Erythrocyte osmotic brittleness testing device and testing method

Abstract

The invention belongs to the technical field of analytical instruments and biological medicines, and particularly relates to an erythrocyte osmotic brittleness testing device and a testing method. The testing device comprises a halogen lamp light source, a light collector, a detection cup, a condensing lens path, a transmission light receiver, a scattered light receiver, a detector and a microprocessor. The light collector is positioned on a light path of the halogen lamp light source to enable light to move forwards in the same direction; the condensing lens path is connected with the light collector and the detection cup and gathers the light beams; the detection cup allows light to be transmitted to form transmitted light and scattered light, and the transmitted light and the scattered light are captured by the transmitted light receiver and the scattered light receiver respectively; the detector processes the received signal and transmits the received signal to the microprocessor for analysis. The device utilizes the full spectrum and high brightness of the halogen lamp, realizes erythrocyte osmotic brittleness detection in combination with turbidimetry, and provides an objective quantitative method by measuring the change of light transmittance or absorbance. Compared with a traditional turbidimetric measuring instrument which needs various light sources, is high in cost and complex in operation, the device simplifies detection and reduces cost.

Description

Technical Field

[0001] The invention belongs to the technical field of analytical instruments and biomedicine, and particularly relates to a red blood cell osmotic fragility testing device and a testing method. Background Art

[0002] When water penetrates red blood cells (RBCs) to a certain degree in a hypotonic saline solution, they swell and rupture, releasing intracellular hemoglobin (IGB) in a process called hypotonic hemolysis. The resistance of the RBC membrane to the hemolytic effects of a hypotonic saline solution is called RBC osmotic fragility. Patients with thalassemia and iron-deficiency anemia have reduced intracellular hemoglobin production, resulting in smaller cells and significantly reduced osmotic fragility compared to healthy individuals. Therefore, RBC osmotic fragility is often used clinically to screen for microcytic anemias such as thalassemia and iron-deficiency anemia.

[0003] The inventor's previously filed Chinese invention patent, patent publication number CN114295533A, proposes a method for measuring red blood cell osmotic fragility based on cell counting technology. The method disclosed in this patent requires measuring turbidity when testing red blood cell osmotic fragility. Turbidity refers to the cloudiness of water. Two optical methods are commonly used to measure turbidity: transmission, which measures how much light can pass through; the more turbid the water, the less light can pass through; and scattering, which measures how much light is reflected by particles; the more turbid the water, the more light is reflected.

[0004] However, current medical testing instruments (such as coagulometers and protein analyzers) typically use only one of these methods and only use a single color of light, resulting in a narrow detection range, high cost, and low efficiency. Therefore, there is an urgent need to develop a new measurement device with a simple structure, comprehensive functions, and low cost. Summary of the Invention

[0005] To remedy the deficiencies of the prior art, the present application provides a red blood cell osmotic fragility testing device and testing method to solve the technical problems that traditional medical testing instruments require a variety of different light sources, are costly, and have complex testing.

[0006] In order to solve the above technical problems, this application provides the following technical solutions.

[0007] In a first aspect, the present application provides a red blood cell osmotic fragility testing device, comprising a halogen lamp light source, a light collector, a detection cup, a condenser lens, a transmitted light receiver, a scattered light receiver, a detector, and a microprocessor;

[0008] The light collector is arranged on the optical path of the light from the halogen lamp light source and can allow the light from each halogen lamp light source to travel forward in the same direction;

[0009] The two ends of the condenser path are connected to the light collector and the detection cup respectively, and the condenser path gathers the light emitted by the light collector;

[0010] The detection cup is arranged on the optical path behind the condenser and allows the light emitted by the halogen lamp to pass through to form direct transmitted light and scattered light;

[0011] The transmitted light receiver is disposed on the optical path of the transmitted light and receives the transmitted light;

[0012] The scattered light receiver is arranged on the optical path of the scattered light and receives the scattered light;

[0013] The detector is connected to the transmitted light receiver and the scattered light receiver and detects the transmitted light and scattered light received by them respectively and transmits the detection information to the microprocessor.

[0014] Optionally, an optical intensity detection patch is provided on a side of the condenser path facing the detection cup, and the optical intensity detection patch is configured to issue a warning after the intensity of the light beam emitted by the condenser path reaches a standard.

[0015] Optionally, the condenser lens circuit includes:

[0016] a pipe cavity wall, with two ends of the pipe cavity wall connected to the light collector and the detection cup respectively;

[0017] A plurality of reflective lenses are arranged around the axis of the pipe cavity wall, obliquely attached to the pipe cavity wall, and laid along the length direction of the pipe cavity wall until the entire pipe cavity wall is covered.

[0018] Optionally, the angle between the reflective lens and the optical axis is less than 30 degrees.

[0019] Optionally, the surface shape of the reflective lens is an ellipsoidal shape.

[0020] Optionally, the red blood cell osmotic fragility testing device further comprises a Fresnel lens, and the Fresnel lens is arranged on a side of the channel cavity wall facing the detection cup.

[0021] Optionally, a mounting hole is provided on a side of the detection cup close to the condenser lens path, and a side of the Fresnel lens facing the detection cup is adapted and fixed to the mounting hole.

[0022] Optionally, a light shielding member is provided on the edge of the mounting hole.

[0023] Optionally, the detector has a sensitive wavelength of 540-575 nm for detecting transmitted light and a sensitive wavelength of 700-800 nm for detecting scattered light.

[0024] Optionally, the detector is a spectral detector.

[0025] In a second aspect, the present application provides a method for testing red blood cell osmotic fragility, which is applied to the red blood cell osmotic fragility testing device as described above, comprising the following steps:

[0026] Step 1: Add light salt water to a clean test cup

[0027] First, add a saline solution with very low concentration, such as a low osmotic pressure buffer, into the reaction pool of the detection cup.

[0028] Step 2: Add blood sample and mix

[0029] Add a certain amount of fresh blood sample to the saline solution in step 1 as a whole blood specimen and stir it quickly.

[0030] Step 3: Measure the number of cells after rupture (A)

[0031] Since the mixture will cause some red blood cells to rupture, which is called hemolysis, when the number of red blood cells no longer decreases and reaches equilibrium, measure the number of remaining red blood cells and record it as A.

[0032] Step 4: Change to normal saline

[0033] In another test cup or the reaction pool of the cleaned test cup, add saline with normal concentration, that is, isotonic buffer.

[0034] Step 5: Add blood sample and mix

[0035] Add the same volume of fresh blood sample to the normal saline in step 4 and stir quickly.

[0036] Step 6: Measure the normal cell count (B)

[0037] After the mixture stabilizes, measure the number of remaining red blood cells and record it as B. In normal saline, red blood cells basically do not rupture, so B represents the starting number of red blood cells.

[0038] Calculation of fragility: The "osmotic fragility" of red blood cells is calculated using the formula: (BA) / B x 100%.

[0039] Compared with the prior art, the present invention has the following advantages:

[0040] The device is mainly composed of a halogen light source, a light collector, a detection cup, a condenser lens path, a transmitted light receiver, a scattered light receiver, a detector and a microprocessor. The light collector is located on the light path of the halogen light source, so that the light travels in the same direction; the condenser lens path connects the light collector and the detection cup, and converges the light beam; the detection cup allows the light to be transmitted to form transmitted light and scattered light, which are captured by the transmitted light receiver and the scattered light receiver respectively; the detector processes the received signal and transmits it to the microprocessor for analysis. The device uses the full spectrum and high brightness of halogen lamps, such as halogen tungsten lamps, which cover the ultraviolet, visible and infrared bands, and realizes the detection of red blood cell osmotic fragility by combining with the turbidimetry method, and provides an objective and quantitative method by measuring the change of light transmittance or absorbance. Compared with the traditional turbidimetry measuring instrument which needs multiple light sources, has high cost and complex operation, the device simplifies the detection and reduces the cost, solves the problems of the prior art, and thus has great application value. BRIEF DESCRIPTION OF DRAWINGS

[0041] The application can be better understood by describing the embodiments of the application in conjunction with the accompanying drawings, in which:

[0042] Figure 1 A structural schematic diagram of an embodiment of a red blood cell osmotic fragility testing device according to the application is shown;

[0043] Figure 2 A structural sectional view of an embodiment of a red blood cell osmotic fragility testing device according to the application is shown;

[0044] Figure 3 is Figure 2 A local enlarged view of N in the above figure.

[0045] In the above figures, the meanings of the reference signs are as follows:

[0046] 1, halogen light source; 2, light collector; 3, detection cup; 4, condenser lens path; 5, transmitted light receiver; 6, scattered light receiver; 7, detector; 8, microprocessor; 9, reflecting lens; 10, Fresnel lens; 11, time-sharing controller; 12, optical intensity detection patch; A, mounting hole. DETAILED DESCRIPTION

[0047] Unless otherwise defined, technical or scientific terms used in the specification and claims should be interpreted as is customary in the art to which this application pertains.

[0048] All numerical values recited herein, including those in any accompanying claims, include all values from the lower limit to the upper limit of the range, in increments of one unit up to the upper limit unless the context clearly dictates otherwise.

[0049] In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", etc., indicating the orientation or position relationship, are based on the orientation or position relationship shown in the accompanying drawings, and are only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operate in a specific orientation, and therefore cannot be understood as limiting the present invention.

[0050] Furthermore, the terms "first," "second," etc., are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of the technical features being referred to. Thus, a feature identified with "first," "second," etc., may explicitly or implicitly include one or more of the features. In the description of the present invention, unless otherwise specified, "plurality" means two or more.

[0051] Normal red blood cells are biconcave discs. If placed in a hypotonic solution, the osmotic pressure difference between the inside and outside of the cell causes water molecules to enter the cell, causing it to swell or even rupture, releasing hemoglobin. This is called erythrolysis. Red blood cells have varying degrees of resistance to hypotonic solutions, which is related to their surface area / volume ratio. That is, red blood cells have different osmotic fragility: those with a smaller surface area / volume ratio have less resistance (greater osmotic fragility); conversely, those with a smaller surface area / volume ratio have greater resistance (less osmotic fragility). Increased red blood cell membrane fragility is commonly seen in hereditary spherocytosis, elliptocytosis, autoimmune hemolytic anemia with spherocytosis, some cases of hereditary stomatocytosis, and type 2 diabetes. Reduced red blood cell fragility is seen in conditions such as iron deficiency anemia, thalassemia, post-splenectomy, obstructive jaundice, hepatitis, cirrhosis, and liver cancer. Certain traditional Chinese medicines, such as angelica sinensis, can significantly reduce red blood cell fragility. Magnetic fields, ultraviolet light, and radiofrequency can also reduce red blood cell fragility. The red blood cell osmotic fragility test can serve as an important auxiliary diagnostic method for various diseases, including hereditary polycythemia and thalassemia.

[0052] In view of this, the present application proposes a red blood cell osmotic fragility testing device, comprising a halogen lamp light source 1, a light collector 2, a detection cup 3, a condenser path 4, a transmitted light receiver 5, a scattered light receiver 6, a detector 7, and a microprocessor 8; the light collector 2 is arranged on the optical path of the light from the halogen lamp light source 1 and allows the light from each halogen lamp light source 1 to travel forward in the same direction; the two ends of the condenser path 4 are respectively connected to the light collector 2 and the detection cup 3, and the condenser path 4 converges the light emitted by the light collector 2; the detection cup 3 is arranged on the optical path behind the condenser path 4 and allows the light emitted by the halogen lamp light source 1 to pass through to form direct transmitted light and scattered scattered light; the transmitted light receiver 5 is arranged on the optical path of the transmitted light and receives the transmitted light; the scattered light receiver 6 is arranged on the optical path of the scattered light and receives the scattered light; the detector 7 is connected to the transmitted light receiver 5 and the scattered light receiver 6 and detects the transmitted light and scattered light received by each of them respectively and transmits the detection information to the microprocessor 8.

[0053] refer to Figure 1 、 Figure 2 、 Figure 3 , showing a schematic cross-sectional structure diagram of a red blood cell osmotic fragility testing device provided by the present invention. As shown in the figure, the red blood cell osmotic fragility testing device described herein comprises a halogen lamp light source 1, a light collector 2, a detection cup 3, a condenser path 4, a transmitted light receiver 5, a scattered light receiver 6, a detector 7, and a microprocessor 8; the light collector 2 is arranged on the optical path of the light from the halogen lamp light source 1 and allows the light from each of the halogen lamp light sources 1 to be transmitted in the same direction. The two ends of the condenser path 4 are respectively connected to the light collector 2 and the detection cup 3, and the condenser path 4 converges the light emitted by the light collector 2. The detection cup 3 is arranged on the optical path after the condenser path 4 and allows the light emitted by the halogen lamp light source 1 to pass through to form direct transmitted light and scattered scattered light. The transmitted light receiver 5 is arranged on the optical path of the transmitted light and receives the transmitted light, and the scattered light receiver 6 is arranged on the optical path of the scattered light and receives the scattered light. The detector 7 is connected to the transmitted light receiver 5 and the scattered light receiver 6 and detects the transmitted light and scattered light received by them respectively and transmits the detection information to the microprocessor 8 .

[0054] In this embodiment, a halogen lamp light source 1 is used as the light source, and the full spectrum of the halogen lamp light source 1 (usually a halogen tungsten lamp) is used to obtain its relative or absolute radiation energy distribution in the ultraviolet, visible and infrared bands. This detection using a halogen lamp is crucial for evaluating its light quality, color rendering, color temperature, light efficiency and potential applications. The present application combines the full spectrum detection of a halogen lamp with turbidimetry for the detection of red blood cell osmotic fragility, which is an innovative and more objective and quantitative method. The present application utilizes the advantages of a wide spectrum and high brightness of a halogen lamp, and uses a spectrometer to accurately measure the transmittance or absorbance changes of a red blood cell suspension under different osmotic pressure gradients, and combines it with the turbidimetric detection method to solve the technical problems that traditional turbidimetric meters require a variety of different light sources, are costly, and have more complex detection.

[0055] The light source of the present application adopts a halogen lamp light source 1, and the light collector 2 can be a fiber coupler or a semi-transparent and semi-reflective prism arranged at a 45° angle on the path of the light from each point light source. Figure 1 The light collector 2 shown is a semi-transparent and semi-reflective prism arranged at an angle of 45 degrees to the halogen lamp light source 1 and on the path of the light emitted by the halogen lamp light source 1.

[0056] The detection cup 3 can be a cubic cup, which is arranged on the optical path of the halogen lamp light source 1 after passing through the light collector 2 and allows the light emitted by the point light source to pass through to form direct transmitted light and scattered scattered light.

[0057] Since the light intensity of the halogen lamp light source 1 is inconsistent with that of the traditional LED lamp, generally speaking, most of the energy of the halogen lamp light source 1 is converted into heat, and only about 10-20% is converted into visible light, with low luminous efficiency, roughly 15-25 lumens / watt. In order to ensure that the intensity of the light beam emitted to the detection cup 3 meets the requirements, the present application sets a condenser path 4 between the detection cup 3 and the collector 2, and the two ends of the condenser path 4 are respectively connected to the collector 2 and the detection cup 3. The condenser path 4 gathers the light emitted by the collector 2 to ensure that the light intensity in the condenser path 4 meets the standard. The detection cup 3 is set on the light path behind the condenser path 4, which can allow the light emitted by the halogen lamp light source 1 to pass through the detection cup 3 after being gathered by the condenser path 4, thereby forming direct transmitted light and scattered scattered light.

[0058] The transmitted light receiver 5 is arranged on the optical path of the transmitted light and receives the transmitted light; the scattered light receiver 6 is arranged on the optical path of the scattered light and receives the scattered light; the transmitted light receiver 5 and the scattered light receiver 6 can be one or more of a photoelectric converter, a grating, or a combined lens.

[0059] The detector 7 is connected to the transmitted light receiver 5 and the scattered light receiver 6 and detects the transmitted light and scattered light received by the transmitted light receiver 5 and the scattered light receiver 6 respectively and transmits the detection information to the microprocessor 8 .

[0060] Optionally, the sensitive wavelength of the detector 7 for detecting transmitted light is 300-1000nm, preferably, the wavelength range is 540-575nm, the sensitive wavelength for detecting scattered light is 300-1000nm, and the wavelength range is 700-800nm; the detector 7 can be a spectral detector 7.

[0061] If the detector 7 is a spectral detector 7 , the transmitted light receiver 5 and the detector 7 connected thereto are combined into one device; similarly, the scattered light receiver 6 and the detector 7 connected thereto can also be a spectral detector 7 combined into one.

[0062] Furthermore, to ensure that the intensity of the light beam emitted to the detection cup 3 meets the requirements, an optical intensity detection patch 12 is provided on the side of the condenser path 4 facing the detection cup 3. The optical intensity detection patch 12 is configured to issue a warning when the intensity of the light beam emitted by the condenser path 4 reaches the standard. In this embodiment, since the halogen lamp light source 1 requires a certain startup time after the instrument is started before it can reach a constant output light intensity, the present application provides the optical intensity detection patch 12 on the side of the condenser path 4 facing the detection cup 3. When the halogen lamp light source 1 reaches a constant output light intensity, the optical intensity detection patch 12 is triggered and a signal is generated and sent to the microprocessor 8, issuing an alarm.

[0063] like Figure 2 and Figure 3 As shown, further, the focusing lens path 4 includes: a pipe cavity wall (not marked in the figure), with the two ends of the pipe cavity wall respectively connected to the collector 2 and the detection cup 3; a plurality of reflective lenses 9, which are surrounded by the axis of the pipe cavity wall and obliquely attached to the pipe cavity wall, and are laid along the length direction of the pipe cavity wall until the entire pipe cavity wall is covered.

[0064] In this embodiment, the wall of the pipe cavity is a cylindrical channel, and a number of reflective lenses 9 are attached to the wall of the pipe cavity. The reflective lenses 9 are distributed on all the walls of the pipe cavity. When the light beam emitted by the collector 2 enters the wall of the pipe cavity, the scattered light is continuously reflected by the reflective lenses 9 and gathered in the wall of the pipe cavity. After the concentrator path 4 gathers the light emitted by the collector 2, the light intensity in the concentrator path 4 reaches the standard and penetrates the detection cup 3, thereby forming direct transmitted light and scattered scattered light.

[0065] Furthermore, the angle between the reflector lens 9 and the optical axis is less than 30 degrees. In this embodiment, to ensure that the light beam from the condenser lens 4 is emitted horizontally, the inclination angle of the reflector lens 9 needs to be correctly set. In this application, the angle between the reflector lens 9 and the optical axis is less than 30 degrees, which can maximize the convergence of scattered light toward the optical axis.

[0066] Furthermore, the surface shape of the reflective lens 9 is an ellipsoidal shape. In this embodiment, the reflective lens 9 in the condenser path 4 is a parabolic reflector, for example, the surface shape of the reflective lens 9 is an ellipsoidal shape, and its working principle is to place the light source at the focus of the reflector, and after the light is reflected, the reflected light is emitted as parallel to the optical axis as possible.

[0067] Furthermore, the red blood cell osmotic fragility testing device further includes a Fresnel lens 10, which is disposed on the side of the channel lumen facing the test cup 3. In this embodiment, to further ensure that the light beam emitted to the test cup 3 is horizontal, the present application includes the Fresnel lens 10 on the side of the channel lumen facing the test cup 3. By utilizing the optical properties of the Fresnel lens 10, the light beam emitted from the condenser path 4 to the test cup 3 is maintained as horizontally as possible.

[0068] Furthermore, a mounting hole A is defined on the side of the detection cup 3 near the condenser path 4, and the side of the Fresnel lens 10 facing the detection cup 3 is adapted to be fixed to the mounting hole A. In this embodiment, the mounting hole A can be defined on the side of the detection cup 3 near the condenser path 4 to facilitate placement of the Fresnel lens 10 within the mounting hole A, thereby preventing loss of light intensity.

[0069] Furthermore, a light shielding member (not shown in the figure) is provided at the edge of the mounting hole A. In this embodiment, the light shielding member can reduce the weakening of the light beam intensity in the mounting hole A.

[0070] Furthermore, the detector 7 has a sensitive wavelength of 540-575 nm for detecting transmitted light and a sensitive wavelength of 700-800 nm for detecting scattered light. In this embodiment, since hemoglobin (Hb) has significant absorption peaks in the visible light region, with the main peaks located in the β absorption band of oxyhemoglobin and the α absorption band of oxyhemoglobin, both of which have sensitive wavelengths of 540 nm and 575 nm, the detector 7 has a sensitive wavelength of 540-575 nm for detecting transmitted light.

[0071] In addition, due to the extremely low absorption of hemoglobin, its absorption coefficient drops to the lowest in the near-infrared band of >700nm, that is, the absorbance is close to 0. In order to avoid the interference of hemoglobin release after hemolysis on the signal, the sensitive wavelength for detecting scattered light is 700-800nm.

[0072] Furthermore, the detector 7 is a spectral detector 7. In this embodiment, the present application utilizes the advantages of the wide spectrum and high brightness of the halogen lamp to accurately measure the transmittance or absorbance changes of the red blood cell suspension under different osmotic pressure gradients through a spectrometer.

[0073] It is worth noting that Figure 1 and Figure 2 As shown, the red blood cell osmotic fragility testing device provided by the present invention can also be installed with a time-sharing controller 11, which is respectively connected to each halogen lamp light source 1 and a photoelectric converter (not shown in the figure) and is connected to the microprocessor 8 signal, and controls the linkage switch of each halogen lamp light source 1 and the photoelectric converter under the management of the microprocessor 8.

[0074] The time-sharing controller 11 controls the power supply of each halogen light source 1 alternately under the management of the microprocessor 8. The power supply duration of each halogen light source 1 can be 1-50ms, and the power supply interval time of each halogen light source 1 can be 1ms-60s.

[0075] The red blood cell osmotic fragility test device of the present application can be measured using the following method:

[0076] Step 1: Add light salt water to the clean test cup 3

[0077] A saline solution with a very low concentration, such as a low osmotic pressure buffer solution, is first added to the reaction pool of the detection cup 3 .

[0078] Step 2: Add blood sample and mix

[0079] Add a certain amount of fresh blood sample to the saline solution in step 1 as a whole blood specimen and stir it quickly.

[0080] Step 3: Measure the number of cells after rupture (A)

[0081] Since the mixture will cause some red blood cells to rupture, which is called hemolysis, when the number of red blood cells no longer decreases and reaches equilibrium, measure the number of remaining red blood cells and record it as A.

[0082] Step 4: Change to normal saline

[0083] In another test cup 3 or the reaction pool of the cleaned test cup 3, saline with normal concentration, i.e., isotonic buffer solution, is added.

[0084] Step 5: Add blood sample and mix

[0085] Add the same volume of fresh blood sample to the normal saline in step 4 and stir quickly.

[0086] Step 6: Measure the normal cell count (B)

[0087] After the mixture stabilizes, measure the number of remaining red blood cells and record it as B. In normal saline, red blood cells basically do not rupture, so B represents the starting number of red blood cells.

[0088] Calculation of fragility: The "osmotic fragility" (ability to resist rupture) of red blood cells is calculated using this formula: (BA) / B x 100%.

[0089] It is worth noting that the above steps use the light scattering method to detect the particle size of 1000 microns using the transmitted light receiver 5 and the scattered light receiver 6, and can detect all types of cells in the whole blood. The particle detection module can be continuous detection or time-sharing detection.

[0090] In summary, the present invention provides a red blood cell osmotic fragility testing device, which is mainly composed of a halogen lamp light source 1, a light collector 2, a detection cup 3, a condenser path 4, a transmitted light receiver 5, a scattered light receiver 6, a detector 7 and a microprocessor 8. The light collector 2 is located on the optical path of the halogen lamp light source 1, so that the light travels in the same direction; the condenser path 4 connects the light collector 2 and the detection cup 3 to gather the light beam; the detection cup 3 allows light to be transmitted to form transmitted light and scattered light, which are captured by the transmitted light receiver 5 and the scattered light receiver 6 respectively; the detector 7 processes the received signal and transmits it to the microprocessor 8 for analysis. The device utilizes the full spectrum and high brightness of halogen lamps, such as halogen tungsten lamps, which cover ultraviolet, visible and infrared bands, and combines turbidimetry to realize red blood cell osmotic fragility detection, and provides an objective quantitative method by measuring the transmittance or absorbance change. Compared with the traditional turbidimetric measuring instruments that require multiple light sources, high costs and complex operations, the present device simplifies detection, reduces costs, solves the shortcomings of the existing technology, and is therefore of great value for promotion and application.

[0091] The specific embodiments described above further illustrate the objectives, technical solutions and beneficial effects of the present invention in detail. It should be understood that the above are only specific embodiments of the present invention and are not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present invention should be included in the scope of protection of the present invention.

Claims

1. A red blood cell osmotic fragility testing device, characterized in that: It includes a halogen lamp light source, a light collector, a detection cup, a condenser lens, a transmitted light receiver, a scattered light receiver, a detector, and a microprocessor; The light collector is arranged on the optical path of the light from the halogen lamp light source and can allow the light from each halogen lamp light source to travel forward in the same direction; The two ends of the condenser path are connected to the light collector and the detection cup respectively, and the condenser path gathers the light emitted by the light collector; The detection cup is arranged on the optical path behind the condenser and allows the light emitted by the halogen lamp to pass through to form direct transmitted light and scattered light; The transmitted light receiver is disposed on the optical path of the transmitted light and receives the transmitted light; The scattered light receiver is arranged on the optical path of the scattered light and receives the scattered light; The detector is connected to the transmitted light receiver and the scattered light receiver and detects the transmitted light and scattered light received by them respectively and transmits the detection information to the microprocessor.

2. The red blood cell osmotic fragility testing device according to claim 1, characterized in that: An optical intensity detection patch is provided on the side of the condenser path facing the detection cup, and the optical intensity detection patch is configured to issue a warning after the intensity of the light beam emitted by the condenser path reaches a standard.

3. The red blood cell osmotic fragility testing device according to claim 1, characterized in that: The condenser lens circuit includes: a pipe cavity wall, with two ends of the pipe cavity wall connected to the light collector and the detection cup respectively; A plurality of reflective lenses are arranged around the axis of the pipe cavity wall, obliquely attached to the pipe cavity wall, and laid along the length direction of the pipe cavity wall until the entire pipe cavity wall is covered.

4. The red blood cell osmotic fragility testing device according to claim 3, characterized in that: The included angle between the reflective lens and the optical axis is less than 30 degrees.

5. The red blood cell osmotic fragility testing device according to claim 4, characterized in that: The surface shape of the reflective lens is an ellipsoidal shape.

6. The red blood cell osmotic fragility testing device according to claim 3, characterized in that: The red blood cell osmotic fragility testing device further comprises a Fresnel lens, which is arranged on a side of the channel cavity wall facing the detection cup.

7. The red blood cell osmotic fragility testing device according to claim 6, characterized in that: A mounting hole is provided on a side of the detection cup close to the condenser lens path, and a side of the Fresnel lens facing the detection cup is adapted and fixed to the mounting hole.

8. The red blood cell osmotic fragility testing device according to claim 7, characterized in that: A light shielding member is provided at the edge of the mounting hole.

9. The red blood cell osmotic fragility testing device according to claim 1, characterized in that: The detector has a sensitive wavelength of 540-575 nm for detecting transmitted light and a sensitive wavelength of 700-800 nm for detecting scattered light; The detector is a spectral detector.

10. A method for testing red blood cell osmotic fragility, applied to the red blood cell osmotic fragility testing device according to any one of claims 1 to 9, comprising the following steps: Step 1: Add light salt water to a clean test cup First, add a very low concentration of salt water, such as a low osmotic pressure buffer, into the reaction pool of the test cup; Step 2: Add blood sample and mix Add a certain amount of fresh blood sample to the saline solution in step 1 as a whole blood sample and stir quickly; Step 3: Measure the number of cells after rupture Since the mixture will cause some red blood cells to rupture, this is called hemolysis. When the number of red blood cells stops decreasing and reaches equilibrium, measure the number of remaining red blood cells and record it as A. Step 4: Change to normal saline Add saline with normal concentration, i.e. isotonic buffer, to another test cup or the reaction pool of the cleaned test cup; Step 5: Add blood sample and mix Add the same volume of fresh blood sample to the normal saline in step 4 and stir quickly; Step 6: Measure the normal cell count After the mixture stabilizes, measure the number of remaining red blood cells, which is recorded as B. In normal saline, red blood cells basically do not rupture, so B represents the starting number of red blood cells. Calculation of fragility: The "osmotic fragility" of red blood cells is calculated using the formula: (BA) / B×100%.

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