phase-contrast microscope, aggregate analysis may be adapted to the needs on lateral resolution (e.g. highest for platelets) versus the aggregate height information depending on wavelength and numerical aperture. Histograms of aggregate size distribution and/or cellular composition can be plotted. e.g. in cases of assays using activating substances or detailed analysis of patient samples.
The method may further comprise determining one or more morphological parameters for some or all of the constituents of the cell aggregate, e.g. from the segmented image. The one or more morphological parameters may for example comprise a minimum diameter, a mean diameter, a maximum diameter, a circumference, an aspect ratio, a minimum phase shift, a mean phase shift, a maximum phase shift, a variation or standard deviation of the phase shift and/or a correlation length of the phase shift. The one or more morphological parameters may in particular comprise one or more texture features such as an entropy or homogeneity, an energy, one or more features extracted from a co-occurrence matrix such as a gray level co-occurrence matrix (GLCM) and/or one or more Haralick features. In some embodiments, the one or more morphological parameters may be extracted using AI-based computer vision techniques, e.g. using a neural network for feature extraction.
The method may also comprise determining the cell type of some or all of the constituents of the cell aggregate, e.g. based on the one or more morphological parameters. The cell type may for example be determined using one or more thresholds for the respective morphological parameters. Additionally or alternatively, the cell type may be determined using a regression analysis, a linear discriminant analysis, a decision tree classification a random forest classification, a support vector machine (SVM), a quadratic discriminant analysis, a K-means clustering, a logistic regression and/or a naïve Bayes classifier. In some embodiments, the cell type may additionally or alternatively be determined using AI-based computer vision techniques, e.g. using a neural network-based classifier.
In a preferred embodiment, the method may also comprise identifying single cells in the one or more phase shift images, e.g. similar to the identification of cell aggregates described above. Single cells and cell aggregates may for example be distinguished based on one or more morphological parameters pertaining to their size, shape and/or structure, and/or may be distinguished using classical and/or AI-based computer vision techniques. The method may further comprise determining a cell type of the single cells, e.g. similar to the determination of the cell type for constituents of a cell aggregate described above.
The shear-thinning polymer may have a molecular weight between 3 MDa and 6 MDa in some embodiments, preferably a molecular weight between 3.5 MDa and 4.5 MDa, in one example a molecular weight of 4.0 MDa, with Da being the unified atomic mass unit (u). Increasing the molecular weight of the polymer may facilitate viscoelastic focusing of objects, but at the same time may also lead to an increase in the rate of polymer-induced formation of “artificial” cell aggregates as well as to increased mechanical stress on the cell aggregates due to interactions with the polymers in the suspension. The inventors have found that using a shear-thinning polymer with a molecular weight in these ranges is particularly advantageous for achieving sufficient confinement of both cell aggregates and single cells in the suspension even at low flow velocities and without inducing a formation of “artificial” cell aggregates. Preferably, the shear-thinning polymer is a linear polymer, e.g. a polymer comprising a single unbranched linear chain.
The mass fraction of the shear-thinning polymer in the suspension may be between 0.03% and 0.12% in some embodiments, preferably between 0.04% and 0.06%, in one example 0.05%. The mass fraction of a given constituent of the suspension may for example be defined as the ratio of the combined mass of the respective constituent in the suspension and the total mass of the suspension, i.e. the sum of the combined masses of each of the constituents of the suspension. Increasing the mass fraction of the shear-thinning polymer may facilitate viscoelastic focusing of objects, but at the same time may also lead to an increase in the rate of polymer-induced formation of “artificial” cell aggregates as well as to increased mechanical stress on the cell aggregates due to interactions with the polymers in the suspension. The inventors have found that using a shear-thinning polymer with a mass fraction in these ranges is particularly advantageous for achieving sufficient confinement of both cell aggregates and single cells in the suspension even at low flow velocities and without inducing a formation of cell aggregates.
Preferably, the shear-thinning polymer is a water soluble polymer. The shear-thinning polymer may for example be selected from the group consisting of poly(ethylene oxide) (PEO), poly(vinyl pyrrolidone) (PVP), hyaluronic acid (HA) and polyacrylamide (PAA). Preferably, the shear-thinning polymer is poly(ethylene oxide) or poly(vinyl pyrrolidone). In one example, the shear-thinning polymer is 4 MDa water soluble linear polymer PEO at a mass fraction of 0.05% in the suspension. In another example, the shear-thinning polymer is 4 MDa water soluble linear polymer PEO at a mass fraction of 0.2% in the suspension. In some embodiments, the viscoelastic fluid may comprise one or more additional shear-thinning polymers, wherein the additional shear thinning polymers may e.g. comprise a polymer of the same type, but with a different molecular weight (e.g. PEO with molecular weights distributed within a range of 3 MDa to 6 MDa) and/or a polymer of a different type with the same or a different molecular weight (e.g. PVP with a molecular weight of 2 MDa in addition to PEO with a molecular weight of 4 MDa). In such embodiments, a combined mass fraction of all shear-thinning polymers in the suspension may be less than 0.2%, preferably between 0.03% and 0.12%, in one example between 0.04% and 0.06%, and/or a molecular weight of some or all of the shear-thinning polymers may be within the range of 2 MDa and 10 MDa, preferably between 3 MDa to 6 MDa, in one example between 3.5 MDa and 4.5 MDa.
In a preferred embodiment, a flow velocity of the suspension along the microfluidic channel is chosen such that a shear stress within the flow is below 50 Pa, preferably below 10 Pa, in one example below 5 Pa. A shear rate within the flow of the suspension in the microfluidic channel, e.g. a gradient of the flow velocity, may for example be smaller than 10,000 s−1, in some examples smaller than 5,000 s−1, in one example smaller than 2,000 s−1. A flow velocity of the suspension may for example be between 1 mm/s and 1.0 m/s, preferably between 1 mm/s and 250 mm/s, in some examples between 5 mm/s and 100 mm/s, in one example between 8 mm/s and 64 mm/s.
In some embodiments, a length from an inlet of the microfluidic channel to a focal point of the quantitative phase-contrast microscope is between 30 mm and 60 mm, preferably between 35 mm and 50 mm. The inlet of the microfluidic channel may for example be an input port for providing the suspension to the microfluidic channel or a junction between two or more channels merging into the microfluidic channel, e.g. a hydrodynamic focusing junction. In some examples, the microfluidic channel may be straight or substantially straight, wherein the inlet of the microfluidic channel may for example also be a curved channel portion at the beginning of the microfluidic channel. Choosing a length of the microfluidic channel within the aforementioned ranges may for example facilitate a stable (viscoelastic) focusing even of smaller objects such as single cells and in particular platelets.
Preferably, a height of the flow of the suspension in a direction perpendicular to the focal plane of the quantitative phase-contrast microscope is between 30 μm and 100 μm, in some examples between 30 μm and 70 μm, in one example between 40 μm and 60 μm, e.g. 50 μm. The height of the flow of the suspension may for example be measured at the focal point of the quantitative phase-contrast microscope and may e.g. be the distance between sidewalls of the microfluidic channel that are in contact with the flow of the suspension, between interfaces between the flow of the suspension and one or more additional flows surrounding the flow of the suspension in the microfluidic channel or a combination thereof. The height of the flow of the suspension may for example be determined by a height of the microfluidic channel, which may e.g. be within the aforementioned ranges. Additionally or alternatively, the height of the flow of the suspension may also be controlled by hydrodynamic focusing by generating one or more sheath flows along the microfluidic channel, e.g. as described below. This may allow for generating a flow of the suspension having a height in the aforementioned ranges even in a microfluidic channel having a larger height. Choosing a height of the flow of the suspension within the aforementioned ranges may for example be advantageous to ensure a stable viscoelastic focusing of the cells and/or cell aggregates within the suspension.
In a preferred embodiment, the method further comprises generating two or more sheath flows along the microfluidic channel to hydrodynamically focus the flow of the suspension such that cell aggregates in the suspension are focused in a focal plane of the quantitative phase-contrast microscope. In other words, in addition to the viscoelastic focusing of cells and/or cell aggregates within the flow of the suspension, the flow of the suspension itself may be focused hydrodynamically by generating two or more sheath flows along the microfluidic channel. The sheath flows may for example be generated such that the sheath flows flow between the flow of the suspension and a respective sidewall of the microfluidic channel, e.g. such that the flow of the suspension is sandwiched between a pair of sheath flows flowing along opposing sidefaces of the microfluidic channel. The sheath flows may be configured to confine the flow of the suspension in one or more directions, e.g. a direction perpendicular to the focal plane of the microscope and/or a direction parallel to the focal plane of the microscope. Hydrodynamically focusing the flow of the suspension may for example allow for reducing the height of the flow of the suspension in the microfluidic channel and/or preventing objects within the flow of the suspension such as single cells and/or cell aggregates from coming in contact with sidewalls of the microfluidic channel. Hydrodynamic focusing may for example be used if the height of the microfluidic channel is larger than 100 μm, preferably if the height of the microfluidic channel is larger than 70 μm, in some examples if the height of the microfluidic channel is larger than 60 μm, in one example if the height of the microfluidic channel is larger than 50 μm. Additionally or alternatively, hydrodynamic focusing may also be used to control a position of the flow of the suspension within the microfluidic channel, e.g. to displace or offset the flow of the suspension from a center plane or a centerline of the microfluidic channel.
In combination, the viscoelastic focusing of cells and/or cell aggregates within the flow of the suspension and the hydrodynamic focusing of the flow of the suspension may be adapted such that cells and/or cell aggregates in the suspension are focused in the focal plane of the quantitative phase-contrast microscope. For example, the flow velocities and/or the flow rates of the two or more sheath flows may be chosen such that the flow of the suspension is hydrodynamically focused in a center region of the microfluidic channel and the viscoelastic fluid may lead to viscoelastic focusing of cells and/or cell aggregates at the center of the flow of the suspension, e.g. in the vicinity of the central plane or the centerline of the microfluidic channel. In some embodiments, the central plane and/or the centerline of the microfluidic channel may lie in the focal plane of the quantitative phase-contrast microscope. In other embodiments, cells and/or cell aggregates in the suspension may be focused in a different region of the microfluidic channel, e.g. in the vicinity of a plane or line that is offset from the central plane or the centerline of the microfluidic channel, for example by choosing asymmetric flow velocities or flow rates for the two or more sheath flows.
In some embodiments, some or all of the two or more sheath flows may comprise a viscoelastic fluid, in particular a viscoelastic fluid comprising the same shear-thinning polymer as the suspension. A mass fraction of the shear-thinning polymer in the respective sheath flows may for example be equal to or smaller than the mass fraction of the shear-thinning polymer in the suspension.
In some embodiments, the flow of the suspension is hydrodynamically focused by generating a pair of lateral sheath flows sandwiching the flow of the suspension in a first direction and a pair of vertical sheath flows sandwiching the flow of the suspension in a second direction perpendicular to the first direction, e.g. to confine the flow of the suspension along both the first and second directions. Each of the lateral sheath flows may for example flow between the flow of the suspension and a respective vertical sidewall of the microfluidic channel. Each of the vertical sheath flows may for example flow between the flow of the suspension and a bottom and top wall of the microfluidic channel, respectively. In other examples, the flow of the suspension may be hydrodynamically focused using only the pair of lateral sheath flows or only the pair of vertical sheath flows, e.g. to confine the flow of the suspension along the first or along the second direction by hydrodynamic focusing, whereas confinement of the cells and/or of the cell aggregates along the other direction may for example be achieved by viscoelastic focusing. The second direction may for example be perpendicular to the focal plane of the quantitative phase-contrast microscope and may e.g. be parallel to an imaging axis of the quantitative phase-contrast microscope.
In a preferred embodiment, the sample is a whole blood sample, e.g. unmodified blood extracted from a patient, or a blood fraction sample, e.g. a sample comprising one or more components of a whole blood sample such as blood plasma or fractions thereof, a buffy coat comprising leukocytes and platelets, and/or erythrocytes. In other examples, the sample may also be a sample of a different body fluid or a tissue sample extracted from a patient, in particular a tissue sample dissolved into single cells and/or into cell aggregates. The sample may e.g. be or comprise a human sample such as urine, effusions, lavage or sputum to perform cell aggregate tests thereon. In some examples, one or more coagulation-inhibiting substances, such as ethylenediamine tetra-acetic acid (EDTA), heparin or citrate, may be added to the whole blood sample or the blood fraction sample, respectively, to prevent coagulation.
Identifying cell aggregates in the one or more phase shift images may comprise identifying cell aggregates comprising or consisting of one or more predefined types of blood cells in the one or more phase shift images. Identifying cell aggregates in the one or more phase shift images may in particular comprise identifying platelet aggregates, i.e. aggregates consisting of platelets, leukocyte-platelet aggregates, i.e. aggregates consisting of one or more platelets and one or more leukocytes, and/or leukocyte aggregates, i.e. aggregates consisting of leukocytes. This may for example comprise identifying constituents of the cell aggregates in the one or more phase shift images, determining one or more morphological parameters for some or all of the constituents of the respective cell aggregates and determining the cell type of the respective constituents as described above. Additionally or alternatively, identifying cell aggregates in the one or more phase shift images may also comprise identifying cell aggregates comprising tumor cells, in particular cell aggregates comprising tumor cells and blood cells, for example cell aggregates consisting of tumor cells with platelets and/or leukocytes.
Additionally or alternatively, the method may also comprise determining a number of cell aggregates comprising at least a predefined number of cells of one or more certain types of cells, e.g. aggregates comprising at least a first number of cells of a first type or aggregates comprising at least the first number of cells of the first type and at least a second number of cells of a second type. In a preferred embodiment, the method comprises determining a number of leukocyte-platelet aggregates comprising at least a predefined number of leukocytes, in particular two or more leukocytes or three or more leukocytes. Additionally or alternatively, the method may for example also comprise determining a number of leukocyte aggregates and leukocyte-platelet aggregates comprising two or more leukocytes and/or of leukocyte-platelet aggregates comprising two or more leukocytes and two or more platelets. The method may also comprise determining a number of cell aggregates consisting of a predefined number of cells of one or more certain types of cells, e.g. aggregates consisting of a first number of cells of a first type, aggregates consisting of the first number of cells of the first type and a second number of cells of a second type, and/or aggregates consisting of the first number of cells of the first type and at least the second number of cells of the second type, for example a number of leukocyte-platelet aggregates consisting of two leukocytes and one or more platelets or a number of leukocyte-platelet aggregates consisting of three leukocytes and one or more platelets. Additionally or alternatively, the method may further comprise determining a number of cell aggregates comprising at least a predefined number of cells, e.g. three or more cells, in one example four or more cells. The method may in particular comprise determining a number of leukocyte aggregates and/or of leukocyte-platelet aggregates comprising three or more cells. The presence of cell aggregates of a certain composition, e.g. having at least a given number of cells, may be associated with a certain medical condition or disease. For example, the presence of leukocyte-platelet aggregates comprising two or more leukocytes and in particular the presence of leukocyte-platelet aggregates comprising three or more leukocytes may indicate an infection. High concentrations of platelet-platelet aggregates may for example indicate complications of Covid-19 patients or patients with cardiovascular diseases.
In some embodiments, preparing the suspension comprises diluting the whole blood sample or the blood fraction sample, respectively, by a factor between 1:10 and 1:1000, preferably between 1:50 and 1:200, in one example between 1:80 and 1:120. Diluting whole blood or a blood fraction by a factor in these ranges may ensure that the cells and the cell aggregates in the suspension are sufficiently sparse such that the respective objects can easily be distinguished in the phase shift images while also providing a sufficiently high density of objects to allow for an analysis of a large number of objects.
In a preferred embodiment, preparing the suspension does not comprise a lysis of erythrocytes, a sphering of platelets and/or of erythrocytes and/or a labelling or staining of cells. For example, preparing the suspension may only comprise adding the viscoelastic fluid to a blood sample, in particular a whole blood sample or a blood fraction sample, e.g. to dilute the blood sample by a factor within the ranges given above. This may enable a rapid processing of samples, e.g. to prevent spontaneous disintegration of cell aggregates from the sample. Furthermore, the aforementioned sample preparation procedures may affect cell morphology and/or may lead to the disintegration of cell aggregates from the sample. In some examples, one or more coagulation-inhibiting substances such as ethylenediamine tetra-acetic acid (EDTA) may be contained in the viscoelastic fluid and/or may be added to the blood sample.
In some embodiments, the method may further comprise adding a platelet- and/or leukocyte-activating substance to induce platelet aggregation and/or leukocyte-platelet aggregation, e.g. to study coagulation processes, or leukocyte function, e.g. to study morphological changes and aggregate formation. An increase or a decrease in a rate and/or in an extent of coagulation may for example be associated with certain pathological conditions. Samples from patients with coronary artery disease may e.g. exhibit stronger coagulation than samples from healthy individuals, see M. I. Furman et al., J. Am. Coll. Cardiol. Vol. 31, No. 3, 292-296 (2009). The platelet-activating substance may for example be selected from the group consisting of adenosine diphosphate (ADP), thrombin receptor activating peptide (TRAP), epinephrin, thrombin, Von-Willebrand-factor and C-reactive protein (CRP). Vice versa, inhibitors, such as Aspirin or Clopidogrel, can be added. Alternatively or in addition to platelet activation, leukocyte activating substances can be added, such as cytokines. Furthermore, drugs can be added, such as a checkpoint inhibitor, one or more antibody drug conjugates and/or one or more bispecific T-cell engaging antibody constructs, e.g. to study cell aggregation behavior and inhibition. In one example, the method may also comprise adding a substance that induces a formation of aggregates comprising tumor cells in combination with leukocytes and/or platelets.
According to the first aspect, the invention further provides a device for detecting cell aggregates of biological cells using a method according to any one of the embodiments according to the first aspect of the invention described herein. The device comprises a mount that is configured to receive a microfluidic system comprising a measurement volume. The device further comprises a microscope configured to take phase shift images of biological cells in the measurement volume. The device also comprises a microfluidics unit configured to receive a sample fluid comprising biological cells from a sample and a viscoelastic fluid, wherein the viscoelastic fluid comprises a shear-thinning polymer having a molecular weight between 2 MDa and 10 MDa and wherein a mass fraction of the shear-thinning polymer in the sample fluid is less than 0.2%. The microfluidics unit is configured to generate a flow of the sample fluid through the measurement volume to viscoelastically focus cell aggregates in the sample fluid flow in a focal plane of the microscope The device further comprises a controller that is configured to identify cell aggregates in a phase shift image of the sample fluid flow obtained from the microscope.
The mount may be configured to hold the microfluidic system, e.g. at a fixed reference position relative to the microscope. Preferably, the mount is configured to position the microfluidic system relative to the microscope, e.g. to move the microfluidic system along one or more directions and/or to tilt the microfluidic system around one or more axes. In some examples, the mount may further comprise one or more fluid connectors for interfacing ports of the microfluidic system, e.g. one or more input ports and an output port of the microfluidic system. The measurement volume of the microfluidic system may e.g. be a microfluidic channel or a portion thereof. In some embodiments, the device may comprise the microfluidic system.
The microscope is a quantitative phase-contrast microscope, e.g. a digital holographic microscope or a ptychographic imaging device, that is configured to take phase shift images, i.e. images that encode a phase shift of light at one or more wavelengths as a function of position. Preferably, the microscope is configured to determine an absolute value of the phase shift. In other examples, the microscope may only be configured to determine the phase shift modulo 27. The microscope may for example be configured to obtain the phase shift through interference of light, e.g. between a probe or an imaging beam and a reference beam. In other examples, the microscope may be a ptychographic imaging device that is configured to perform ptychographic imaging without a reference beam, e.g. by recording interference patterns without a reference phase. The microscope may be configured to take one or more interference images and to reconstruct a phase shift image from the one or interference images.
In a preferred embodiment, the microscope is a digital holographic microscope, which is configured to take phase shift images as well as amplitude or intensity images, wherein an intensity image may encode an intensity of light as a function of position, e.g. an intensity of light reflected off or transmitted through an imaging sample such as the sample fluid flow as a function of the position in the imaging sample. The digital holographic microscope may for example be configured to interfere an image of the imaging sample, e.g. an imaging beam of light transmitted through the imaging sample, with a reference beam, wherein the reference beam may pass through the imaging sample or may not pass through the imaging sample. The digital holographic microscope may be configured to extract or reconstruct the phase shift and intensity images from one or more interference images, e.g. by reconstructing a wave front of light transmitted through or reflected off the imaging sample. The digital holographic microscope may be an on-axis digital holographic microscope, in which the imaging beam and the reference beam propagate along the same axis when interfering. Preferably, the digital holographic microscope is an off-axis digital holographic microscope, in which the imaging beam and the reference beam interfere under an angle and which may be configured to extract a phase shift image from a single interference image of the imaging sample. Such digital holographic microscopes are for example known from EP 1 524 491 A1 and EP 2 357 539 A1.
The microfluidics unit may for example comprise a reservoir for receiving the sample fluid and/or may comprise a slot for receiving a reservoir containing the sample fluid, e.g. a test or sample tube. The microfluidics unit may further comprise one or more fluid connectors for interfacing ports of the microfluidic system and/or ports of the mount. The microfluidics unit may further comprise one or more pressure sources such as pumps and/or one or more valves for generating the sample fluid flow and/or additional flows such as one or more sheath fluid flows.
The controller may be implemented in hardware, software or a combination thereof. The controller may for example comprise a processing device and a memory storing instructions for execution by the processing device to provide the functionality described herein. The controller may for example be configured to read-out one or more phase shift images from the microscope and to identify cell aggregates therein, e.g. as described above for the method according to the first aspect of the invention. The controller may further be configured to control some or all of the other components of the device, in particular the microfluidics unit and/or a sample preparation unit as described below. Preferably, the controller is configured to execute some or all of the steps of the method for detecting cell aggregates of biological cells according to one of the embodiments according to the first aspect of the invention described herein.
In a preferred embodiment, the microfluidic system further comprises a hydrodynamic focusing junction in fluid communication with the measurement volume. The hydrodynamic focusing junction may be configured to generate two or more sheath flows surrounding a sample fluid flow to hydrodynamically focus the sample fluid flow in the measurement volume. The microfluidics unit may be configured to provide a sheath fluid to the hydrodynamic focusing junction to hydrodynamically focus the sample fluid flow in the measurement volume such that cell aggregates in the sample fluid flow are focused in the focal plane of the microscope. At the hydrodynamic focusing junction, a sample channel, which may e.g. be configured to guide the sample fluid flow to the measurement volume, may intersect with two or more sheath flow channels, each of which may e.g. be configured to guide a respective one of the sheath flows to the measurement volume such that the corresponding sheath flow flows between the sample fluid flow and a respective wall of the measurement volume.
In a preferred embodiment, the device further comprises a sample preparation unit configured to provide the viscoelastic fluid comprising the shear-thinning polymer with a molecular weight between 2 MDa and 10 MDa to prepare the sample fluid comprising biological cells from the sample and the viscoelastic fluid, wherein the mass fraction of the shear-thinning polymer in the sample fluid is less than 0.2%. The sample preparation unit may for example comprise a reservoir for receiving the sample or a part thereof, e.g. a whole blood sample or a blood fraction sample, or a slot for receiving a reservoir containing the sample. The sample preparation unit may further comprise a reservoir for receiving the viscoelastic fluid and may be configured to mix the viscoelastic fluid and the sample or a part thereof, e.g. by adding the viscoelastic fluid to the sample or vice versa. In some examples, the sample preparation unit and the microfluidics unit may be integrated into a single unit.
Preferably, the sample preparation unit is configured to adjust a mass fraction of the shear-thinning polymer in the sample fluid, for example at least within a range between 0.03% and 0.12%, in some examples at least within a range between 0% and 0.2%. The sample fluid may for example be configured to adjust an amount of viscoelastic fluid added to the sample fluid, a concentration of the shear-thinning polymer in the viscoelastic fluid and/or an amount of another fluid, e.g. water or an aqueous solution, added to the sample fluid in addition to the viscoelastic fluid.
Additionally or alternatively, the sample preparation unit is configured to dilute the sample fluid by a factor between 1:10 and 1:1000, preferably between 1:50 and 1:200. Diluting the sample fluid by a given factor may e.g. refer to adding the viscoelastic fluid and/or other fluids to the sample or a part thereof in such amounts that the sample or a part thereof makes up the respective fraction of the sample fluid by mass or volume. In a preferred embodiment, the sample preparation unit is further configured to adjust the dilution factor, e.g. within the aforementioned ranges.
In some embodiments, the sample preparation unit is further configured to add one or more platelet-activating substances and/or one or more leukocyte-activating substances to the sample fluid and/or to the sheath fluid. The sample preparation unit may for example comprise a respective reservoir for each of the one or more platelet-activating substances and/or for each of the one or more leukocyte-activating substances and may be configured to add a predefined amount of one or more of these substances to the sample fluid and/or to the sheath fluid.
Preferably, the microfluidics unit is configured to control a flow velocity of the sample fluid flow in the measurement volume, wherein the flow velocity of the sample fluid flow may for example be between 1 mm/s and 1.0 m/s, preferably between 1 mm/s and 250 mm/s, in some examples between 5 mm/s and 100 mm/s, in one example between 8 mm/s and 64 mm/s. The microfluidics unit may for example be configured to adjust a flow rate of the sample fluid provided to the hydrodynamic focusing junction. The microfluidics unit may further be configured to adjust a flow rate of the sheath fluid provided to the hydrodynamic focusing junction, preferably such that a flow velocity or a flow rate of each of the two or more sheath flows can be controlled individually, e.g. to move or adjust a focusing region to which the sample fluid flow is confined by the sheath flows.
In a preferred embodiment, the controller is configured to execute some or all of the steps for analyzing a phase shift image described above for the method according to the first aspect of the invention. In particular, the controller may be configured to determine a number of cells in a cell aggregate identified in the phase shift image and/or a cell type of some or all of the cells in the cell aggregate identified in the phase shift image, e.g. as described above. The controller may be configured to identify platelet aggregates and/or leukocyte-platelet aggregates in the phase shift image. Preferably, the controller is further configured to determine a number of leukocyte-platelet aggregates comprising two or more leukocytes and/or a number of cell aggregates comprising three or more cells in the phase shift image, e.g. as described above.
In the following, a detailed description of the invention and exemplary embodiments thereof is given with reference to the figures. The figures show schematic illustrations of
The device 100 comprises a mount 106 that is configured to receive a microfluidic system 200, wherein the microfluidic system 200 comprises a measurement volume 202 and a hydrodynamic focusing junction 204. The measurement volume 202 and the hydrodynamic focusing junction 204 may for example be arranged in a substrate comprising one or more layers, each of which may e.g. comprise or consist of glass, plastic (in particular a transparent thermoplastic such as polymethyl methacrylate, PMMA), metal or a combination thereof.
The measurement volume 202 may for example be a microfluidic channel or a portion thereof and may for example have a width between 50 μm and 1000 μm in a direction of view of
At the hydrodynamic focusing junction 204, a sample channel 206A intersects with a plurality of sheath flow channels 206B such that a sample fluid flow 208A entering the measurement volume 202 from the sample channel 206A can be surrounded by two or more sheath flows 208B that flow between the sample fluid flow 208A and a respective wall of the measurement volume 202. In the example of
In some embodiments, the microfluidic system 200 may not comprise the hydrodynamic focusing junction 204, e.g. in cases in which cell aggregates 102A, 102B and single cells 104A, 104B in the sample fluid flow 208A are only focused by viscoelastic focusing. In such examples, there may be no sheath flows in the measurement volume 204 and the sample fluid flow 208A may extend over the entire height of the measurement volume 202, e.g. from a bottom wall comprising the illumination window 202B to a top wall comprising the detection window 202A. To provide sufficient confinement of the cell aggregates 102A, 102B and single cells 104A, 104B in the sample fluid flow 208A, a measurement volume 202 having a smaller height may e.g. be used in these cases. The height of the measurement volume 202 may for example be between 30 μm and 70 μm, in some examples between 40 μm and 60 μm, e.g. 50 μm.
The mount 106 is configured to hold the microfluidic system 200 at a fixed reference position relative to the microscope 108. The mount 106 may also be configured to position the microfluidic system 200 relative to the microscope 108, e.g. to move the microfluidic system 200 along one or more directions and/or to tilt the microfluidic system 200 around one or more axes, e.g. to align a central plane or a centerline of the measurement volume 202 with the focal plane of the microscope 108.
The microscope 108 of the device 100 is a quantitative phase-contrast microscope, in particular a digital holographic microscope that is configured to take phase shift images and intensity images of the sample fluid flow 208A in the measurement volume 202 through the detection window 202A. For this, the microscope 108 comprises an imaging system with an objective 110, a holographic imaging system 112 and an imaging lens 114, wherein the imaging system is configured to image the focal plane of the microscope 108 onto a camera 116, which may for example be a CCD or CMOS camera. The microscope 108 also comprises an illumination source 118 that is configured to illuminate the measurement volume 202 through the illumination window 202B. The microscope 108 further comprises a microscope controller 108A for controlling the holographic imaging system 112, the camera 116 and/or the illumination source 118.
The objective 110 may for example be a high-NA objective having a numerical aperture larger than 0.4, in some examples larger than 0.5. A depth of field of the objective 110 may be smaller than 10 μm, preferably smaller than 5 μm, in one example between 2 μm and 3 μm, wherein the depth of field may e.g. be defined as a minimum Rayleigh length of a laser beam focused by the objective 110, for example at a wavelength of 1064 nm. This may allow for precise focusing on objects such as the cell aggregates 102A, 102B in the measurement volume 202 and may provide sufficient spatial resolution to resolve morphological features of individual cells.
The holographic imaging system 112 is configured to create an interference image on the camera 116, e.g. by interfering an imaging beam with a reference beam on the camera 116. The imaging beam may for example be a beam that passes through the measurement volume 202 and propagates from the focal plane of the microscope 108 to the camera 116 along a first optical path through the holographic imaging system 112. The reference beam may for example be a beam propagating to the camera 116 along a second optical path through the holographic imaging system 112. In some examples, the reference beam may be split from the imaging beam, e.g. using a beam splitter or a diffraction grating, i.e. the reference beam may also have passed through the measurement volume 202 and may propagate to the camera 116 from the focal plane of the microscope 108 along the second optical path. In other examples, the reference beam may not have passed through the measurement volume 202 and may e.g. be split from the imaging beam in front of the measurement volume 202.
The digital holographic microscope 108 may be an on-axis digital holographic microscope, in which the imaging beam and the reference beam propagate along the same axis when interfering, i.e. interfere at an angle of 0°. The microscope controller 108A may for example be configured to extract or reconstruct a phase shift image as well as an intensity image of the sample fluid flow 208A in the measurement volume 202 from a plurality of interference images, e.g. by varying a phase offset between the reference and imaging beams using the holographic imaging system 112. Preferably, the microscope 108 is an off-axis digital holographic microscope, in which the imaging beam and the reference beam interfere under an angle. In this case, the microscope controller 108A may be configured to extract or reconstruct the phase shift image as well as the intensity image of the sample fluid flow 208A from a single interference image. Alternatively, the microscope 108 may be a ptychographic imaging device and analysis of ptychographic images may be performed to classify cell aggregates.
The illumination source 118 is configured to illuminate the measurement volume 202 by spatially and/or temporally coherent light, wherein a coherence length of the illumination light may for example be larger than a field of view of the microscope 108 and a coherence time of the illumination light may for example be larger than a time delay between the image and reference beams, i.e. such that an interference pattern can be observed on the camera 116. The illumination source 108 may for example comprise a laser or a light-emitting diode and may be configured to emit monochromatic light, e.g. at a wavelength between 500 nm and 1100 nm.
The microscope controller 108A may be implemented in hardware, software or a combination thereof. The microscope controller 108A may be configured to provide the phase shift and intensity images to another device, in particular to the controller 124 of the device 100, and may be controlled by another device such as the controller 124. In some examples, the microscope controller 108A or a part thereof may be integrated into the controller 124. In addition to reconstructing the phase shift and intensity images, the microscope controller 108A may also be configured to analyze the phase shift and/or intensity images, e.g. as detailed below for method 300.
The device 100 further comprises a microfluidics unit 120 and a sample preparation unit 122, which in some embodiments may be integrated into a single unit. The sample preparation unit 122 is configured to receive a liquid sample comprising biological cells, e.g. in a test tube. The liquid sample may in particular be a whole blood sample, which comprises single cells such as platelets 104A, white blood cells (leukocytes) 104B as well as red blood cells (not shown). The whole blood sample may further comprise aggregates of blood cells such as platelet aggregates 102A consisting of a plurality of platelets, leukocyte-platelet aggregates 102B consisting of one or more platelets and one or more leukocytes and/or leukocyte aggregates (not shown) consisting of a plurality of leukocytes. In other examples, the liquid sample may also be a blood fraction sample, e.g. a sample comprising one or more components of a whole blood sample. The sample preparation unit 122 is configured to prepare a sample fluid comprising biological cells from the sample by adding a viscoelastic fluid to the sample, e.g. as described below for method 300.
The microfluidics unit 120 is configured to receive the sample fluid from the sample preparation unit 122 and is configured to generate the sample fluid flow 208A through the measurement volume 202 by providing the sample fluid to an inlet of the sample channel 206A. The microfluidics unit 120 is further configured to generate the sheath fluid flows 208B for hydrodynamically focusing the sample fluid flow 208A by providing a sheath fluid to inlets of the sheath flow channels 206B. The microfluidics unit 120 may for example comprise a respective reservoir for the sample fluid and the sheath fluid as well as one or more pumps for providing the sample fluid and the sheath fluid to the respective inlets of the microfluidic system 200.
The device 100 comprises a controller 124 that is configured to control the microscope controller 108A, the microfluidics unit 120 and/or the sample preparation unit 122. The controller 124 is further configured to analyze phase shift images obtained from the microscope 108 and in particular to identify cell aggregates such as the cell aggregates 102A, 102B therein, e.g. as described below for method 300. Preferably, the controller 124 is configured to execute the method 300 at least in part. The controller 124 may be implemented in hardware, software or a combination thereof. The controller 124 may for example comprise a processing device (not shown) and a memory (not shown) storing instructions for execution by the processing device to provide the functionality described herein. The controller 124 may for example comprise a central processing unit (CPU), a graphics processing unit (GPU), a field programmable gate array (FPGA), an application-specific integrated circuit (ASIC) and/or a microcontroller.
In step 302, a suspension is prepared which comprises a viscoelastic fluid and biological cells from the sample such as the single cells 104A, 104B and the cell aggregates 102A, 102B. The suspension, which may also be referred to as the sample fluid in the following, may for example be prepared using the sample preparation unit 122 of the device 100, e.g. by adding the viscoelastic fluid to the whole blood sample or vice versa in a reservoir of the sample preparation unit 122. The viscoelastic fluid comprises a linear water soluble shear-thinning polymer such as poly(ethylene oxide) (PEO) or poly(vinyl pyrrolidone) (PVP), wherein the molecular weight of the shear-thinning polymer is between 2 MDa and 10 MDa, preferably between 3.5 MDa and 4.5 MDa, e.g. 4.0 MDa. The sample fluid is prepared such that a mass fraction of the shear-thinning polymer in the sample fluid is less than 0.2%, preferably between 0.04% and 0.06%, for example 0.05%. In the sample fluid, the whole blood sample may be diluted by a factor between 1:50 and 1:200, for example by a factor of 1:100, e.g. by adding an appropriate amount of the viscoelastic fluid and/or of another fluid such as water or an aqueous solution.
Preparing the suspension in step 302 preferably does not comprise any of a lysis of erythrocytes, a sphering of platelets and erythrocytes and a labelling or staining of cells. In some embodiments, a coagulation-inhibiting substance such as ethylenediamine tetra-acetic acid (EDTA) may be added to the whole blood sample to prevent coagulation, e.g. prior to or when preparing the sample fluid. In some examples, a platelet-activating substance such as thrombin receptor activating peptide (TRAP) may be added to the whole blood sample or to the sample fluid.
In step 304, a flow 208A of the sample fluid containing the single cells 104A, 104B and the cell aggregates 102A, 102B is generated through the measurement volume 202 of the microfluidic system 200, e.g. using the microfluidics unit 120. As a result of the shear thinning induced by the shear-thinning polymer, the viscoelastic fluid may exert hydrodynamic forces on the single cells 104A, 104B and the cell aggregates 102A, 102B in the sample fluid flow 208A. This may induce a motion perpendicular to a direction of flow such that the single cells 104A, 104B and the cell aggregates 102A, 102B are focused viscoelastically in a center region of the sample fluid flow 208A, which may be aligned with a focal plane of the microscope 108.
Simultaneously, two or more sheath flows 208B may be generated through the measurement volume 202 in step 306 to hydrodynamically focus the sample fluid flow 208A in addition to the viscoelastic focusing, e.g. by providing a sheath fluid to inlets of the sheath flow channels 206B of the microfluidic system 200. A pair of vertical sheath flows 208B may sandwich the sample fluid flow 208A in the Z direction of
In order to avoid damaging the cell aggregates 102A, 102B, the flow velocities of the sample fluid flow 208A and of the sheath flows 208B are chosen such that a shear stress that the cell aggregates 102A, 102B are exposed to in the sample fluid flow 208A is less than 50 Pa, preferably less than 10 Pa, e.g. by adjusting the flow rates through the sample channel 206A and the sheath flow channels 206B accordingly. The flow rates may for example be chosen such that the flow velocity of the sample fluid flow 208A in the measurement volume 202 is between 5 mm/s and 100 mm/s, in one example between 8 mm/s and 64 mm/s.
While the sample fluid flow 208A flows through the measurement volume 202, one or more phase shift images of the single cells 104A, 104B and the cell aggregates 102A, 102B in the sample fluid flow 208A are taken with the microscope 108. The dilution factor of the sample in the sample fluid may for example be chosen such that each phase shift image contains between 5 and 50 single cells or cell aggregates in order to facilitate distinguishing the single cells and cell aggregates from each other. Preferably, a sequence of phase shift images is taken, for example with a frame rate between 10 frames per second and 200 frames per second. This may allow for analyzing a large number of single cells and cell aggregates in a short amount of time and thus facilitates the detection of types of cell aggregates that rarely occur in the sample.
In steps 310 and 312, the phase shift images taken in step 308 are analyzed, e.g. using the microscope controller 108A and/or the controller 124 of the device 108. This comprises identifying cell aggregates 102A, 102B as well as single cells 104A, 104B in the respective phase images in step 310. Cell aggregates and single cells may for example be distinguished based on a combination of morphological parameters such as a mean diameter and a maximum phase shift, for example by defining corresponding regions in the parameter space spanned by the morphological parameters, e.g. using one or more thresholds for the respective parameters. Additionally or alternatively, cell aggregates may also be identified using computer vision techniques such as a neural network-based classifier. Step 310 may also comprise determining a total number of single cells, a total number of cell aggregates and/or a fraction of cell aggregates, i.e. the ratio of the total number of cell aggregates to the total number of single cells and cell aggregates.
In step 312, the single cells 104A, 104B and the cell aggregates 102A, 102B identified in step 310 may be analyzed further. This may in particular comprise determining a number of cells in the cell aggregates 102A, 102B as well as determining a cell type of the single cells 104A, 104B and a cell type of the cells in the cell aggregates 102A, 102B. To determine the number of cells in a cell aggregate 102A, 102B, constituents of the cell aggregate 102A, 102B may be identified by performing an image segmentation on a portion of the phase shift image associated with the cell aggregate 102A, 102B, e.g. using a watershed algorithm as detailed below with reference to
Step 312 may in particular be used to identify platelet aggregates, leukocyte-platelet aggregates and/or leukocyte aggregates in the phase shift images, e.g. to determine a total number or fraction of the respective aggregates in the phase shift images. Step 312 may also comprise determining a number or fraction of leukocyte-platelet aggregates comprising two or more leukocytes and/or a number or fraction of leukocyte-platelet aggregates and/or platelet aggregates comprising three or more cells, e.g. as an indicator for a bacterial infection.
The method for detecting cell aggregates of biological cells according to the first aspect of the invention may comprise some or all of the features and/or steps of the method for detecting cellular and/or molecular biological objects according to the second aspect of the invention described below. The device for detecting cell aggregates of biological cells according to the first aspect of the invention may comprise some or all of the features and/or components of the device for detecting cellular and/or molecular biological objects according to the second aspect of the invention described below.
The present inventors have further found that a viscoelastic fluid as described above is particularly suitable also for focusing objects other than cell aggregates, in particular for focusing composite objects comprising two or more constituents that are bound or adhere to each other. As detailed above, viscoelastic focusing of objects in a suspension comprising a shear-thinning polymer having a molecular weight between 2 MDa and 10 MDa at a mass fraction in the suspension of less than 0.2% may allow for a reliable focusing of objects of various sizes (e.g. composite objects and non-composite objects) while reducing mechanical stress on the objects, thus preventing damage to or disintegration of the composite objects.
As such, a viscoelastic fluid as described above may for example be used for focusing objects, in particular biological objects, that are labelled with a marker object such as an imaging marker. The marker object may for example be configured to selectively bind to a certain type of object (e.g. to a certain type of cell) and may have characteristic geometric and/or optical properties that allow for distinguishing different types of objects (e.g. different types of cells) in an image. Conventional imaging markers may for example have characteristic spectral properties such as characteristic absorption and/or emission spectra (as e.g. employed in fluorescent imaging markers). Alternatively, imaging markers may be distinguished based on their size or their absorption properties such as a transmittance, see e.g. H. Im et al., PNAS vol. 112, no. 18, 5613-5618 (2015).
Phase shift images obtained with a quantitative phase-contrast microscope may contain more morphological information than for example intensity images obtained with a conventional bright-field microscope and may thus allow for distinguishing different types of cells (e.g. different types of blood cells such as erythrocytes, leukocytes and platelets) without the use of imaging markers, i.e. label-free. Certain types or subtypes of cells, however, may exhibit a very similar morphology and may thus be challenging to distinguish even in phase shift images. This for example applies to subtypes of lymphocytes and in particular to subtypes of T cells. Other objects such as molecular objects (e.g. proteins) may be too small to resolve structural or morphological features of such objects in microscopic images. Therefore, even when using quantitative phase-contrast microscopes, the use of markers objects may be advantageous for certain applications to enable a reliable detection, in particular for automated high-throughput analyses in a clinical setting.
It is thus a further object of the invention to provide a method that allows for a fast and reliable detection of cellular and molecular biological objects and is suitable for performing automated high-throughput analyses in a clinical setting.
This object is met by a method for detecting cellular and/or molecular biological objects using a quantitative phase-contrast microscope according to claim 29 and a device for detecting cellular and/or molecular biological objects according to claim 41. Embodiments thereof are detailed in the corresponding dependent claims.
According to a second aspect of the invention, a method for detecting cellular and/or molecular biological objects using a quantitative phase-contrast microscope is provided. The method comprises labelling biological objects from a sample with marker objects to form composite aggregates, wherein each of the composite aggregates comprises one or more of said biological objects and one or more of said marker objects. A suspension is prepared, wherein the suspension comprises composite aggregates and a viscoelastic fluid. The viscoelastic fluid comprises a shear-thinning polymer having a molecular weight between 2 MDa and 10 MDa, wherein a mass fraction of the shear-thinning polymer in the suspension is less than 0.2%. A flow of the suspension is generated along a microfluidic channel to viscoelastically focus composite aggregates in the suspension in a focal plane of the quantitative phase-contrast microscope. One or more phase shift images of biological objects and/or composite aggregates in the suspension are taken using the quantitative phase-contrast microscope and composite aggregates are identified in the one or more phase shift images.
The method for detecting cellular and/or molecular biological objects according to the second aspect of the invention may further comprise some or all of the features and/or steps of the method for detecting cell aggregates of biological cells according to the first aspect of the invention according to any one of the embodiments described herein.
In particular, the suspension, the viscoelastic fluid and/or the shear-thinning polymer may have similar or identical properties as described above for the method according to the first aspect of the invention. For example, the shear-thinning polymer may have a molecular weight between 3 MDa and 6 MDa in some embodiments, preferably a molecular weight between 3.5 MDa and 4.5 MDa, in one example a molecular weight of 4.0 MDa. Additionally or alternatively, the mass fraction of the shear-thinning polymer in the suspension may be between 0.03% and 0.12%, preferably between 0.04% and 0.06%, in one example 0.05%. The shear-thinning polymer may be a water soluble polymer and may for example be selected from the group consisting of poly(ethylene oxide) (PEO), poly(vinyl pyrrolidone) (PVP), hyaluronic acid (HA) and polyacrylamide (PAA). Preferably, the shear-thinning polymer is poly(ethylene oxide) or poly(vinyl pyrrolidone).
The biological objects that are labelled with the marker objects may be or comprise cellular biological objects such as single cells and/or cell aggregates, in particular blood cells and/or aggregates thereof. Some or all of said biological objects may each for example be a cellular biological object, but may also contain additional constituents in some examples (i.e. may comprise a cellular biological object). A cell aggregate may for example be a cluster of cells adhering to each other. The cell aggregate may e.g. comprise between 2 and 100 cells, in some examples between 2 and 20 cells, in one example between 2 and 10 cells.
Additionally or alternatively, the biological objects that are labelled with the marker objects may be or comprise molecular biological objects (e.g. biomolecules), in particular biological macromolecules such as proteins and/or nucleic acids. Some or all of said biological objects may each for example be a molecular biological object, but may also contain additional constituents in some examples (i.e. may comprise a molecular biological object).
The method according to the second aspect of the invention may also be used for detecting cell aggregates as detailed above for the method according to the first aspect of the invention. The cell aggregates may be the biological objects that are to be detected (e.g. may be labelled using the marker objects) or may be detected in addition to said biological objects. The method may for example be used for detecting labelled biological objects (e.g. labelled macromolecules, labelled single cells and/or labelled cell aggregates) as well as for detecting non-labelled and/or labelled cell aggregates. Put differently, the methods according to the first and second aspects of the invention may be combined for detecting (labelled) cellular and/or molecular biological objects and (labelled and/or non-labelled) cell aggregates. The suspension may comprise biological cells from the sample, e.g. in the form of the composite aggregates and/or in addition to the composite aggregates. The flow of the suspension may be generated such that composite aggregates as well as cell aggregates (and optionally single cells) are focused in the focal plane of the quantitative phase-contrast microscope. In the one or more phase shift images, composite aggregates as well as (labelled and/or non-labelled) cell aggregates (and optionally labelled and/or non-labelled single cells) may be identified.
The marker objects are not particularly limited and may be or comprise any type of object that can be identified in a phase shift image and/or in an intensity image, e.g. distinguished from other objects in the respective image. The marker objects may for example have characteristic geometric properties (e.g. a characteristic size and/or shape) and/or characteristic optical properties (e.g. a characteristic transmittance, a characteristic reflectivity, a characteristic absorption and/or emission spectrum and/or a characteristic refractive index and/or phase shift). In some embodiments, the marker objects may for example be or comprise fluorescent imaging markers, e.g. fluorophore-labelled antibodies, quantum dots and/or nitrogen-vacancy centers.
Preferably, the marker objects are or comprise microbeads, i.e. particles having a size of less than 1 mm. The microbeads may for example be ellipsoidal and/or substantially ellipsoidal particles, in particular spherical and/or substantially spherical particles. The microbeads may for example have a characteristic size, a characteristic transmittance and/or may be associated with a characteristic phase shift (e.g. as a result of a characteristic size and refractive index) that allows for identifying the microbeads in an image, in particular in a phase shift image. In some embodiments, the microbeads may not be fluorescent and/or may be transparent (i.e. may not absorb light at the wavelength used for obtaining the phase shift images).
The microbeads may each have a physical dimension (e.g. a length, a width and/or a height), in particular a diameter, of between 0.5 μm and 100 μm, preferably of between 0.5 μm and 30 μm, in some examples of between 1 μm and 20 μm, in one example of between 2 μm and 10 μm. The microbeads may comprise or consist of a material having a refractive index n (i.e. the real part of the complex refractive index, which determines the phase velocity and thus the phase shift) that is substantially different from that of water (n Z 1.33) and/or larger than a typical refractive index of erythrocytes (n z 1.418). The microbeads may for example comprise or consist of a material having a refractive index of at least 1.4, in some examples of at least 1.45, in some examples of at least 1.5, preferably of at least 1.6, in one example of at least 1.7 and in one example of at least 2.0. Additionally or alternatively, the microbeads may for example comprise or consist of a material having a refractive index of no more than 1.1, preferably of no more than 0.9, in one example of no more than 0.6. The microbeads may for example comprise or consist of a polymer material such as polystyrene, a metal such as gold and/or silver, and/or glass such as fused silica. In some embodiments, the marker objects may also be or comprise nanoparticles, i.e. particles having a size of less than 1 μm, in some examples of less than 500 μm.
The marker objects may be configured to selectively bind to a certain type of biological object, for example to a certain type of binding site associated with (e.g. present or provided on) a certain type of biological object. Thereby, this particular type of biological object (“target objects”) from the sample may be labelled selectively, while other types of biological objects from the sample may e.g. not be labelled with marker objects or may be labelled with a different type of marker object as detailed below. The labelling may be performed using any cell-labelling technique known in the art, e.g. by streptavidin/biotin-based and/or antibody-based cell labelling. A type of biological object as used herein may for example refer to a certain type of cell (e.g. a certain type of blood cell such as erythrocyte, leukocyte or platelet) or to a certain subtype of cell (e.g. a certain leukocyte subtype of such as neutrophil, eosinophil, basophil, lymphocyte or monocyte; a certain lymphocyte subtype of such as B cell, T cell or natural killer cell; or a certain T cell subtype such as T helper cell/CD4+ cell). In other examples, a type of biological object may refer to a certain nucleic acid or to a certain protein. The marker objects may be configured to bind to a single biological object (e.g. such that the composite objects consist of a single biological objects and a single marker object) or may be configured to bind to a plurality of biological objects (e.g. such that the composite object consists of a plurality of biological objects and a single marker object).
The sample may be a sample extracted from a patient, in particular a liquid sample such as a blood sample (for example a whole blood sample or a blood fraction sample), e.g. as detailed above. The suspension may for example be prepared as described above for the method according to the first aspect of the invention, e.g. by adding the viscoelastic fluid (or the shear-thinning polymer) to the sample or vice-versa and optionally diluting the sample. The biological objects may be labelled with the marker objects prior to and/or after preparing the suspension comprising the viscoelastic fluid. In other words, the steps of labelling the biological objects and preparing the suspension may be executed in an arbitrary order and may in particular also be executed simultaneously at least in part. Labelling the biological objects may for example comprise adding the marker objects to the sample and/or to the suspension, e.g. by adding a marker fluid containing the marker objects. In some embodiments, the viscoelastic fluid may be the marker fluid, i.e. may also contain the marker objects. The biological objects may be exposed to the marker objects for an amount of time that is sufficient to allow for the formation of the composite objects, i.e. the binding of the marker objects to the biological objects or vice-versa, prior to taking the phase shift images.
The flow of the suspension along the microfluidic channel may for example be generated as detailed above for the method according to the first aspect of the invention. The composition of the suspension, a flow velocity or flow rate of the suspension and/or the dimensions and/or shape of the microfluidic channel may be adapted so as to achieve viscoelastic focusing of the composite aggregates in the focal plane of the microscope. In some examples, the composite aggregates may additionally or alternatively be focused hydrodynamically, e.g. as detailed above.
Composite aggregates of biological objects and marker objects are similar to cell aggregates in the sense that the composite aggregates also consist of two or more constituents that are bound or adhere to each other. Composite aggregates may also be fragile and prone to break apart, e.g. when exposed to mechanical forces. Furthermore, composite aggregates may differ in size from individual biological objects or other composite aggregates. Therefore, using a suspension comprising a viscoelastic fluid as specified above may be advantageous for imaging composite aggregates for the same reasons as for cell aggregates. In particular, such a suspension may allow for a reliable focusing of objects of various sizes (e.g. composite objects and non-composite objects) while reducing mechanical stress on the objects, thus preventing damage to or disintegration of the composite objects.
The one or more phase shift images of the suspension and of the composite aggregates and/or biological objects contained therein may be taken as described above for the method according to the first aspect of the invention, for example using a digital holographic microscope, wherein the microscope may for example image a portion of the microfluidic channel.
Composite aggregates in the one or more phase shift images may for example be identified similar to the identification of cell aggregates described above. This may in particular comprise distinguishing composite aggregates comprising one or more marker objects from other objects such as non-aggregated marker objects (i.e. individual/single marker objects not contained in a composite aggregate) and/or non-labelled biological objects (e.g. single cells and/or cell aggregates that do not form a composite aggregate with a marker object). This may further comprise identifying constituents of a composite aggregate, e.g. a number and/or a type of the biological objects (in particular cells) contained therein and/or a number and/or a type of the marked objects contained therein. Marker objects and/or composite aggregates may for example be identified (e.g. distinguished from biological objects) based on one or more morphological parameters pertaining to their size, shape and/or structure, for example a mean diameter (equivalent diameter) and/or a phase shift (optical height). Additionally or alternatively, marker objects and/or composite aggregates may also be identified using classical and/or artificial intelligence-based (AI-based) computer vision techniques, e.g. using a neural network-based classifier. Furthermore, labelled and/or non-labelled cell aggregates and/or single cells may also be identified in the one or more phase shift images, e.g. as detailed above.
In a preferred embodiment, the composite aggregates in the one or more phase shift images are identified without relying on or using intensity images, i.e. may be identified based on the one or more phase shift images only. In other embodiments, identifying composite aggregates in the one or more phase shift images may comprise analyzing one or more intensity images associated with the one or more phase shift images. A composite aggregate in a phase shift image may for example be identified based on or using a corresponding intensity image (e.g. an intensity image that was reconstructed from the same interference image(s) as the phase shift image), for example by identifying one or more constituents of the respective aggregate in the intensity image.
In some embodiments, two or more different types of marker objects (e.g. microbeads of different types) may be used. The marker objects may for example comprise marker objects of a first type and marker objects of a second type.
Marker objects of different types may differ in one or more geometric and/or optical properties such that marker objects of different types can be distinguished in a phase shift image and/or in an intensity image. Marker objects of different types (e.g. marker objects of the first type and marker objects of the second type) may for example differ in one or both of a size (e.g. a physical dimension such as a diameter) and a refractive index. For example, a physical dimension of marker objects of different types (e.g. for all possible permutations of the types of marker objects used) may differ by at least 1 μm, preferably at least 2 μm, most preferably at least 3 μm (e.g. a physical dimension of the marker objects of the first type may be at least 1 μm, preferably at least 2 μm, most preferably at least 3 μm smaller or larger than the respective physical dimension of the marker objects of the second type). Additionally or alternatively, the refractive index of the material that the marker objects of different types comprise or consist of may differ by at least 0.1, in some examples by at least 0.2, preferably by at least 0.3, in one example by at least 0.5. The physical dimension and/or the refractive index may for example be chosen such that a phase shift associated with marker objects of different types (e.g. a mean, median or maximum phase shift/optical height) differs by at least π (λ/2), preferably by at least 2π (λ), most preferably at least 4π (2λ).
Based on their different geometric and/or optical properties, marker objects of different types may be distinguished in a phase shift image and/or in an intensity image. The type of a marker object may for example be determined based on one or more morphological parameters pertaining to its size, shape and/or structure, for example a size such as a mean diameter (equivalent diameter) and/or a phase shift (optical height), e.g. by defining one or more thresholds for the respective parameters. Additionally or alternatively, the type of marker object may also be determined using classical and/or artificial intelligence-based (AI-based) computer vision techniques, e.g. using a neural network-based classifier.
Preferably, marker objects of different types are distinguished in the one or more phase shift images based on a phase shift associated with the respective marker object, for example using one or more thresholds for said phase shift. For example, the marker objects of the second type may differ from the marker objects of the first type in the refractive index (and optionally in their size) and the method may further comprise distinguishing, in the one or more phase shift images, marker objects of the second type from marker objects of the first type based on a phase shift associated with the respective marker object. A marker object may e.g. be classified as a marker object of the first type if said phase shift is below a classification threshold and may be classified as a marker object of the second type if said phase shift is above the classification threshold. In some embodiments, marker objects of different types are distinguished based solely on the phase shift associated with the respective marker object (e.g. without relying on any information other than the phase information or phase shift). In other embodiments, marker objects of different types may be distinguished using a more complex classification metric, for example a classification metric based on a phase shift and a size (e.g. a physical dimension in the image plane) of the marker objects.
Marker objects of different types may be configured to selectively bind to different types of binding sites (e.g. to different molecular structures such as different antigens or epitops) on the biological objects. For example, the marker objects of the first type may be configured to selectively bind to a binding site of a first type on the biological objects (e.g. to a first antigen) and the marker objects of the second type may be configured to selectively bind to a binding site of a second type on the biological objects (e.g. to a second antigen).
The different types of binding sites may be associated with different types of biological objects, e.g. to distinguish biological objects of different types via the different types of marker objects attached thereto. For example, the binding site of the first type may be a binding site on biological objects of a first type (e.g. a first type or subtype of cell) and the binding site of the second type may be a binding site on biological objects of a second type (e.g. a second type or subtype of cell).
Additionally or alternatively, different types of binding sites may be associated with the same type of biological objects, for example to form composite aggregates comprising two or more marker objects (e.g. composite aggregates with a sandwich structure comprising a biological object arranged between a first marker object and a second marker object. For example, the binding site of the first type and the binding site of the second type may be different binding sites on biological objects of the same type (e.g. different epitopes on cell of a certain type or different molecular structures on a certain protein).
In some embodiments, the biological objects to be labelled with marker objects are or comprise leukocytes, in particular lymphocytes. The marker objects of the first type may be configured to selectively bind to leukocytes of a first type, in particular to lymphocytes of a first type (for example to T cells or to a subtype of T cells such as e.g. T helper cells/CD4+ cells). The marker objects of the second type may be configured to selectively bind to leukocytes of a second type, in particular to lymphocytes of a second type (for example to B cells or natural killer cells or to a different subtype of T cells such as e.g. cytotoxic T cells/CD8+ cells). This may for example allow for distinguishing different types of lymphocytes, in particular different types of T cells, which due to their similar morphology may otherwise be difficult to distinguish from each other in phase shift images.
Some or all of the marker objects may comprise or consist of a magnetic material, for example a paramagnetic material (e.g. a material with a magnetic susceptibility of more than 10−5, preferably of more than 2·10−5) or diamagnetic material (e.g. a material with a magnetic susceptibility of less than −10−5, preferably of less than −2·10−5). Preferably, the respective marker objects comprise or consist of ferrimagnetic material and/or a ferromagnetic material. In one example, some or all of the marker objects are superparamagnetic objects. Marker objects made from a magnetic material may for example allow for the manipulation of composite aggregates using magnetic fields, e.g. for sorting objects and/or for accumulating objects in certain regions.
Additionally or alternatively, some or all of the marker objects may comprise or consist of a material having a high acoustic impedance. As used herein, a high acoustic impedance may for example refer to an acoustic impedance of at least 10 N·s/m3, preferably of at least 30 N·s/m3, in one example of at least 50 N·s/m3. Marker objects made of a material with a high acoustic impedance may for example allow for the manipulation of composite aggregates using acoustic waves such as ultrasound, e.g. for sorting objects and/or for accumulating objects in certain regions.
In some embodiments, some or all of the marker objects may be functionalized. The respective marker objects may for example comprise a substance that is configured to interact (e.g. chemically) with a biological object. The substance may for example be a chemical messenger that is configured to bind to a receptor on the biological object, e.g. to activate or inhibit a response of the biological object. The substance may for example be arranged on a surface of the marker objects and/or in a surface layer of the marker objects. The biological objects may for example be or comprise platelets and/or leukocytes. Some or all of the marker objects may comprise a platelet-activating substance to induce platelet aggregation and/or leukocyte-platelet aggregation, a coagulation-inhibiting substance and/or a leukocyte-activating substance, e.g. as detailed above for the method according to the first aspect of the invention. The platelet-activating substance may for example be selected from the group consisting of adenosine diphosphate (ADP), thrombin receptor activating peptide (TRAP), epinephrin, thrombin, Von-Willebrand-factor, C-reactive protein (CRP), selectin P ligand (PSGL-1), fibrinogen, thromboxane, tissue factor and collagen. Additionally or alternatively, some or all of the marker objects may for example comprise a drug such as a checkpoint inhibitor, one or more antibody drug conjugates and/or one or more bispecific T-cell engaging antibody constructs.
The method according to the second aspect of the invention is not limited to a particular way of focusing the composite aggregates in the focal plane of the quantitative phase-contrast microscope, in particular not to the viscoelastic focusing described above. In some embodiments, the composite aggregates in the suspension may thus be focused in a different way than described above. For example, a shear-thinning polymer with a different molecular weight, in particular with a molecular weight below 2 MDa, may be used. Additionally or alternatively, the mass fraction of the shear-thinning polymer in the suspension may be different, e.g. 0.2% or more. Furthermore, other focusing techniques such as hydrodynamic focusing may be used in addition to or instead of viscoelastic focusing.
Accordingly, the present invention also provides a method for detecting cellular and/or molecular biological objects using a quantitative phase-contrast microscope, the method comprising: (1) labelling biological objects from a sample with marker objects to form composite aggregates, wherein each of the composite aggregates comprises one or more of said biological objects and one or more of said marker objects; (2) preparing a suspension comprising composite aggregates; (3) generating a flow of the suspension along a microfluidic channel to viscoelastically and/or hydrodynamically focus composite aggregates in the suspension in a focal plane of the quantitative phase-contrast microscope; (4) taking one or more phase shift images of biological objects and/or composite aggregates in the suspension using the quantitative phase-contrast microscope; and (5) identifying composite aggregates in the one or more phase shift images. The above numbering is for clarity only and does not imply a certain order of execution. As far as technically feasible, the method may be executed in an arbitrary order and steps thereof may be executed simultaneously at least in part, e.g. the labelling of biological objects and the preparation of the suspension. The method may further comprise some or all of the features and/or steps of the methods according to the first and second aspect of the invention according to any one of the embodiments described herein.
According to the second aspect, the invention further provides a device for detecting cellular and/or molecular biological objects using a method for detecting cellular and/or molecular biological objects according to any one of the embodiments according to the second aspect of the invention described herein. The device comprises a mount configured to receive a microfluidic system comprising a measurement volume. The device further comprises a microscope configured to take phase shift images of biological objects and/or composite aggregates in the measurement volume. The device also comprises a microfluidics unit configured to receive a sample fluid. The sample fluid is a suspension comprising a viscoelastic fluid and composite aggregates, wherein each of the composite aggregates comprises one or more biological objects from a sample and one or more marker objects for labelling the biological objects. The viscoelastic fluid comprises a shear-thinning polymer having a molecular weight between 2 MDa and 10 MDa with a mass fraction of the shear-thinning polymer in the sample fluid being less than 0.2%. The microfluidics unit is configured to generate a flow of the sample fluid through the measurement volume to viscoelastically focus composite aggregates in the sample fluid flow in a focal plane of the microscope. The device further comprises a controller configured to identify composite aggregates in a phase shift image of the sample fluid flow obtained from the microscope.
The device according to the second aspect of the invention and/or its components including the microfluidic system may be similar to the device according to the first aspect of the invention and its components, respectively. The device according to the second aspect of the invention may comprise some or all of the features and/or components of the device according to the first aspect of the invention described above, e.g. some or all of the features and/or components of the device 100 of
In a preferred embodiment, the device according to the second aspect of the invention further comprises a sample preparation unit, which in some examples may be integrated with the microfluidics unit into a single unit. The sample preparation unit may be configured to provide the viscoelastic fluid comprising the shear-thinning polymer with a molecular weight between 2 MDa and 10 MDa to prepare the sample fluid comprising composite aggregates and the viscoelastic fluid, wherein the mass fraction of the shear-thinning polymer in the sample fluid is less than 0.2%, e.g. as detailed above for the device according to the first aspect of the invention. The sample preparation unit may be configured to adjust a mass fraction of the shear-thinning polymer in the sample fluid and/or to dilute the sample fluid, e.g. as described above for the device according to the first aspect of the invention.
Additionally or alternatively, the sample preparation unit may be configured to provide marker objects for labelling biological objects from the sample. Each of the marker objects is configured to bind to one or more biological objects to form a composite aggregate, e.g. as discussed above for the method according to the second aspect of the invention. The sample preparation unit may for example be configured to add the marker objects, e.g. in the form of a marker fluid containing the marker objects, to the sample, to the sample fluid/suspension and/or to the viscoelastic fluid. In some embodiments, the marker objects may be contained in the viscoelastic fluid.
The controller may be configured to execute some or all of the steps of a method for detecting cellular and/or molecular biological objects according to any one of the embodiments according to the second aspect of the invention described herein, e.g. some or all of the steps of method 800 described below. For this, the controller may be configured to control some or all of the other components of the device accordingly, in particular the microscope, the microfluidics unit and/or the sample preparation unit, for example by generating corresponding digital and/or analog control signals. The controller may be configured to identify marker objects in a phase shift image and/or to determine the type of a marker object from the phase shift image as described above, e.g. based on a size and/or a phase shift associated with marker object. In some embodiments, the controller may further be configured to execute some or all of the steps of a method for detecting cell aggregates of biological cells according to any one of the embodiments according to the first aspect of the invention described herein.
The method 800 comprises, in step 802, labelling biological objects from the sample with marker objects to form composite aggregates. A composite aggregate is an aggregate or cluster that comprises one or more biological objects and one or more marker objects. Examples for labelling of biological objects are schematically illustrated in
For example, marker objects 900-I of a first type may be added to the sample (or to the sample fluid or suspension prepared from the sample in step 804) as illustrated in
In some embodiments, marker objects 900-II of a second type, e.g. microbeads of a second type, may be added to the sample (or to the sample fluid or suspension prepared from the sample in step 804) as also illustrated in
The marker objects 900-I of the first type and the marker objects 900-II of the second type differ in one or more geometric and/or optical properties such that marker objects of different types can be distinguished in a phase shift image and/or in an intensity image. For example, as illustrated in
In this example, the marker objects 900-I and 900-II have the same size, but differ in their refractive index as illustrated by the different hatching in
The method 800 further comprises, in step 804, preparing a suspension (sample fluid) that comprises a viscoelastic fluid and composite aggregates, e.g. similar to step 302 of the method 300. The viscoelastic fluid comprises a shear-thinning polymer having a molecular weight between 2 MDa and 10 MDa, preferably between 3.5 MDa and 4.5 MDa, e.g. 4.0 MDa. A mass fraction of the shear-thinning polymer in the suspension is less than 0.2%, preferably between 0.04% and 0.06%, for example 0.05%. The shear-thinning polymer or a fluid containing the shear-thinning polymer may for example be added to the sample prior to or after labelling the biological objects in step 802. The shear-thinning polymer may for example be poly(ethylene oxide) (PEO) or poly(vinyl pyrrolidone) (PVP).
In step 806, a flow 208A of the suspension is generated along a microfluidic channel such as the measurement volume 202 to viscoelastically focus composite aggregates in the suspension in a focal plane of a quantitative phase-contrast microscope such as the microscope 108, for example similar to steps 304 and 306 of the method 300. Preferably, the flow 208A is generated such that non-labelled biological objects such as non-labelled single cells and/or non-labelled cell aggregates are also focused in the focal plane of the microscope 108.
In step 808, one or more phase shift images of biological objects and/or composite aggregates in the suspension flowing through the measurement volume 202 are taken using the microscope 108, e.g. similar to step 308 of method 300.
The method 800 further comprises analyzing the one or more phase shift images in steps 810 and 812, e.g. similar to the image analysis performed in steps 310 and 312 of method 300. The image analysis may for example be performed by the controller 124 of the device 100.
In step 810, composite aggregates are identified in the one or more phase shift images. This may for example comprise identifying marker objects in the one or more phase shift images and determining whether another object (i.e. a biological object labelled by the respective marker object) is in contact with or in close vicinity to the marker object, e.g. within a distance threshold, or vice-versa. Thereby, single marker objects may be distinguished from marker objects bound in a composite aggregate. Marker objects and/or composite aggregates may be identified based on one or more morphological parameters pertaining to their size, shape and/or structure, for example a mean diameter (equivalent diameter) and/or a phase shift (optical height), e.g. by defining one or more thresholds for the respective parameters.
In step 812, a type of marker object may be determined for some or all of the composite aggregates and/or marker objects identified in step 810, e.g. to distinguish between marker objects 900-I of the first type and marker objects 900-II of the second type. This may for example allow for distinguishing T cells 104B-I of the first type from T cells 104B-II of the second type. The type of a marker object may for example be determined based on one or more morphological parameters pertaining to its size, shape and/or structure, for example a mean diameter (equivalent diameter) and/or a phase shift (optical height), e.g. by defining one or more thresholds for the respective parameters. Step 812 may further comprise identifying other constituents of the composite aggregates identified in step 810, e.g. determining a number and/or a type of the biological objects in a composite aggregate and/or determining a number of the marker objects in the composite aggregate.
Analyzing the one or more phase shift images may further comprise identifying single cells and/or cell aggregates in the one or more phase shift images as well as optionally analyzing the single cells and/or cell aggregates, e.g. to determine a cell type, to identify constituents of a cell aggregate and/or determine a number of cells in a cell aggregate, for example by executing step 310 and/or step 312 of method 300 at least in part.
The embodiments of the present invention disclosed herein only constitute specific examples for illustration purposes. The present invention can be implemented in various ways and with many modifications without altering the underlying basic properties. Therefore, the present invention is only defined by the claims as stated below.
| Number | Date | Country | Kind |
|---|---|---|---|
| 21188590.0 | Jul 2021 | EP | regional |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2022/068788 | 7/6/2022 | WO |
