US3830569A - Process and apparatus for counting biological particles - Google Patents

Process and apparatus for counting biological particles Download PDF

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Publication number
US3830569A
US3830569A US00386280A US38628073A US3830569A US 3830569 A US3830569 A US 3830569A US 00386280 A US00386280 A US 00386280A US 38628073 A US38628073 A US 38628073A US 3830569 A US3830569 A US 3830569A
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cells
blood
red
accordance
hematocrit
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J Meric
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    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06M—COUNTING MECHANISMS; COUNTING OF OBJECTS NOT OTHERWISE PROVIDED FOR
    • G06M11/00—Counting of objects distributed at random, e.g. on a surface
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
    • G01N15/02—Investigating particle size or size distribution
    • G01N15/0205—Investigating particle size or size distribution by optical means
    • G01N15/0211—Investigating a scatter or diffraction pattern
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N2021/4704—Angular selective
    • G01N2021/4711—Multiangle measurement
    • G01N2021/4716—Using a ring of sensors, or a combination of diaphragm and sensors; Annular sensor

Definitions

  • ABSTRACT A method and apparatus for analyzing with a high degree of reliability the number of red cells, white cells and platelets in a sample of blood, as well as the hematocrit and average volume of the red blood cells.
  • the focal plane contains photosensitive areas which correspond to the directions which form, with the initial direction of the light beam, angles which fall between:
  • the present invention concerns a new process, as well as an apparatus for performing said process, to permit counting of biological particles suspended in a liquid medium and particularly to allow direct and instantaneous determination of the quantitative composition of the formed elements in the blood.
  • the blood contains essentially three types of cells, namely, red blood cells, white blood cells and platelets. It is particularly important to know the concentration of these elements in order to facilitate many diagnoses of human illnesses. It is also interesting to know the hematocrit as well, i.e., the volume occupied by the red blood cells in the blood volume.
  • optical counting Another classical method, called optical counting, consists in measuring the diffusion produced by the blood particles which are examined one by one in an irradiated suspension volume.
  • the errors in these methods of counting are high because of the background noise in the apparatus caused by the presence of the red cells.
  • the electronic discriminations associated with this apparatus lead to numerous errors in the final count.
  • the arrangement requires frequent calibration and constitutes a very expensive assembly for the user.
  • the invention provides a simple solution and a less expensive approach to the problem. Essentially, it makes it possible for the first time to determine rapidly from a very small blood sample the quantitative proportions of the principal elments making up the blood, i.e., red blood cells, white blood cells and platelets, as well as the hematocrit and the average cll volume; the latter can be accomplished without the need to separate the red cells and the platelets, as is done in the known methods of electronic counting, and without having to resort to auxiliary determinations, which therefore eliminates the principal sources of error encountered in the known devices currently in use. Moreover, this direct determination of the principal hematological parameters of the blood is acquired with the aid of a device which is easy to use and has a less complex structure than the arrangements which are currently employed for analyzing the blood.
  • the process according to the invention is based on the well known principle, described below, of the diffraction of light by the microparticles of the blood and the analysis of the spatial frequency spectrum of the differences in the index of the sample which correspond to different particles of blood.
  • the counting procedures used thus far which employ this principle have not been able to count more than one part of the formed elements of the blood, it has been found that by a series of specific adaptations and operational modes, appropriately combined, it is possible to achieve directly the determination of all the investigated parameters and thus to satisfy the pressing need of the market for system which is easy to operate and yields reproducible results.
  • the new process is essentially charcterized by the fact that two blood samples to be analyzed, in one of which the red cells have been hemolyzed and in the other of which the cells have been spherized, are placed in the path of a beam of light emerging from a convergent optical system powered by a source of cohernet and monochromatic light so as to obtain in he focal plane of the optical system at least two photosensitive zones which receive the luminous flux diffracted by the particles, said flux corresponding to the directions which form angles with the initial direction of the beam which are located respectively between:
  • 1 mm of human blood contains approximately 5 million red blood cells, 8,000 white blood cells and 300,000 platelets; the volume occupied by the red cells (or the hematocrit) amounts to approximately 45 percent of the total blood volume.
  • the size of the particles is about 3 microns for the platelets, 6 microns for the red blood cells and 12 microns for the white cells.
  • the number of white cells and platelets is much lower than that of the red cells, so that it is necessary, in order to count these platelets and white cells, to deprive the red cells of the hemoglobin which they contian in advance (transforming them into Rollets stromata) so that they will lose their diffracting power.
  • a hemolyzing fluid such as, for example, ammonium oxalate at a concentration of l g/liter or any other agent with the same function (see the work by E. Ponder, Hemolysis and Related Phenomena, Gruen and Stratton, New York, N.Y.). In this fashion, it is possible to count the white blood cells and the platelets together with a high degree of accuracy.
  • the blood sample in order to be able to count the red cells, it is necessary to spherize the latter by placing the blood sample in a solution of the appropriate liquid, such as, for example, the solution called Gowers which is based on sodium sulfate and acetic acid, or any other appropriate spherizing agent (cf. E. Ponder, cited above).
  • Gowers which is based on sodium sulfate and acetic acid, or any other appropriate spherizing agent (cf. E. Ponder, cited above).
  • the process of the invention it is also possible to employ a single blood sample in a single cell and thus obtain directly a total result for the number of formed elements, providing a circuit for circulation of the sample in the cell so that the sample receives adequate amounts of the spherizing agent and then, introduced after a specific time, a supplementary quantity of this agent in order to produce in known fashion the hemolysis of the spherized red cells.
  • the series of diffraction angles in accordance with equations (1) and (2) above have the following correspondence: the first to the counting zones of the white blood cells, platelets and red cells (all of the particles, whose variations in diameter around an average value remain low) and the second to the zone of evaluation of the total volume occupied by the particles.
  • the de' termination of a certain interval of diffraction angles has admittedly been mentioned before (U.S. Pat. No.
  • f. means of transforming the fluxes into electrical signals and to display directly the counting results.
  • the laser serves particularly well as a light generator because its spatial coherence makes it possible to produce a beam which has very little natural diffraction. Moreover, its emission is strictly monochromatic and its power is high, making it possible to use it as an output amplifier.
  • the optical system of the enlarger type, is preferably equipped at its internal focus with a spatial filter composed of a screen which is perforated at its center, and filters out the laser rays which are not parallel with teh axis, and therefore serves to purify the light beam by cutting down the background noise cause by parasitic diffractions or possible defects in the coherence of the beam.
  • the cell containing the sample to be analyzed may be composed of two transparent sheets with parallel faces.
  • the cell may be a receptacle with transparent walls supplied with spherizing liquid.
  • the cell is preferably mounted between the exterior lens of the optical system and the focal plane of this system. In this position, in which the distance between the particles to be analyzed and the focal plane can be varied, the diffraction image varies homothetically relatively to its center, with the homothetic ratio being equal to the ratio of the distances.
  • the system may be equipped with two cells which are mounted between the exterior lens of the optical system and the focal plane of this system.
  • the screen which is placed in the focal plane is supplied with at least two windows with internal and external radii which are respectively calculated according to formulas (1) and (2) above.
  • the cell (or, according to another version, the two cells) containing the sample is displaced during measurement relative to the focal plane of the optical system but one cannot correct the measurement errors caused by the presence of stromata whose diffraction is very low but nevertheless perceptible.
  • the diffraction angles between s, 1.5 Mir-(ad) and s 3 s it is therefore preferable when selecting the diffraction angles between s, 1.5 Mir-(ad) and s 3 s to provide three windows, two of which correspond to the measurement zones for the red cells and the hematocrit (in the case where the red cells are spherized) or the platelets and the white cells (in the case where the red cells are he molyzed), with the third window therefore serving to measure the perturbation caused by the stromata.
  • the means of measuring the luminous fluxes which pass through each window are mounted behind the latter and may be composed of photosensitive cells which transform the energy which they receive into electrical signals which are fed into an electronic apparatus of known type which acts as the calculator and make it possible to display directly on a panel the numerical results of the analysis.
  • FIG. I is a simplified diagram of the apparatus.
  • FIG. 2 is a front view of the screen with windows.
  • the light source is represented by a continuous laser 1 provided with mirrors 2 and 3 (the latter being nonreflecting).
  • Ahead of generator 1 are two lenses 4 and S which magnify the laser beam 6.
  • Each window is theoretically annular in shape but practically speaking the configuration need not be very strict because the apparatus according to the invention does not perform absolute determination; acting as a trap, it must shield 9, provided with a central aperture 10 behind 6 which is a light trap 11, is equipped in the non-limiting fashion of the embodiment shown here with four be calibrated and furnishes results which are compared to reference measurements.
  • the blood sample to be analyzed is placed in cell 20 between lens 5 and the focal plane F of the optical system at a distance D from the latter.
  • the radii of the internal and external edges of the window 12 are equal to r and r such that r Ds, and r Ds s and s corresponding to the definition (1) given above with ad 6 microns (average diameter of the spherized red blood cells).
  • Window 13 has radii r Ds and r Ds with s and s corresponding to definition (II) with ad 3 microns (average diameter of the platelets).
  • Window 14 has radii r Ds and r Ds s and s corresponding to the definition (1) given above, with ad 12 microns (average diameter of the white cells).
  • Window 15 has radii r Dr, and r Ds With s' and s' corresponding to the definition (2) given above with ad 6 microns.
  • the rays in beam 6 undergo diffraction while passing through the blood and strike screen 9 within the annular zones delimited by radii r 4 r 4 r -r and r r,, of each window.
  • the luminous flux strikes photodiodes I6, 17, I8 and 19 which produce potentials S (platelets), 5,, (white cells), S, (red cells) and S H (hematocrit) with intensities proportional to the members of formed elements present in the blood to be analyzed.
  • S platelets
  • 5 white cells
  • S red cells
  • S H hematocrit
  • the potential S for example, depends not only on the number of platelets in the sample but also on the number of white cells and stromata. In order to obtain the number of platelets, it is necessary to correct S using signals 8,, and 5,.
  • corrections can be made automatically and instantaneously by injecting, for example, in know fashion, signals 5,, S,,, S, and S coming from the cited photodiodes, across resistance bridges; in this case, the result can be read at the output in the form of a voltage. It is also possible to utilize in advantageous fashion analog or numerical modules which provide the same result. These methods of displaying the results do not themselves characterize an original characteristic of the process of the invention and therefore have not been shown in the attached drawing.
  • N aS bS,, c dS N HS b s C (PS (N and N represent the number of platelets and white cells per mm of blood) 5,, and S represent respectively the platelets and the white cells but they lead to a slight interaction between the two signals which is translated by the terms b and b.
  • PS N and N represent the number of platelets and white cells per mm of blood
  • S represent respectively the platelets and the white cells but they lead to a slight interaction between the two signals which is translated by the terms b and b.
  • These terms, as well as a and a and c and c (background noise of the apparatus) are determined by preliminary calibration.
  • Terms d and d correspond to the influence of the stromata, and can vary as a function of the degree of completeness of hemolysis.
  • N representing the number of red cells per mm of blood and factors e andfbeing determined as above by preliminary calibration.
  • the external radii of the windows may be assumed to be equal to 3 (or 3 to times the internal radii as indicated in equations (1) and (2).
  • zones 5,, and 5,, on the one hand and zones 8,, and S, on the other hand are homothetic. It is therefore sufficient to have two measurement zones in the focal plane and to shift the cell when the blood is added. If the first position corresponds to a distance D, the zones of internal radii 0.167 D and 0.040 D will serve to measure the platelets and the white cells and it will suffice to shift the sample cell through a distance of about D/ l .8 to measure the red cells and the hematocrit with the same window.
  • a process for the instantaneous counting of the various particles in suspension in a sample of blood and for determining the hematocrit and average red blood cell volume comprising the steps of:
  • placing step is accomplished by placing a single blood sample for analysis in said light beam and supplementing said blood initially by a quantity of spherizing liquid sufficient to spherize the red cells and subsequently with a quantity of hemolyzing liquid sufficient to hemolyze the red cells to form stromata.
  • An apparatus for the instantaneous counting of the various particles in suspension in a sample of blood and for determining the hematocrit and average red cell volume comprising:
  • c. at least one cell which serves as a receptacle for the blood to be analyzed, said cell being placed on the trajectory of the light beam;
  • a screen placed in the focal plane of the optical system and containing at least two windows whose internal edges and external edges correspond to the diffraction angles which are essentially equal respectively to the following:
  • f. means for transforming the fluxes into electrical signals characteristic of each type of particle and for displaying directly the results thereof.
  • said light source is a continuous laser and wherein said optical system includes a spatial filter at the internal focus thereof.
  • An apparatus in accordance with claim 6 including two of said cells, in one of which the red blood cells are spherized and in the other of which the red blood cells are hemolyzed and wherein the number of windows in said screen is two.
  • An apparatus in accordance with claim 6 further including means for shifting the cell in the course of the measurement in a space between the outer lens of said optical system and the focal plane thereof.
  • An apparatus in accordance with claim 6 wherein said screen has exactly three windows, two of which have internal and external edges corresponding to angles of type s and s and the third having internal and external edges corresponding to angles of the type s, and s 11.
  • An apparatus in accordance with claim 6 wherein said screen has exactly four windows, three of which have internal and external edges corresponding to angles of type s and s and the fourth having internal and external edges corresponding to angles of the type s and s' 12.
  • said means for measuring the diffracted light fluxes comprise photosensitive cells mounted behind each window and wherein each of said cells is associated with said means for transforming the fluxes into electri-

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US00386280A 1972-08-10 1973-08-07 Process and apparatus for counting biological particles Expired - Lifetime US3830569A (en)

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JP (1) JPS49125097A (enrdf_load_stackoverflow)
BE (1) BE803075A (enrdf_load_stackoverflow)
DE (1) DE2340252A1 (enrdf_load_stackoverflow)
ES (1) ES417763A1 (enrdf_load_stackoverflow)
FR (1) FR2195907A5 (enrdf_load_stackoverflow)
GB (1) GB1400640A (enrdf_load_stackoverflow)
IT (1) IT1008026B (enrdf_load_stackoverflow)
NL (1) NL7310960A (enrdf_load_stackoverflow)

Cited By (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3923397A (en) * 1974-05-29 1975-12-02 Dolive Stephen E Hematocrit measuring method
US3930726A (en) * 1974-05-29 1976-01-06 Reginald C. Shuck System for measuring volumetric ratios of liquid suspended solids
US3990851A (en) * 1974-02-27 1976-11-09 Behringwerke Aktiengesellschaft Process and device for measuring antigen-antibody reactions
US4052600A (en) * 1975-01-06 1977-10-04 Leeds & Northrup Company Measurement of statistical parameters of a distribution of suspended particles
US4139303A (en) * 1977-01-21 1979-02-13 The Board Of Regents Of The University Of Washington Adaptive coherent optical processing method and apparatus for recognizing and counting objects
JPS5537998A (en) * 1978-09-06 1980-03-17 Ortho Diagnostics Method of and apparatus for detecting blood plasma plate in all blood
US4303336A (en) * 1978-08-28 1981-12-01 Baxter Travenol Laboratories, Inc. Method and apparatus for making a rapid measurement of the hematocrit of blood
US4441816A (en) * 1982-03-25 1984-04-10 The United States Of America As Represented By The United States Department Of Energy Optical double-slit particle measuring system
US4522494A (en) * 1982-07-07 1985-06-11 The United States Of America As Represented By The Department Of Health And Human Services Non-invasive optical assessment of platelet viability
EP0207176A1 (de) * 1985-06-07 1987-01-07 Fritsch GmbH Gerät zur Bestimmung von Korngrössen
WO1988007198A1 (en) * 1987-03-13 1988-09-22 Coulter Electronics, Inc. Multi-part differential analyzing apparatus utilizing light scatter techniques
EP0575712A3 (en) * 1992-03-31 1994-06-08 Univ Manitoba Spectrophotometric blood analysis
US5601080A (en) * 1994-12-28 1997-02-11 Coretech Medical Technologies Corporation Spectrophotometric blood analysis
EP0696731A3 (en) * 1994-08-08 1997-10-15 Toa Medical Electronics Cytoanalyzer
US5844685A (en) * 1996-07-30 1998-12-01 Bayer Corporation Reference laser beam sampling apparatus
US5872627A (en) * 1996-07-30 1999-02-16 Bayer Corporation Method and apparatus for detecting scattered light in an analytical instrument
US5936729A (en) * 1996-03-26 1999-08-10 Horiba, Ltd. Photo detector assembly for measuring particle sizes
US6041246A (en) * 1997-10-14 2000-03-21 Transonic Systems, Inc. Single light sensor optical probe for monitoring blood parameters and cardiovascular measurements
US20030130570A1 (en) * 1997-10-14 2003-07-10 Transonic Systems, Inc. Sensor calibration and blood volume determination
US20050255600A1 (en) * 2004-05-14 2005-11-17 Honeywell International Inc. Portable sample analyzer cartridge
US20110222050A1 (en) * 2010-03-10 2011-09-15 Sony Corporation Optical measuring device and optical measuring method
CN103487362A (zh) * 2013-10-16 2014-01-01 中国工程物理研究院激光聚变研究中心 一种激光粒子测量探头
US9280726B2 (en) 2009-12-18 2016-03-08 Fpinnovation On-line macrocontaminant analyser and method
CN107941662A (zh) * 2017-11-10 2018-04-20 吉林大学 一种利用强场激光检测火焰内颗粒物分布的装置与方法
US10473519B2 (en) * 2013-03-15 2019-11-12 Beckman Coulter, Inc. Radiated light filtering for a flow cytometer
US20220412866A1 (en) * 2019-11-22 2022-12-29 Ams Ag Optical particle counter for air quality assessment
CN119880716A (zh) * 2025-03-27 2025-04-25 烟台格藻生物科技有限公司 应用于生物信息的细胞数量测量方法

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2445523A1 (fr) * 1978-12-28 1980-07-25 Sable Sarl Procede pour mesurer le volume des matieres en suspension dans un liquide
DE2964764D1 (en) * 1978-12-28 1983-03-17 Omnium Assainissement Method of measuring the volume of suspended matter in a liquid with special application to the automatic determination of the quality of water
US4274741A (en) * 1979-09-26 1981-06-23 Compagnie Industrielle Des Lasers Device for determining the granulometric composition of a mixture of particles by diffraction of light
US4412004A (en) * 1981-06-26 1983-10-25 Technicon Instruments Corporation Method for treating red blood cells to effect sphering and reagent therefor
FR2521294A1 (fr) * 1982-02-05 1983-08-12 Bajard Jean Procede de granulometrie interferentielle globale applicable notamment a des particules biologiques polydispersees
JPS63215942A (ja) * 1987-03-04 1988-09-08 Natl Aerospace Lab 粒子径分布計測用光電変換センサ−
CN110542686A (zh) * 2019-09-30 2019-12-06 广东牧玛生命科技有限公司 一种多功能分析仪器

Cited By (40)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3990851A (en) * 1974-02-27 1976-11-09 Behringwerke Aktiengesellschaft Process and device for measuring antigen-antibody reactions
US3923397A (en) * 1974-05-29 1975-12-02 Dolive Stephen E Hematocrit measuring method
US3930726A (en) * 1974-05-29 1976-01-06 Reginald C. Shuck System for measuring volumetric ratios of liquid suspended solids
US4052600A (en) * 1975-01-06 1977-10-04 Leeds & Northrup Company Measurement of statistical parameters of a distribution of suspended particles
US4139303A (en) * 1977-01-21 1979-02-13 The Board Of Regents Of The University Of Washington Adaptive coherent optical processing method and apparatus for recognizing and counting objects
US4303336A (en) * 1978-08-28 1981-12-01 Baxter Travenol Laboratories, Inc. Method and apparatus for making a rapid measurement of the hematocrit of blood
JPS5537998A (en) * 1978-09-06 1980-03-17 Ortho Diagnostics Method of and apparatus for detecting blood plasma plate in all blood
US4441816A (en) * 1982-03-25 1984-04-10 The United States Of America As Represented By The United States Department Of Energy Optical double-slit particle measuring system
US4522494A (en) * 1982-07-07 1985-06-11 The United States Of America As Represented By The Department Of Health And Human Services Non-invasive optical assessment of platelet viability
EP0207176A1 (de) * 1985-06-07 1987-01-07 Fritsch GmbH Gerät zur Bestimmung von Korngrössen
US4755052A (en) * 1985-06-07 1988-07-05 Fritsch Gmbh Apparatus for determining grain size
WO1988007198A1 (en) * 1987-03-13 1988-09-22 Coulter Electronics, Inc. Multi-part differential analyzing apparatus utilizing light scatter techniques
AU632393B2 (en) * 1987-03-13 1992-12-24 Coulter International Corporation Multi-part differential analyzing apparatus utilizing light scatter techniques
EP0575712A3 (en) * 1992-03-31 1994-06-08 Univ Manitoba Spectrophotometric blood analysis
US5331958A (en) * 1992-03-31 1994-07-26 University Of Manitoba Spectrophotometric blood analysis
EP0696731A3 (en) * 1994-08-08 1997-10-15 Toa Medical Electronics Cytoanalyzer
US5737078A (en) * 1994-08-08 1998-04-07 Toa Medical Electronics Co., Ltd. Cytoanalyzer using separate sensing portions on a dectector and method for aligning the same
US5601080A (en) * 1994-12-28 1997-02-11 Coretech Medical Technologies Corporation Spectrophotometric blood analysis
US5936729A (en) * 1996-03-26 1999-08-10 Horiba, Ltd. Photo detector assembly for measuring particle sizes
US5844685A (en) * 1996-07-30 1998-12-01 Bayer Corporation Reference laser beam sampling apparatus
US5872627A (en) * 1996-07-30 1999-02-16 Bayer Corporation Method and apparatus for detecting scattered light in an analytical instrument
US7734322B2 (en) 1997-10-14 2010-06-08 Transonic Systems, Inc. Blood volume determination and sensor calibration
US6041246A (en) * 1997-10-14 2000-03-21 Transonic Systems, Inc. Single light sensor optical probe for monitoring blood parameters and cardiovascular measurements
US6493567B1 (en) 1997-10-14 2002-12-10 Transonic Systems, Inc. Single light sensor optical probe for monitoring blood parameters and cardiovascular measurements
US20030130570A1 (en) * 1997-10-14 2003-07-10 Transonic Systems, Inc. Sensor calibration and blood volume determination
US6718190B2 (en) 1997-10-14 2004-04-06 Transonic Systems, Inc. Sensor calibration and blood volume determination
US8540946B2 (en) 2004-05-14 2013-09-24 Honeywell International Inc. Portable sample analyzer cartridge
US8071051B2 (en) * 2004-05-14 2011-12-06 Honeywell International Inc. Portable sample analyzer cartridge
US20050255600A1 (en) * 2004-05-14 2005-11-17 Honeywell International Inc. Portable sample analyzer cartridge
US9280726B2 (en) 2009-12-18 2016-03-08 Fpinnovation On-line macrocontaminant analyser and method
US20110222050A1 (en) * 2010-03-10 2011-09-15 Sony Corporation Optical measuring device and optical measuring method
US8780338B2 (en) * 2010-03-10 2014-07-15 Sony Corporation Optical measuring device and optical measuring method
US9766174B2 (en) 2010-03-10 2017-09-19 Sony Corporation Optical measuring device and optical measuring method
US10473519B2 (en) * 2013-03-15 2019-11-12 Beckman Coulter, Inc. Radiated light filtering for a flow cytometer
CN103487362B (zh) * 2013-10-16 2015-09-23 中国工程物理研究院激光聚变研究中心 一种激光粒子测量探头
CN103487362A (zh) * 2013-10-16 2014-01-01 中国工程物理研究院激光聚变研究中心 一种激光粒子测量探头
CN107941662A (zh) * 2017-11-10 2018-04-20 吉林大学 一种利用强场激光检测火焰内颗粒物分布的装置与方法
US20220412866A1 (en) * 2019-11-22 2022-12-29 Ams Ag Optical particle counter for air quality assessment
US12345638B2 (en) * 2019-11-22 2025-07-01 Ams Ag Optical particle counter for air quality assessment
CN119880716A (zh) * 2025-03-27 2025-04-25 烟台格藻生物科技有限公司 应用于生物信息的细胞数量测量方法

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DE2340252A1 (de) 1974-02-21
FR2195907A5 (enrdf_load_stackoverflow) 1974-03-08
JPS49125097A (enrdf_load_stackoverflow) 1974-11-29
NL7310960A (enrdf_load_stackoverflow) 1974-02-12
IT1008026B (it) 1976-11-10
GB1400640A (en) 1975-07-16
ES417763A1 (es) 1976-02-16
BE803075A (fr) 1973-11-16

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