KR100599856B1 - Apparatus For Measuring Blood Cell Deformability - Google Patents

Abstract

An object of the present invention is to provide a blood cell deformability measuring apparatus capable of measuring the deforming properties of blood cells in a short time using a small amount of blood samples using a disposable blood flow channel kit (disposable kit) that does not require washing. To this end, the present invention is a blood cell deformability measuring device, the blood sample is in direct contact with the disposable kit 20 that can be used for single use; A light generator 10 positioned on one side of the disposable kit to generate a light source; And providing a pressure different from atmospheric pressure to the disposable kit to flow the blood sample while acquiring an image of the light source diffracted by the blood cells of the blood sample passing through the disposable kit to measure the deformability of the blood cell. It includes a measuring unit 30.

Blood, blood cells, deformability, disposable

Description

Apparatus For Measuring Blood Cell Deformability

1 is an internal configuration of an embodiment of a blood cell deformability measuring apparatus according to the present invention.

Figure 2 is an embodiment external configuration of a disposable kit of blood cell deformability measuring apparatus according to the present invention.

Figure 3 is an exemplary view showing the initial form of the blood sample is filled in the disposable kit of the blood cell deformability measuring apparatus according to the present invention.

Figure 4 is an external configuration of an embodiment of the blood cell deformability measuring apparatus according to the present invention.

Figure 5 is a diagram illustrating a variety of image data collected through the blood cell deformability measuring apparatus according to the present invention.

Figure 6 is an embodiment graph of time-differential pressure measured in the apparatus for measuring blood cell deformability according to the present invention.

FIG. 7 is a graph illustrating an example of deformability of blood cells analyzed through a blood cell deformability measuring apparatus according to a wall shear stress-deformation index (DI). FIG.

8 is an external configuration diagram of an embodiment of the differential pressure generator of the blood cell deformability measuring apparatus according to the present invention.

9 is a view showing the internal structure of another embodiment of the blood cell deformability measuring apparatus according to the present invention.

The present invention relates to a blood cell deformability measuring device.

Recently, development of a measuring device for deformability of blood cells has been attempted as the deformability of blood cells is known as a direct influence factor on the viscosity and rheological properties of blood.

In particular, the LORCA hemocytometer, published in the Journal of Clinical Hemorheology and Microcirculation (Vol. 14, pp. 605-618, 1994), irradiates the blood cells with lasers under a double concentric tubular rotating Couette flow condition. It is a device that obtains the diffracted image by CCD camera and analyzes it through computer program to measure the deformability of blood cells. At this time, since the shear force or shear rate depends on the rotational speed, repeated experimental measurements with different rotational speeds are required to measure a wide range of shear rates and shear forces. There is this.

In addition, the Blood Cell Strain Distribution Tester (ARCA), published in the Journal of Blood Cells, Molecules, and Diseases (Vol. 28, pp. 373-384), injects diluted blood between two rotating parallel disks. At this time, the image of the blood cells deformed in the shear force applied by the rotation is obtained directly through a microscope and a CCD camera, only the focused image among them are selected and analyzed by the curve fitting program to the respective blood cells It is a device that obtains deformation distribution under given shear force condition by analyzing deformation. At this time, it takes a significant time of at least 1 to 2 hours to acquire a plurality of blood cell images, image processing and analysis, and has the disadvantage of cleaning the device in contact with the blood sample.

On the other hand, one of the problems found by using the blood cell deformability measuring device developed as described above is that the blood sample is in direct contact with the device, which requires the trouble and effort of cleaning the device every time the experiment is performed. to be. In addition, the conventional devices as described above require professional training for experimental measurement, and require specialized knowledge for operation and analysis, which makes it difficult to use in a medical field such as a general hospital.

The present invention is to solve the above problems, an object of the present invention is to measure the deformation characteristics of blood cells in a short time using a very small amount of blood samples using a disposable blood flow channel kit (disposable kit) that does not require washing. The present invention provides a blood cell deformability measuring apparatus.

In order to achieve the above object, the present invention provides a blood cell deformability measuring apparatus, comprising: a disposable kit (20) for direct contact with a blood sample and usable for single use; A light generator 10 positioned on one side of the disposable kit to generate a light source; And measuring deformability of the blood cells by providing the disposable kit with a pressure different from atmospheric pressure to flow the blood sample while acquiring an image of the light source diffracted by the blood cells of the blood sample passing through the disposable kit. Including a measuring unit 30, the disposable kit 20, Sample storage chamber 21, the blood sample is injected and stored; A slit channel 22 having one end connected to the sample storage chamber and allowing blood samples introduced through the sample storage chamber to pass with great flow resistance; And a waste sample storage chamber 23 connected to the other end of the slit channel, for storing the blood sample drawn out through the slit channel, wherein the measurement unit 30 includes a connection pipe and a valve. A differential pressure generator 33 for providing a pressure other than atmospheric pressure to the disposable kit 20 through 32 to allow the blood sample to flow; A pressure gauge (34) having one end connected to the differential pressure generator or the disposable kit to continuously measure the pressure in the differential pressure generator or the disposable kit over time; A screen 31 for projecting an image diffracted by blood cells while passing through the slit channel; An image acquirer 35 for obtaining a projected image; The controller 36 for calculating the amount of change in shear force with time while calculating the blood cell deformability according to the shear force, using the values measured by the pressure gauge and the image acquirer, and the calculation result of the controller Or an output 37 for outputting to a printer and a storage 38 for storing various data transmitted to or generated by the controller.

That is, according to the present invention, after filling the diluted blood sample in a disposable storage container (disposable kit), when the blood sample passes through the slit channel of the disposable kit, the light source is irradiated to project the diffracted image on the screen, which is then converted into an image. After the acquisition, it is analyzed to analyze the characteristics of the blood cell strain, relates to a blood cell deformability measuring device associated with laser diffraction and variable driving pressure.

Hereinafter, exemplary embodiments of the present invention will be described in detail with reference to the accompanying drawings.

1 is an internal configuration of an embodiment of a blood cell deformability measuring apparatus according to the present invention.

That is, the blood cell deformability measuring apparatus according to the present invention, as shown in the drawings, the blood sample is in direct contact with the disposable kit 20 that can be used for single use, the light generating unit 10 for generating a light source in the disposable kit And measuring unit 30 for measuring the deformability of the blood cells by providing an image of the light source diffracted by the blood cells of the blood sample passing through the disposable kit while providing a pressure lower than atmospheric pressure to the disposable kit. It is configured to include.

In this case, the disposable kit 20 is connected to one end of the sample storage chamber 21 and the sample storage chamber in which the blood sample is injected and stored, and the blood sample introduced through the sample storage chamber generates a large flow resistance. It is connected to the other end of the slit channel 22 and the slit channel to pass through, and comprises a waste sample storage chamber 23 for storing the blood sample exited through the slit channel.

In addition, the measuring unit 30, the differential pressure generator 33 for providing a pressure lower than atmospheric pressure to the waste sample storage chamber 23 through the connecting pipe and the valve 32, one end of the differential pressure generator or the A pressure gauge 34 for continuously measuring the pressure of the differential pressure generator or the waste sample reservoir over time, and a screen for projecting an image diffracted by blood cells while passing through the slit channel. (31), an image obtainer 35 for acquiring the projected image, a controller 36 for storing, calculating, and processing the values measured by the pressure gauge and the image acquirer, and displaying the calculation result in the controller or And an output unit 37 for outputting to a printer and a storage unit 38 for storing various information transmitted to or generated by the controller.

In this case, the image acquirer 35 may acquire an image projected after projecting the image diffracted and transmitted from the slit channel 22 on the screen 31, but is not limited thereto. The image diffracted and transmitted at 22 may be obtained directly without projecting onto the screen 31.

Finally, the light generator 10 is located on one side of the slit channel to perform a function of generating a light source.

2 is an external configuration diagram of an embodiment of a disposable kit of blood cell deformability measuring apparatus according to the present invention, showing the external configuration of the disposable kit 20 shown in FIG.

That is, the disposable kit 20 illustrated in FIG. 2 includes a sample storage chamber 21, a slit channel 22, and a waste sample storage chamber 23 as described above, and may be configured as an integrated or assembled type. Can be.

In particular, the thickness of the slit channel 22 can be manufactured from several micrometers to several hundred micrometers in size, in the present embodiment will be described as using 200 micrometers.

In addition, the sample storage chamber 21 and the waste sample storage chamber 23 may be sealed with a stopper 24 such as rubber or silicon.

On the other hand, the amount of blood required when using the disposable kit 20 as described above is a very small amount of 5 microliters, blood cell deformability measuring apparatus according to the present invention using a very small amount of blood as described above in a high viscosity liquid such as PVP solution Dilution allows determination of blood cell deformability.

3 is an exemplary view showing an initial form in which a blood sample is filled in a disposable kit of a blood cell deformability measuring apparatus according to the present invention, showing a cross section of the disposable kit shown in FIG.

That is, when the blood sample is injected into the sample reservoir 21, the blood sample is filled up to the middle portion of the slit channel 22 as shown in the drawing due to the capillary effect, but more due to the high viscosity of the blood sample. It is not filled anymore.

At this time, the blood sample stored in the sample storage chamber 21 is introduced into the waste sample storage chamber 23 through the slit channel 22 from the sample storage chamber 21 by the vacuum pressure added to the waste sample storage chamber 23. In this case, in the slit channel 22, the shear force acts on the blood cells with a large flow resistance, and the blood cells exposed to the shear force are deformed and introduced into the lung sample storage chamber 23.

4 is an external configuration diagram of an apparatus for measuring blood cell deformability according to an embodiment of the present invention. Referring to FIG. 4, an operation method of the apparatus for measuring blood cell deformability according to the present invention will be described below.

That is, when a light source such as a laser, a laser diode, or a light emitting diode (LED) of the light generator 10 is irradiated to the optically transparent slit channel 22, it is irradiated by blood cells deformed by shear force. The transmitted light is diffracted and at this time, the transmitted light is projected onto the screen 31, which is obtained by the image acquirer 35.

FIG. 5 is a diagram illustrating various image data collected by the blood cell deformability measuring apparatus according to the present invention. As shown in the drawing, red blood cells, which were circular when the shear force was close to zero, were elliptical when exposed to high shear force. It can be seen that the deformation is long, which will be described in more detail as follows.

That is, when a plurality of blood cells (plural blood cells) is deformed by the shear force present in the shear flow field through the slit channel 22, when irradiated with light 10 having an appropriate wavelength (wave length) from the outside This light passes through the blood sample and causes diffraction and interference, and when the passed light is projected onto the screen 31, the projected image causes the deformation of the plurality of blood cells to appear as one integrated image.

In particular, the shape of the blood cells changes according to the speed of the flow or the magnitude of the shear force, in the present invention, the flow velocity is rapidly flowed due to the high differential pressure at the beginning of the measurement, at this time, the shear force also acts largely deforms the blood cells greatly Diffraction images appear as ellipses with very high aspect ratios. On the other hand, as the flow rate gradually decreases, the corresponding shear force also decreases, and the blood cells are restored to their original shape, and thus the diffraction image becomes close to the circle.

Meanwhile, the blood cell deformability measuring apparatus according to the present invention may determine the deformation index (DEFORMATION INDEX, DI) by analyzing the length of the long axis and the short axis of the image acquired by the image acquirer 35 by an image processing analysis program.

6 is an exemplary graph of time-differential pressure measured in the apparatus for measuring blood cell deformability according to the present invention.

That is, the graph shown in FIG. 6 measures the pressure difference between the pressure of the waste sample storage chamber 23 connected to the differential pressure generator 32 and the atmospheric pressure over time, and the differential pressure generator 33 measures the waste sample storage chamber 23. When a pressure lower than atmospheric pressure is applied, the blood sample of the sample storage chamber 21 is introduced into the waste sample storage chamber 23 through the slit channel 22 by the differential pressure.

At this time, the pressure of the waste sample storage chamber 23 gradually increases from the initial vacuum pressure due to the volume of the incoming blood sample, gradually approaches the atmospheric pressure value, and finally measures the pressure balance between the two storage chambers 21 and 23. Is complete. That is, it can be seen from FIG. 6 that the differential pressure decreases exponentially and reaches the equilibrium pressure gradually over time.

On the other hand, if the viscosity of the blood sample and the initial differential pressure is kept constant in each experiment, the same pressure-time curve can be obtained, and thus pressure over time can be predicted without a separate pressure measurement.

FIG. 7 is a graph illustrating an example of deformability of blood cells analyzed by a blood cell deformability measuring apparatus according to a wall shear stress-deformation index (DI).

That is, FIG. 7 obtains a plurality of images in which blood cells are deformed and flows under a variable driving pressure as described above, and analyzes them with an image processing program. It is represented by the deformation index (DI).

At this time, the strain index is represented as the long axis length (A) and the short axis length (B) of the diffraction image is defined as shown in Equation 1 below.

DI = (A-B) / (A + B)

That is, the deformation index (DI) is a value close to zero, that is, circular if the shear force is small, and the DI value increases as the shear force increases.

On the other hand, the operating principle and blood cell deformability measuring method of the blood cell deformability measuring apparatus according to the present invention will be described in detail.

First, a blood sample is injected into the sample reservoir 21. In this case, some blood samples injected into the sample reservoir 21 may be partially introduced into the slit channel 22 connected to the sample reservoir due to a capillary effect.

Next, the differential pressure generator 33 is operated to form a differential pressure different from the atmospheric pressure. That is, in this embodiment, a vacuum pressure lower than atmospheric pressure is formed. The differential pressure generator 33 in which the vacuum pressure is formed in this way is connected to the waste sample storage chamber 23 by the valve device 32 to lower the pressure of the waste sample storage chamber 23 to atmospheric pressure or less. At this time, the pressure gauge 34 connected to the differential pressure generator 33 or the waste sample storage chamber 23 through a connecting pipe continuously measures the vacuum pressure of the waste sample storage chamber 23.

On the other hand, due to the driving force generated by the pressure difference between the sample storage chamber 21 exposed to atmospheric pressure and the waste sample storage chamber 23 under low pressure, the blood sample is slit channel 22 from the sample storage chamber 21. Through the flow to the waste sample storage chamber (23).

At this time, the volume of air decreases due to the volume of the blood sample flowing into a constant internal volume of the closed waste sample storage chamber 23, and thus the pressure of air increases. Therefore, the pressure difference between the sample storage chamber 21 and the waste sample storage chamber 23 decreases exponentially, and as time passes, the pressure between the two storage chambers is gradually balanced, and finally, the flow of the blood sample stops and the measurement process is Will end.

Meanwhile, the measured pressure is a pressure difference between the sample storage chamber 21 and the waste sample storage chamber 23, and the shear rate and shear force are calculated using the equation already known through the differential pressure ΔP. Can be calculated. That is, when the ideal gas state equation is applied to the volume of the waste sample storage chamber 23, the internal volume V corresponding to each time can be calculated.

P _wi V _wi = P _w (t) V _w (t)

As the blood sample is transferred to the waste sample storage chamber 23 through the slit channel 22, the pressure [P _w (t)] of the closed lung sample storage chamber 23 gradually increases with time, and the lung sample storage chamber 23 The internal air volume [V _w (t)] decreases. At this time, since P _w (t) is a value measured or converted by the pressure gauge 34, the air volume [Vw (t)] of the waste sample storage chamber 23 at each instant is finally determined using Equation 2 above. Can be calculated In Equation 2, the subscripts i and w represent initial values and lung sample storage chambers, respectively.

In this case, the decrease in the internal volume of air in the waste sample storage chamber 23 obtained above is the same as the inflow volume increase of the blood sample.

ΔV _{w, air} = ΔV _liq

On the other hand, the first derivative of the volume change of the blood sample over time is the volume flow rate (Q) of the test fluid passing through the capillaries per unit time.

Q = [ΔV _liq / Δt]

In this case, assuming that the given slit channel 22 is a rectangular channel using the driving pressure and the flow rate applied to both ends of the slit channel 22, and the spacing, width, and length of the channel are H, W, and L, respectively, The equation for calculating the shear rate to be is shown in Equation 5 below.

γ = (1/3) [6Q / (WH ² )] [2 + {d (ln Q) / d (ln τ)}]

In [Equation 5], the shear stress is calculated as shown in [Equation 6] below.

τ = [ΔP (t) H / L] / [(1+ 2H / W)]

In Equation 6, τ represents a shear stress in the wall.

Meanwhile, another method may be applied instead of the method of calculating the shear force using the volume. In other words, when preparing a blood sample, the buffer solution (buffer solution) and the blood is mixed to about 100 to 1, or 200 to 1, the amount of blood required is about 5 microliters. As such, since the volume ratio of the blood sample is very small, the viscosity of the blood sample is not much different from that of the buffer solution. Therefore, the viscosity of the blood sample may be regarded as the viscosity of the buffer solution already known. Therefore, in the above-described embodiment of the present invention, although a pressure gauge is used, the viscosity of the blood sample is known in advance, and the resources for the geometry of the flow resistance tube and the predetermined vacuum pressure are known. This can be used to precalculate pressure changes over time. Alternatively, one simulation can measure the pressure over time and apply it to other experiments. That is, the shear force can be calculated using the pressure over time.

That is, as one of the embodiments of the present invention, it can be one of the features of the present invention that the shear stress over time can be obtained in advance through a pressure measured in advance without a separate pressure measurement. In addition, only the blood cell deformability measured every hour with respect to the shear stress calculated in advance as described above can be measured in real time to show the shear force and the deformability corresponding to each time in a graph.

During the process of gradually decreasing the driving differential pressure as described above, blood cells in the blood sample flowing through the slit channel 22 flow in a state deformed by the shear force generated by the flow. A light source 10, such as a laser diode, is irradiated onto the optically transparent slit channel, and the light is diffracted or interfered by blood cells flowing inside the slit, and some light passes through the slit and is projected onto the screen 31.

In this case, the projected image is an image diffracted by the shape of a plurality of blood cells and exhibits a characteristic representing an average shape of blood cells, which is commonly known as a laser-diffraction technique. to be. At this time, the signal input values obtained from the pressure gauge 34 and the image acquirer 35 are processed by the controller 36 according to each time, and are stored in the storage 38.

At this time, the pressure is converted into shear stress and shear rate through a simple mathematical relationship, and the geometric shape of the projected image is analyzed through a dedicated image processing analysis program, and the controller 36 again curve-fits the curve. The program analyzes the aspect ratios of the major and minor axes of the ellipse, calculates the respective index of deformation (DI), and displays them in graphs or tables for the shear forces acting on the results.

On the other hand, since deformability of blood cells may be affected by temperature, it is necessary to control the measurement temperature to a constant temperature. Therefore, even in the configuration of the present invention, in order to maintain the disposable kit 20 in contact with blood at a constant temperature, the disposable kit should be used while keeping thermal equilibrium in a predetermined chamber. In addition, during the measurement time, it is possible to install a temperature control block or water-jacket that can be heated or cooled in the system parts in contact with each other in order to minimize the temperature change of the kit. In the embodiment of the present invention, the temperature is controlled by using a thermo-electric component at the site where the disposable kit 20 contacts. It is also possible to configure the halogen lamp or the like to preheat the temperature of the air surrounding the device to a predetermined temperature.

On the other hand, as shown in Figure 2, in the device configuration of the present invention, the disposable kit 20 in which the blood sample is in direct contact includes a sample reservoir 21, a slit channel 22, a waste sample reservoir 23, etc. As an integrated element, it is designed and manufactured to be disposed of after use so that a series of measurements can be performed without washing in an environment like a general hospital. At this time, the disposable kit 20 as described above should be designed to be measured with only a very small amount of blood samples at the same time. To this end, the disposable kit 20 may be manufactured through a well-known microstructure fabrication technique or may be manufactured through precision injection. In the embodiment of the present invention, the disposable kit 20 was manufactured by precisely injecting an optically transparent plastic material. Plastic injection molding as described above is very economically suitable for use in a single-use, in the case of contamination of pathogens, such as blood, can be discarded after measurement has a very convenient advantage.

In addition, the light generating unit 10 used in the present invention needs a light source having a form of a point light source and having a wavelength range (wave length range) that can be diffracted by blood cells. That is, the wavelength band suitable for causing red blood cells and diffraction is about 350 nm to 690 nm. In the embodiment of the present invention, a laser diode having a wavelength of 650 nm is used.

In addition, an image acquisition device 35 for acquiring the projected image may be an image acquisition device such as a CCD sensor array, a CCD camera, a web camera, or a video camera. In an embodiment of the present invention, an image is acquired through a CCD camera. It was. On the other hand, when using a CCD sensor array, it is possible to obtain an image directly without the projection screen 31.

FIG. 8 is an external configuration diagram of the differential pressure generator in the apparatus for measuring blood cell deformability according to the present invention, and shows an example of the differential pressure generator 33 shown in FIG. 1.

That is, the differential pressure generator 33 is configured to connect the step motor 42 to a device such as a linear motion (LM) guide 43 so that the step motor 42 is controlled by the controller 36. As the linear guide 43 moves forward or backward by a predetermined amount at an initial position, a pressure higher or lower than atmospheric pressure is formed inside the device 41 such as a piston-cylinder device or a syringe.

9 is an internal configuration diagram of another embodiment of a blood cell deformability measuring apparatus according to the present invention, and illustrates a blood cell deformability measuring apparatus including a differential pressure generator 33-1 using a pressurized driving method.

That is, the driving method of the present invention described with reference to FIGS. 1 to 7 has been described as a differential pressure driving type, in particular with respect to a vacuum driving method, but other pressurized driving methods are possible.

On the other hand, the blood cell deformability measuring apparatus according to the present invention applying the pressure-driven driving method as shown in Figure 9, the sample storage chamber 21, the sample storage chamber and one end of the blood sample is injected and stored as shown Connected to the slit channel 22 through which the blood sample introduced through the sample storage chamber generates a large flow resistance, and is connected to the other end of the slit channel, and exits through the slit channel. A differential pressure generator 33-1 for providing a pressure higher than atmospheric pressure to the sample reservoir 21 through a lung sample reservoir 23, a connection tube and a valve 32 for storing blood samples, one end of which is A pressure gauge 34 for continuously measuring pressure of the differential pressure generator over time, and attached to one side of the slit channel to generate a light source The living part 10, a screen 31 for projecting an image diffracted by blood cells while passing through the slit channel, an image acquirer 35 for acquiring the projected image, and a pressure gauge and an image acquirer. A controller 36 for storing, calculating, and processing a value, an output 37 for outputting the calculation result of the controller to a screen or a printer, and a storage for storing various data transmitted to or generated by the controller It is comprised including the group 38.

In this case, in another blood cell deformability measuring apparatus according to the present invention including the differential pressure generator 33-1 using the pressurized driving method as described above, the differential pressure generator 33-1 is referred to in the description of FIG. 8. Of the one or two pressure generation methods, the method of forming a pressure higher than atmospheric pressure is used, and thus, the valve 32, the differential pressure generator 33-1, and the pressure gauge 34 measure the blood cell deformability shown in FIG. Unlike the device, the only difference is that it is connected to the sample storage chamber 21, and other functions and operations may be applied in the same manner as described above.

Also, in the case of the pressurized driving method as described above, the pressure difference between the pressure of the sample storage chamber 21 connected to the differential pressure generator 33-1 and the atmospheric pressure is shown as shown in FIG. 6 over time. That is, when the differential pressure generator 33-1 applies a pressure higher than atmospheric pressure to the sample storage chamber 21, the blood sample of the sample storage chamber 21 passes through the slit channel 22 through the slit channel 22 by the differential pressure. Flows into. At this time, the pressure in the closed sample storage chamber 23 sealed by the volume of the incoming blood sample gradually increases from the initial pressure, and finally the pressure is balanced between the two storage chambers, and the measurement is completed. That is, as shown in FIG. 6, the differential pressure decreases exponentially and gradually reaches an equilibrium pressure as time passes.

The present invention is not limited to the embodiments described above, and various modifications and changes can be made by those skilled in the art, which are included in the spirit and scope of the present invention as defined in the appended claims.

The present invention as described above can measure the deformability of blood cells using a small amount of blood in a very short time, there is an excellent effect that the deformable distribution characteristics of a plurality of blood cells can be obtained through one measurement.

In addition, the present invention has an excellent effect that is very advantageous for real-time clinical application in the treatment field because all the parts in contact with the blood sample can be produced in a disposable kit.

In addition, the present invention has an excellent effect of measuring the blood cell deformability of the circulating blood of the living body with respect to a plurality of shear stress by applying a variable pressure over time.

Claims (11)

In the blood cell deformability measuring device, A disposable kit 20, in which the blood sample is in direct contact and usable for single use; A light generator 10 positioned on one side of the disposable kit to generate a light source; And A measurement for measuring the deformability of the blood cells by providing the disposable kit with a pressure different from atmospheric pressure to flow the blood sample while acquiring an image of the light source diffracted by the blood cells of the blood sample passing through the disposable kit Including part 30, The disposable kit 20, A sample storage chamber 21 into which blood samples are injected and stored; A slit channel 22 having one end connected to the sample storage chamber and allowing blood samples introduced through the sample storage chamber to pass with great flow resistance; And a waste sample storage chamber 23 connected to the other end of the slit channel, for storing the blood sample drawn out through the slit channel. The measuring unit 30, A differential pressure generator (33) for providing a pressure other than atmospheric pressure to the disposable kit (20) through a connector and valve (32) to allow the blood sample to flow; A pressure gauge (34) having one end connected to the differential pressure generator or the disposable kit to continuously measure the pressure in the differential pressure generator or the disposable kit over time; A screen 31 for projecting an image diffracted by blood cells while passing through the slit channel; An image acquirer 35 for obtaining a projected image; The controller 36 for calculating the amount of change in shear force with time while calculating the blood cell deformability according to the shear force, using the values measured by the pressure gauge and the image acquirer, and the calculation result of the controller Or an output unit 37 for outputting to a printer and a storage unit 38 for storing various data transmitted to or generated by the controller. Blood cell deformability measuring device comprising a. The method of claim 1, The differential pressure generator 33, By providing a pressure below atmospheric pressure to the waste sample reservoir 23 of the disposable kit via a connection tube and valve 32, the blood sample passes from the sample reservoir 21 via the slit channel 22 to the waste sample reservoir 23. Blood cell deformability measuring device characterized in that the flow to). The method of claim 1, The differential pressure generator 33, By providing a pressure higher than atmospheric pressure to the sample reservoir 21 of the disposable kit via a connection tube and valve 32, the blood sample passes from the sample reservoir 21 via the slit channel 22 to the waste sample reservoir 23. Blood cell deformability measuring device characterized in that the flow to. The method of claim 1, The slit channel (22) is blood cell deformability measuring apparatus characterized in that the optically transparent and the cross section is rectangular. The method of claim 1, The disposable kit 20, Blood cell strain measurement device, characterized in that consisting of a plastic material. The method of claim 1, In order to prevent the disposable kit 20 from being affected by temperature, A blood cell deformability measuring apparatus provided in a chamber capable of maintaining thermal equilibrium, or configured to be controlled by a device capable of heating or cooling a temperature, or configured to control the temperature of ambient air. The method of claim 1, The image acquirer 35, The apparatus for measuring blood cell deformability, characterized in that for obtaining a projected image after projecting the image diffracted transmitted in the slit channel (22) to the screen (31). The method of claim 1, The image acquirer 35, The apparatus for measuring blood cell deformability, characterized in that the image diffraction transmitted in the slit channel (22) is directly acquired without projecting onto the screen (31). The method of claim 1, The image acquirer 35, Blood cell deformability measuring apparatus comprising at least one of a CCD camera, a CCD sensor array, a digital camera, a web camera, a high-speed CCD video. The method of claim 1, The light generator 10, Blood cell deformability measuring device, characterized in that composed of at least one of a laser, a laser diode or a light emitting diode (LED). The method of claim 1, The controller 36, The strength of the shear force exerted on the blood sample is not calculated using the pressure value measured from the pressure gauge 34, but is calculated in advance by using the time-dependent pressure measured in the slit channel in advance. Blood cell deformability measuring apparatus characterized in that for calculating the blood cell deformability according to each time using the calculated shear force over time.

Images