GB2544196A - Portable real-time biological aerosol-detecting device - Google Patents
Portable real-time biological aerosol-detecting device Download PDFInfo
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- GB2544196A GB2544196A GB1618659.5A GB201618659A GB2544196A GB 2544196 A GB2544196 A GB 2544196A GB 201618659 A GB201618659 A GB 201618659A GB 2544196 A GB2544196 A GB 2544196A
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Classifications
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- 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
- G01N15/10—Investigating individual particles
- G01N15/14—Electro-optical investigation, e.g. flow cytometers
- G01N15/1434—Electro-optical investigation, e.g. flow cytometers using an analyser being characterised by its optical arrangement
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- 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
- G01N15/10—Investigating individual particles
- G01N15/14—Electro-optical investigation, e.g. flow cytometers
- G01N15/1456—Electro-optical investigation, e.g. flow cytometers without spatial resolution of the texture or inner structure of the particle, e.g. processing of pulse signals
- G01N15/1459—Electro-optical investigation, e.g. flow cytometers without spatial resolution of the texture or inner structure of the particle, e.g. processing of pulse signals the analysis being performed on a sample stream
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- G—PHYSICS
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
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- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
- G01N21/33—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using ultraviolet light
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
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- 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
- G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
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- 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
- G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
- G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
- G01N21/64—Fluorescence; Phosphorescence
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
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- G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
- G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
- G01N21/64—Fluorescence; Phosphorescence
- G01N21/6486—Measuring fluorescence of biological material, e.g. DNA, RNA, cells
Abstract
A portable real-time biological aerosol-detecting device including a particle collecting unit (200, fig. 1) into which particles dispersed in air are introduced, a particle concentrating unit (350, fig. 1) installed in a main body case, and a particle-optical measurement unit (300, fig. 1). The particle-optical measurement unit includes: an optical chamber having a measurement space S therein; a beam forming optical system 320 that irradiates a particle introduced into the measurement space with a UV-LED beam L; a beam dump 330 that extinguishes the UV-LED beam emitted from the beam-forming optical system; two reflectors (370, fig. 3) arranged in the measurement space; a particle discharging unit 240 that discharges the particle from the measurement space after the particle interacts with the UV-LED beam; a beam-splitting optical system (340, fig. 5) that detects scattered light and fluorescent light that are generated due to interaction between the UV-LED beam and the particle in the measurement space; and a battery power supply. The beam dump comprises an opening (334, fig. 5) into which light reflected from a detector surface is extinguished.
Description
PORTABLE REAL-TIME BIOLOGICAL AEROSOL-DETECTING DEVICE BACKGROUND OF THE INVENTION 1. Field of the Invention
The present invention relates to a biological aerosol-detecting device that measures the concentration of a biological aerosol dispersed in the air and provides an audio or visual alarm signal when the presence of a toxic biological aerosol in the air is detected. The present invention more particularly relates to a portable real-time biological aerosol-detecting device that measures the concentration of a biological aerosol dispersed in the air by causing fine particles dispersed in the air to move to a detector, gathering scattered light and fluorescent light that are generated due to interaction between a light beam of an ultraviolet light-emitting diode (UV-LED) and a fine particle, and classifying the gathered light by wavelength band. The portable real-time biological aerosol-detecting device has a compact size and can be operated on batteries. For this reason, the portable real-time biological aerosol-detecting device can be used at any time or location. 2. Description of the Related Art
Recently the danger of biological terrorism attacks has increased because biological agents are easy to manufacture, carry, and disseminate. While a carrier is moving using public transportation or other fast transportation means during an incubation period of a biological agent, the biological agent can be disseminated over a wide area. Therefore, bioterrorism causes both psychological panic and economical disruption. As we learned from the economical and psychological damage caused by the Middle East Respiratory Syndrome (MERS) and the Severe Acute Respiratory Syndrome (SARS) that recently occurred in many countries, if there were an intentional release of deadly viruses, severe panic would occur in society.
Therefore, it is necessary to detect biological agents that are intentionally spread by a terrorist and to take prompt and proper actions in real time. However, since biological agents are present in the form of fine particles or aerosol particles that are not visible, it is difficult to visually check for the presence of toxic or harmful biological agents in the air. Therefore, a specific detecting device for detecting biological agents is needed.
Biological aerosol particles such as bacteria, viruses, or fungi are collected through a typical sampling method and cultured in a medium for several hours or several days. That is, an air sample is collected to detect harmful biological agents among various particles and agents that are present in the air, and then the sample is cultured in a medium. After that, the number of colonies is counted to measure the amount of biologic aerosols or to identify the kinds of biological agents in the collected sample. In this way, the presence of biological agents is identified.
This method has many problems. First, the culture time is usually 24 hours or longer. Second, the processes of sampling, culturing, and counting of biological agents need to be periodically repeated. Third, the detection result can only be obtained after several hours or several days because of the long culture time. Above all, knowing the point of time at which it is necessary to screen for harmful biological agents is impossible. Therefore, the periodic sampling of air and identification of biological agents have to be performed at regular time intervals, and such processes are costly, laborious, and time-consuming.
There is another method of detecting and identifying biological agents. This method uses a Polymerase Chain Reaction (PCR) device that can analyze a collected air sample to identify biological agents in the sample in only several hours. However, this method also needs to continuously detect biological agents at predetermined time intervals. Therefore, this method also incurs huge cost and requires many man hours.
Therefore, at the present time, a Laser Induced Fluorescence (LIF) method is usually used to reduce time and cost attributable to continuous culturing of biological agents and overcomes the problem that it is difficult to specify the point of time at which it is necessary to screen for harmful biological agents in the air. LIF is a spectroscopic method used for detection of biological agents and analysis of harmfulness of biological agents, based on scattered light and fluorescent light that are generated when a biological agent is irradiated with a laser beam.
When it is necessary to detect and measure the concentration of biological agents to be examined in real time with an existing real-time biological aerosol-detecting device, the device needs to be transported to a site to be examined. However, since the device is large and consumes a large amount of electric power, the device is used as being mounted in a large vehicle so as to be easily transported or the device is used as a fixed device at a predetermined place.
SUMMARY OF THE INVENTION
Accordingly, the present invention has been made keeping in mind the above problems occurring in the prior art, and an object of the present invention is to provide a portable real-time biological aerosol-detecting device that provides an alarm signal when harmful biological agents are detected in real time, based on information that is obtained by collecting a fine particle dispersed in air, irradiating the fine particle with a ultraviolet ray using a ultraviolet light-emitting diode (UV-LED), collecting scattered light and fluorescent light that come from the fine particle, and classifying the collected light by wavelength band to produce spectra. The portable real-time biological aerosol-detecting device has a compact size so as to be portable and can be operated on batteries, thus it can be conveniently used at any time or location.
In order to accomplish the object of the invention, one aspect of the present invention provides a portable real-time biological aerosol-detecting device including: a particle collecting unit 200 that is installed at an upper end of an outside surface of a main body case 100 and includes a sorter that sorts out coarse particles when particles are introduced into a main body of the portable real-time biological aerosol-detecting device, and a body 202 that is connected to the sorter 201 through a channel; a particle-optical measurement unit 300 that is installed in the main body case 100, is connected to a lower end of the particle collecting unit 200, and detects aerosol particles dispersed in the air and introduced along the channel formed in the body 200, the particle-optical measurement unit 300 having an opening at an upper end thereof; a parallelepiped optical chamber 360 that is connected to a lower end of a particle concentrating unit 250 through the opening 301 and has a measurement space S in the inside thereof; a beam-forming optical system 320 that is connected to an opening 303 formed in a side surface of the optical chamber 360 and irradiates a particle introduced into the measurement space S through the particle concentrating unit 250 with a ultraviolet light-emitting diode (UV-LED) beam L; a beam dumper 330 that faces the beamforming optical system 320 and is connected to an opening 340 formed in a side surface of the optical chamber 360 so as to extinguish the UV-LED beam that has passed the measurement space S after being emitted from the beam-forming optical system 320; two reflectors 370 that are arranged in the measurement space S to be at a right angle (90°) with respect to a direction in which the UV-LED beam progresses; a particle discharging unit 240 that is connected to an opening 302 formed in a lower surface of the optical chamber 360 so as to discharge air that has undergone interaction with the UV-LED beam L in the measurement space S to an outside through a nozzle 241; and a beam-splitting optical system 340 that is arranged to be perpendicular to the beam-forming optical system 320 and connected to an opening 305 formed in a front surface of the optical chamber 360 so as to receive scattered light and fluorescent light that are generated due to interaction between the UV-LED beam and the particle in the measurement space S and to classify the received light by wavelength band.
The detecting device includes an electronic circuit 600 that is installed in the main body case 100, converts an optical signal measured by the particle-optical measurement unit 300 into a digital signal, and controls a sensor and a UV-LED 253 that are installed in the main body case 100.
The beam-splitting optical system 320 has an internal chamber with open ends in which a light source unit 310, a first lens 255, a band pass filter 256, a second lens 257, and a window 258 are arranged in this order, in which: the light source unit 310 is angle-adjustable and includes a light source circuit 700 that includes the UV-LED 253 and is fixed to the beam-forming optical system; the first lens 255 is separable from the light source unit 310 and collimates a UV-LED beam generated by the UV-LED 253; the band pass filter 256 eliminates a fluorescent light component from the UV-LED beam L that has passed through the first lens 255; the second lens 257 adjusts a size of the beam that has passed through the band pass filter 256; and the window 258 is coated such that the UV-LED beam L can pass through the window 258.
The light source unit 310 has an angle-adjustable structure such that an angle of the light source unit 310 with respect to the first lens 255, the band pass filter 256, or the second lens 257 that are components of the beam-forming optical system 320 can be adjusted, thereby changing a direction of the UV-LED beam so that the UV-LED beam can reach a desired spot in the optical chamber 360.
The UV-LED beam emitted from the UV-LED 253 is first collimated by passing through the first lens 255, then looses a fluorescent light component by passing through the band pass filter 256, and is finally changed into a predetermined pattern by passing through the second lens 257.
The electronic circuit 600 monitors and controls power consumption of the UV-LED because the UV-LED operates on a battery, and the electronic circuit 600 includes: a light source circuit 700 that controls supply of power to a pump 350 that pumps air into the measurement space S of the optical chamber; a signal measurement circuit 702 that measures an optical signal using a scattering detector 720 and a fluorescence detector 730; an output measurement circuit 701 that measures intensity of the UV-LED beam L that has passed through the beam dumper 330; and a micro controller unit (MCU) that analyzes concentration of particles contained in the introduced air and gives a user visual or audio information on the particles. With this structure, it is possible to increase battery operation time by reducing power consumption through efficient calculation of the MCU.
The main body case 100 may be provided with an audiovisual unit 230 that gives an audio or visual alarm signal over the presence of biological aerosol, battery power consumption, device malfunctioning or the like. A handle 210 is provided on an upper end of an outside surface of the main body case 100 so as to allow a user to conveniently hold and carry the portable real-time biological aerosol-detecting device. The handle 210 has an opening at an end so that the particle collecting unit 200 can be introduced into the handle 210 through the opening so as to be received in the handle 210.
The beam-splitting optical system 340 includes the scatting detector 720 and the fluorescence detector 730 that respectively and simultaneously detect scattered light and fluorescent light according to a cut-off frequency of a dichroic mirror 342. The scattering detector 720 is equipped with a filter 343 that is arranged in the front side thereof, blocks fluorescent light, and allows scattered light to pass through. The fluorescence detector 730 is equipped with a filter 346 that is installed in the front side thereof, blocks scattered light, and allows guided fluorescent light to pass through.
The scattering detector 720 and the fluorescence detector 730 each may be a photomultiplier tube (PMT) that operates at low temperatures or an avalanche photo diode (APD) and may additionally include an amplifier.
The portable real-time biological aerosol-detecting device according to the present invention operates on batteries in consideration of mobility and uses a UV-LED that consumes less power. Therefore, the portable real-time biological aerosol-detecting device according to the present invention has increased operation time and can be easily carried. The portable real-time biological aerosol-detecting device according to the present invention is an aerosol detecting device having increased operation time. It collects particles dispersed in air, irradiates a single particle with a UV-LED beam, and detects and classifies scattered light and fluorescent light generated during the irradiation of the UV-LED beam by wavelength band. Therefore, it increases accuracy of detection of biological aerosol particles using a coincidence signal processing method and can analyze the state of air in real time.
In addition, according to the present invention, a pulse height analysis (PHA) method is applied to a low power consumption technology so that the device can operate on batteries. Therefore, the detecting device according to the present invention can more precisely perform photon counting analysis and can improve accuracy of particle size measurement and fluorescence measurement by automatically controlling the output of the UV-LED using an output measurement circuit installed in the beam dumper when the surrounding environment such as temperature or humidity changes.
In addition, according to the present invention, scattered light and fluorescent light are not separately measured but all optical signals are collectively picked up and then a desired signal is separated from the collected optical signals by a dichroic mirror. Therefore, it is possible to dramatically increase intensity of an optical signal and reduce consumption of battery power.
In addition, according to the present invention, two reflectors are used and the size and arrangement of the reflectors and a gap size between nozzles and the diameter of a nozzle are minimized. In this way, all optical signals that are generated in the measurement space and radiated in all directions are collected, so that the size of a fine particle and weak fluorescent light can be measured. Moreover, the present invention uses a 90° side wall scattering measurement method to overcome noise vulnerability of a conventional forward scattering measurement method. The present invention also includes a band pass filter installed between two lenses of the beam-forming optical system 320, thereby blocking fluorescent light contained in the UV-LED beam. This prevents mixing of fluorescent light contained in the UV-LED beam and fluorescent light emitted from biological aerosol particles, thereby increasing an Signal-to-Noise Ratio (SNR).
In addition, in order to send optical signals that are collected by two reflectors to the beamsplitting optical system, the center of a spherical reflector of the two reflectors is not bored and the optical signals are made to pass through an uncoated portion or a non-reflective film coated portion. In addition, since an internal sealing structure is applied to the optical chamber, it is possible to eliminate use of an Ο-ring, a window, and a bolting structure.
In addition, according to the present invention, a photomultiplier tube (PMT) that is operable at low temperatures and compensation algorithm are applied in consideration of a point that the PMT does not operate in cold and freezing weather. Therefore, the detecting device can operate without additional heating.
In addition, according to the present invention, since all components are unified as a module, the components are easily attached or detached to the optical chamber so as to be easily replaced or cleaned. Since the beam-splitting optical system has a structure in which the dichroic mirror can be easily replaced, a user can freely select a desired wavelength of fluorescent light by replacing the UV-LED.
In addition, according to the present invention, it is possible to identify a range of intensity of fluorescent light according to the size of a particle and the intensity of fluorescent light, thereby preliminarily eliminating measurement of unnecessary particles and reducing a false alarm.
In addition, the detecting device of the present invention can be conveniently used as a detecting device because it can be easily carried and transported and can accurately and promptly monitor, in real-time, biological aerosol particles contained in harmful biological agents that are intentionally spread from the vicinity of a dangerous facility or by a terrorist.
BRIEF DESCRIPTION OF THE DRAWINGS
The above and other objects, features and advantages of the present invention will be more clearly understood from the following detailed description taken in conjunction with the accompanying drawings, in which: FIG. 1 is a view illustrating appearance of a portable real-time biological aerosol-detecting device according to one embodiment of the present invention; FIG. 2 is an exploded perspective view of a particle-optical measurement unit according to one embodiment of the present invention; FIG. 3 is a cross-sectional view of the particle-optical measurement unit, which is viewed from one side, according to one embodiment of the present invention; FIG. 4 is a cross-sectional view illustrating an optical chamber according to one embodiment of the present invention; FIG. 5 is an exploded perspective view illustrating a particle collecting unit according to one embodiment of the present invention; FIG. 6 is a cross-sectional view of the particle-optical measurement unit, which is viewed from the top, according to one embodiment of the present invention; and FIG. 7 is a diagram illustrating an optical system according to one embodiment of the present invention.
DETAILED DESCRIPTION OF THE INVENTION
Hereinbelow, exemplary embodiments of the present invention will be described in detail with reference to the accompanying drawings. Throughout the drawings, the same reference numerals will refer to the same or like parts.
Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings. These embodiments may be embodied in many different forms by those who skilled in the art and the present invention is not limited to the embodiments described herein. A portable real-time biological aerosol-detecting device according to one embodiment of the present invention is a device that operates on a battery and monitors in real time the concentration of biological aerosol particles that emit fluorescent light by classifying fluorescent light of biological aerosol particles and weak scattered light that is generated when irradiating a particle existing in the air with a UV-LED beam by wavelength band. The detecting device includes a main body case 100 and a battery power supply 400 as illustrated in FIG. 1. A particle collecting unit 200, a handle 210, and an audiovisual unit 230 are installed at an upper end of the main body case 100. In the inside of the main body case 100, a pump 350, a particle-optical measurement unit 300, and an electronic circuit 600 are arranged. A battery power supply 400 is fixed to a lower end of the main body case 100. The battery power supply 400 includes a body 410 and a battery 420.
The particle collecting unit 200 includes a sorter 201 that sorts out large particles such as coarse particles contained in the externally introduced air using inertia force. Therefore, it is possible to prevent contaminants or unnecessary particles from being introduced into the particle-optical measurement unit 300 installed in the main body case 100. An inside of the particle collecting unit 200 is provided with a tubular body 202 through which particles can pass and which communicates with the atmosphere.
The particle collecting unit 200 has an inner nozzle 251 and an outer nozzle 252, and a particle concentrating unit 250 is connected to an upper end of the particle collecting unit 200 through the nozzles through which air and particles can move to a measurement space S in the optical chamber 360. Clean air can be introduced through the outer nozzle 252. The nozzle of the particle collecting unit surrounds a sample flow introduced from an outside with a sheath flow and transports the sample flow to a particle discharging unit, thereby preventing fine particles escaping the measurement space from floating in the optical chamber and adhering to the surfaces of two reflectors 370. That is, it is possible to prevent contamination of the surface of the reflectors.
The handle 210 has a hollow space in the center so that the particle collecting unit 200 can be accommodated in the hollow space of the handle while the detecting device is carried.
The audiovisual unit 230 includes a light-emitting diode (LED) and a buzzer that respectively provides an audio alarm signal and a visual alarm signal when the battery is about to expire, when device malfunctioning occurs, when device maintenance is needed, or when harmful biological aerosol particles are detected.
The pump 350 pumps particles dispersed in air into the optical chamber through the particle collecting unit 200 and automatically controls the flow rate of introduced air for accurate measurement of concentration of particles for each particle size.
As illustrated in FIGS. 2 to 4, the particle-optical measurement unit 300 installed in the main body case 100 includes the particle concentrating unit 250, the optical chamber 360, the particle discharging unit 240, the reflectors 370 and 380, a light source unit 310, a beam-forming optical system 320, a beam dumper 330, and a beam-splitting optical system 340.
As illustrated in FIGS. 2 to 4, the optical chamber 360 has a parallelepiped body with the measurement space S therein. The top surface, bottom surface, front surface, rear surface, right surface and left surface of the optical chamber 360 that are named with reference to the front surface of the particle-optical measurement unit 300 are provided with respective openings 301, 302, 303, 304, 305, and 306. The particle concentrating unit 250 and the particle discharging unit 240 are respectively installed on the top and bottom surfaces of the optical chamber 360 through the openings. The beam-forming optical system 320 and the beam dumper 330 are arranged to face each other and are thus respectively installed on the front and rear surfaces of the optical chamber 360. The beam-splitting optical system 340 is installed on the right surface of the optical chamber 360 with reference to the front surface of the beam-forming optical system 320 of the particle-optical measurement unit 300.
As illustrated in FIG. 4, the left-side opening 306 formed in the left surface of the optical chamber 360 is provided with a non-spherical reflector 372, and the right-side opening 305 formed in the right surface of the optical chamber 360 is provided with a spherical reflector 371. The non-spherical reflector 372 and the spherical reflector 371 are fixed to the optical chamber 360.
The rims of the openings 301, 302, 304, 303, 305, and 306 of the optical chamber 360 each may be provided with an O ring for hermetic sealing of the optical chamber 360. All surfaces of the optical chamber 360 having a parallelepiped shape are blackened to effectively absorb stray light.
The particle concentrating unit 250 moves an incoming particle introduced through the particle collecting unit 200 to the measurement space S of the optical chamber 360 through the nozzle thereof. As illustrated in FIG. 5, the nozzle includes the inner nozzle 251 and the outer nozzle 252. Clean air is introduced through the outer nozzle 252 to surround particle-containing air introduced through the inner nozzle 251, and the particle-containing air is sent to the measurement space S as it is surround by the clean air. This minimizes contamination of the inside of the optical chamber 360 attributable to particles that are not discharged through the particle discharging unit 240 but still remain in the optical chamber 360.
The particle concentrating unit 250 is connected to the particle collecting unit 200 via a quick connector so that the particle concentrating unit 250 can be removed from the main body and accommodated in the internal space of the handle 210 when the detecting device is carried.
As illustrated in FIGS. 3 and 4, in order to reduce the effect of attachment/detachment of the particle concentrating unit 250 on accuracy of particle size measurement, an eccentricitypreventing slop structure having a reversed circular cone shape that tapers to the opening 301 formed in the top surface of the optical chamber 360 connected to the particle concentrating unit 250 may be provided.
Specifically, when cleaning the particle concentrating unit 250 or the optical chamber 360 in an extreme environment or a yellow-dust alarm state, the particle concentrating unit 250 is disassembled from the optical chamber 360 and then reassembled after cleaning. In this case, when the lower end of the particle concentrating unit 250 is not precisely fitted into the opening 301 in the top surface of the optical chamber 360, a central axis of the particle concentrating unit 250 is displaced from an intended installation position in measurement space S of the optical chamber 360. In this case, a UV-LED beam cannot reach a precise position, which deteriorates accuracy of measurement of particle size or measurement of intensity of fluorescent light.
Therefore, a reversed circular cone shaped structure may be provided in a contact surface at which the lower end of the particle concentrating unit 250 comes into contact with the opening 301 in the top surface of the optical chamber 360. This structure prevents displacement of the central axis of the nozzle when the particle concentrating unit 250 is reassembled with the optical chamber 360, and increases endurance against vibration attributable to an external impact to the detecting device.
In order to solve this problem, the present invention uses a structure in which the contact surface between the lower end of the particle concentrating unit 250 and the opening 301 of the top surface of the optical chamber 360 is processed to have a reversed circular cone shape. This structure prevents displacement of the central axis of the nozzle when the particle concentrating unit 250 is reassembled with the optical chamber 360, and increases endurance against vibration attributable to an external impact to the detecting device.
In the state in which the particle concentrating unit 250 is assembled with the optical chamber 360, air that contains particles and is introduced into the optical chamber 360 interacts with the UV-LED beam L in the measurement space S of the optical chamber 360 and is then discharged to a filter through a discharge nozzle 241 of the particle discharging unit 240.
As illustrated in FIGS. 4 and 6, the two reflectors 370 include a spherical reflector 371 that is coaxially installed with the beam-splitting optical system 340 and a non-spherical reflector 372 having a central axis that agrees with a direction in which the non-spherical reflector faces the spherical reflector 371. The spherical reflector 371 and the non-spherical reflector 372 are arranged at a right side and a left side of a direction in which the UV-LED beam progress and at a right angle (90°) with respect to the direction in which the UV-LED beam L progresses. This arrangement maximizes the ability to collect weak side scattering light and fluorescent light, thereby increasing a signal-to-noise ratio (SNR).
The spherical reflector 371 is a reflector made of a glass material and the non-spherical reflector 372 is made up of an aluminum structure and a glass reflector attached to the aluminum structure. In the non-spherical reflector 372, an O ring may be installed between the aluminum structure and the glass reflector to prevent intrusion of external air.
The surface of the two reflectors 370 may be coated so as not to be damaged by impurities that are externally introduced through the particle concentrating unit 350 or ultraviolet rays. However, a center portion of the spherical reflector 371 may not be provided with a coating so that fluorescent light of a biological aerosol particle and scattered light that is scattered from the particle are reflected by the non-spherical reflector 372 and are directed to the beam-splitting optical system when the UV-LED beam L generated by the beam-forming optical system 320 impinges on the particle introduced into the particle concentrating unit 350. With this structure, it is possible to increase a coating area by which weak scattered light and fluorescent light can be collected.
The two reflectors 370 installed in the optical chamber 350 may be fixed to sealing plates 307 and 308 that can be detachably attached to the right-side opening 305 and the left-side opening 306 formed in the right and left surfaces of the optical chamber 360 so that cleaning can be easily performed.
The particle discharging unit 240 includes: a discharging nozzle 241 that is arranged at the lower end of the optical chamber 360, in a manner that central axes thereof are aligned with each other, and is spaced from the inner nozzle 251 of the particle concentrating unit 250 by a predetermined distance; a body 242 connected to the discharging nozzle 241; and an exhaust port 243.
With this structure, it is possible to discharge the air, which contains fine particles and is introduced into the measurement space S of the optical chamber 360 through the inner nozzle 251 provided in the lower end of the particle concentrating unit 250, through the discharging nozzle 241 and the exhaust port 243. The discharging nozzle 241 and the inner nozzle 251 are tapered to the inside of the optical chamber 360 to prevent interference between scattered light and fluorescent light.
As illustrated in FIG. 6, the beam-forming optical system 320 has a structure with open ends. A light source unit 310 equipped with an ultraviolet light-emitting diode (UV-LED) 253 is formed at one end of the beam-forming optical system 320. In the inside of the beam-forming optical system 320, a first lens 255 that collimates a beam generated by the UV-LED 253, a band pass filter 256, a second lens 257, and a window 258 are arranged in this order. The band pass filter 256 blocks fluorescent light contained in the UV-LED beam L that has passed through the first lens 255 because a signal that is not fluorescent light, which is generated by interaction between the UV-LED beam and a biological aerosol particle, is likely to be detected as fluorescent light of the biological aerosol particle when a UV-LED that emits fluorescent light is used as a light source. The second lens 257 focuses the UV-LED beam collimated by the first lens 255 at a spot in the measurement space S of the optical chamber 360. The window 258 seals the optical chamber 360 and allows the UV-LED beam L to pass therethrough.
The inside of the beam-forming optical system 320 may undergo a blackening process to prevent intrusion of dust and external light. The first lens 255, the second lens 257, and the window 258 may be coated with a non-reflective film to minimize optical loss attributable to scattering of the UV-LED beam.
The UV-LED beam emitted from the light source unit 310 combined with the light source circuit 700 passes through the beam-forming optical system 320, thereby becoming a UV-LED beam with a predetermined pattern in its directions. An angle and a distance to a focus of the UV-LED beam may be slightly adjusted so that the UV-LED beam can be focused at a spot in the measurement space S of the optical chamber 360.
The light source circuit 700 monitors and controls power consumption of the UV-LED because the detecting device operates on batteries. It also controls power supplied to the pump 350 that pumps air into the measurement space S of the optical chamber through the particle collecting unit 200.
When the light source unit 310 and the beam-forming optical system 320 are misaligned due to vibrations or when the first lens 255, the band pass filter 256, the second lens 257, or the window 258 of the beam-forming optical system 320 is contaminated, the output of the UV-LED beam is decreased, which deteriorates accuracy of measurement on the particle size
Specifically, a short wavelength beam such as an ultraviolet ray usually reacts with dust, and the dust is likely to adhere to the first lens 255 or the second lens 257. Accordingly, the intensity of a beam that reaches the measurement space S is decreased as time passes. As a result, accuracy of measurement on particle size is deteriorated and the amount of fluorescent light that is detected is decreased.
This problem can be solved by measuring and controlling the output power of a photodiode included in an output measurement circuit 701 of the beam dumper 330.
The beam dumper 330 faces the beam-forming optical system 320 with the optical chamber 360 interposed therebetween. The beam dumper 330 includes a window 331 that seals the optical chamber 360, a beam dumper body 333 fixed to the rear surface of the optical chamber 360, a focusing lens 332 that is inserted in an opening formed in a center portion of the beam dumper body 333 and focuses the UV-LED beam that is emitted along an optical axis, an output measurement circuit 701 that is installed to be inclined at a predetermined angle with respect to a reference surface that is orthogonal to the optical axis of the focusing lens 332, and an opening 334 toward which the UV-LED beam L that is reflected from the photodiode of the output measurement circuit 710 progresses to be extinguished. The focusing lens may be a convex lens and may be arranged such that the UV-LED beam L progresses to the photodiode of the output measurement circuit 701.
The output measurement circuit 701 of the beam dumper 330 is inclined at an angle of 10° with respect to a reference surface that is perpendicular to an optical axis of the UV-LED beam L. Therefore, when the output measurement circuit 701 measures output intensity of the UV-LED beam L, the UV-LED beam L reflected from the photodiode of the output measurement circuit 701 is not reflected to the optical axis, larger than the angle between the inner inclined surface of the beam dumper body 333 from the reference surface to an acute angle but is extinguished by progressing to the opening 334 formed in the beam dumper 330. Therefore, the amount of the light beam is dramatically reduced.
When the beam-forming optical system 320 installed at a front end of the optical chamber 360 and the beam dumper 330 installed at a rear end of the optical chamber 360 are not aligned with the optical axis of the UV-LED beam L or when the UV-LED beam is not precisely incident on a spot in the measurement space S due to malfunctioning of the beam-forming optical system 320, the output of the output measurement circuit 701 changes. This change is detected and then notified to a user, or the output of the output measurement circuit 701 is adjusted. The output measurement of the output measurement circuit 701 is performed by a photodiode.
The beam dumper 330 seals the opening 304 in the rear surface of the optical chamber 360 with the window 331 to maintain the sealed state of the optical chamber 360. The inside and outside of the beam dumper 330 through which the UV-LED beam L passes are isolated from each other, thereby preventing external light from entering into the optical chamber. This improves accuracy and reliability of measurement.
The beam dumper 330 is structured such that the UV-LED beam L generated by the beam-forming optical system 320 progresses toward the measurement space S, is then incident on a fine particle in the measurement space S, then passes through the window 331, and finally reaches the output measurement circuit 701 through the focusing lens 332. The inside surface of the beam dumper 330 and all components of the beam dumper 330 undergo a blackening process.
As illustrated in FIGS. 2 and 6, the beam-splitting optical system 340 is connected to the right surface of the optical chamber 360. The spherical reflector 371 and the non-spherical reflector 372 that are respectively arranged on the right side and left side of the optical chamber 360 with respect to the measurement space S receive weakly focused scattered light and fluorescent light and classify the collected light by wavelength, thereby performing detection of a biological aerosol particle.
As illustrated in FIGS. 6 and 7, the beam-splitting optical system 340 includes a beamsplitting optical system body 347 that is installed in the direction of the spherical reflector 371 of the optical chamber 360 and has a penetrating structure, a chamber lens 341 that is installed in the beam-splitting optical system body 347 and is in contact with the spherical reflector 371, a dichroic mirror 342 that separates the UV-LED beam that enters through the chamber lens 341 into scattered light and fluorescent light, a fluorescent light-blocking filter 343 that allows only scattered light to pass through and blocks fluorescent light, a third lens 344 that causes the scattered light having passed through the fluorescent light-blocking filter to focus on a scattering detector 720, a scattered light-blocking filter 346 that allows only fluorescent light to pass through and blocks scattered light, and a fourth lens 345 that causes the fluorescent light having passed through the scattered light-blocking filter to focus on a fluorescence detector 730. The third lens 344 and the fourth lens 345 may be a focal lens having the same specification, so that the structure is simplified.
The dichroic mirror 342 can be easily attached or detached through the opening formed in the body 347. The dichoric mirror 342 is inclined at an angle of 45° with respect to the opening in the body. Therefore, when the wavelength of the UV-LED beam of the UV-LED 253 is changed, an old dichroic mirror may be easily replaced with a new dichroic mirror 342 that has different reflection characteristics with respect to scattered light.
The fluorescent light-blocking filter 343 and the scattered light-blocking filter 346 that are optical filters to pass only desired wavelengths are installed in front of the scattering detector 720 and the fluorescence detector 730, respectively.
The scattering detector 720 measures only scattered light that is generated through interaction between a particle and the UV-LED beam in the measurement space S of the optical chamber 360, and the fluorescence detector 730 measures fluorescent light generated through interaction between a particle and the UV-LED beam in the measurement space S of the optical chamber 360. The scattering detector 720 and the fluorescence detector 730 each may be a photomultiplier tube (PMT) that is operable at low temperatures and amplifies and measures weak scattered light and fluorescent light, or an avalanche photo diode (APD). A scattered light signal and a fluorescent light signal detected by the scattering detector 720 and the fluorescence detector 730 are converted into digital signals by the signal measurement circuit 702.
As has been described above, in the particle-optical measurement unit 300 of the portable real-time biological aerosol-detecting device, when a particle dispersed in air is introduced into the optical chamber 360 along with a predetermined amount of air through the particle concentrating unit 250, scattered light and fluorescent light are generated in the measurement space S of the optical chamber 360 by a fine particle that is subjected to the UV-LED beam that is emitted from the beam-forming optical system 320 and directed to the beam dumper 330.
The generated scattered light is detected by the scattering detector 720. When the dispersed particle is a biological aerosol particle, both fluorescent light and scattered light are generated. The generated scattered light and fluorescent light are detected by the scattering detector 720 and the fluorescence detector 730, respectively. The optical signals detected by the scattering detector 720 and the fluorescence detector 730 are converted into digital signals by the signal measurement circuit 702. In this way, it is possible to determine the presence or absence of harmful biological aerosol particles in the air, and to monitor changes in distribution of sizes and concentration of biological aerosol particles.
Although the present invention has been described in detail with reference to specific embodiments, those embodiments are provided only for illustrative purposes. Therefore, those embodiments are not intended to limit the scope of the present invention, but rather those skilled in the art will appreciate that various modifications, additions and substitutions are possible, without departing from the scope and spirit of the invention as disclosed in the accompanying claims. Further, simple changes and modifications of the present invention are appreciated as included in the scope and spirit of the invention, and the protection scope of the present invention will be defined by the accompanying claims.
Claims (6)
1. A portable real-time biological aerosol-detecting device, comprising: a particle collecting unit (200) that collects an aerosol particle dispersed in air; a particle-optical measurement unit(300) that is installed in a main body case (100) and detects a particle introduced thereinto, the particle-optical measurement unit (300) including an optical chamber (360), a beam-forming optical system (320), a beam dumper (330), a pair of reflectors (370), a particle discharging unit (240), and abeam-splitting optical system (340); and an electronic circuit (600) that is installed in the main body case (100), converts optical signals of scattered light and fluorescent light that are measured by the particle-optical measurement unit(300) into digital signals, and controls a circuit and a ultraviolet light-emitting diode (UV-LED) (253) installed in the main body case (100), wherein the beam-forming optical system (320) includes a light source unit (310), a first lens (255), a band pass filter (256), a second lens (257), and a window (258) that are arranged in this order in an internal chamber with open ends therein, the light source unit (310) is angle-adjustable and includes a light source circuit (700) that includes a ultraviolet light-emitting diode (UV-LED) (253) and is fixed to the beam-forming optical system; the first lens (255) is removable from the light source unit (310) and collimates a UV-LED beam emitted from the UV-LED (253); the band pass filter (256) eliminates a fluorescent light component contained in the UV-LED beam (L) that has passed the first lens (255); the second lens (257) adjusts the size of a beam that has passed the band pass filter (256); the window (258) is coated such that the UV-LED beam (L) passes through the window (258); and the beam-forming optical system (320) collimates the UV-LED beam emitted from the UV-LED (253) by passing the UV-LED beam through the first lens (255), eliminates the fluorescent light component from the collimated UV-LED beam by passing the collimated UV-LED beam through the band pass filter (256), and forms a predetermined pattern by passing the fluorescent light-free beam through the second lens, the electronic circuit (600) monitors and controls power consumption of the UV-LED because the UV-LED operates on a battery and includes: the light source circuit (700) that controls power supplied to a pump (350) that pumps air into a measurement space (S) of the optical chamber (360) through the particle collecting unit (200); a signal measurement circuit (702) that measures an optical signal in the beam-splitting optical system (340); an output measurement circuit (701) that measures intensity of the UV-LED beam (L) that has passed through the beam dumper (330); and a micro controller unit (MCU) that analyzes concentration of collected particles and provides a user with audio information or visual information or both on the particles, wherein the output measurement circuit (701) of the beam dumper (330) is inclined at an angle of 10° with respect to a reference surface that is perpendicular to an optical axis of the UV-LED beam (L), wherein the output measurement circuit (701) measures output intensity of the UV-LED beam (L), the UV-LED beam (L) reflected from the photodiode of the output measurement circuit (701) is not reflected to the optical axis, larger than the angle between the inner inclined surface of the beam dumper body (333) from the reference surface to an acute angle but is extinguished by progressing to the opening (334) formed in the beam dumper (330).
2. The portable real-time biological aerosol-detecting device according to claim 1, further comprising: a battery power supply (400) including a rechargeable battery (420) accommodated in a body (410) fixed to a lower end of the main body case (100).
3. The portable real-time biological aerosol-detecting device according to claim 1, further comprising: an audiovisual unit (230) that is installed on an outside surface of the main body case and provides audio or visual information on battery power consumption or device malfunctioning, or gives an audio or visual alarm signal when the presence of biological aerosol particles is detected.
4. The portable real-time biological aerosol-detecting device according to claim 1, further comprising: a handle (210) that is installed at an upper end of the outside surface of the main body case (100) to allow a user to conveniently hold and carry the portable real-time biological aerosoldetecting device, and that has an one open end to allow the particle collecting unit (200) to be introduced into the handle through the open end and thus accommodated in the handle (210).
5. The portable real-time biological aerosol-detecting device according to claim 1, wherein the beam-splitting optical system (340) includes a scattering detector (720) and a fluorescence detector (730) that respectively and simultaneously detect scattered light and fluorescent light according to a cut-off frequency of a dichroic mirror (342), the scattering detector (720) is equipped with a filter 343 that is arranged in front of the scattering detector, blocks fluorescent light, and allows scattered light to pass through, and the fluorescence detector (730) is equipped with a filter (346) that is arranged in front of the fluorescence detector, blocks scattered light, and allows guided fluorescent light to pass through.
6. The portable real-time biological aerosol-detecting device according to claim 6, wherein the scattering detector (720) and the fluorescence detector (730) each are a photomultipliers (PMT) that operate at low temperatures, or an avalanche photodiode (APD).
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| KR1020150155833A KR101623787B1 (en) | 2015-11-06 | 2015-11-06 | Portable real-time detecting device for biological aerosol |
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Also Published As
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| KR101623787B1 (en) | 2016-05-24 |
| GB2544196B (en) | 2020-04-22 |
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