Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
  • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
  • A61M16/0816—Joints or connectors
  • A61M16/0841—Joints or connectors for sampling
  • A61M16/085—Gas sampling
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B10/00—Instruments for taking body samples for diagnostic purposes; Other methods or instruments for diagnosis, e.g. for vaccination diagnosis, sex determination or ovulation-period determination; Throat striking implements
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B10/00—Instruments for taking body samples for diagnostic purposes; Other methods or instruments for diagnosis, e.g. for vaccination diagnosis, sex determination or ovulation-period determination; Throat striking implements
  • A61B10/0045—Devices for taking samples of body liquids
  • A61B10/0051—Devices for taking samples of body liquids for taking saliva or sputum samples
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/08—Measuring devices for evaluating the respiratory organs
  • A61B5/082—Evaluation by breath analysis, e.g. determination of the chemical composition of exhaled breath
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/08—Measuring devices for evaluating the respiratory organs
  • A61B5/097—Devices for facilitating collection of breath or for directing breath into or through measuring devices
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
  • A61M16/10—Preparation of respiratory gases or vapours
  • A61M16/105—Filters
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
  • A61M16/20—Valves specially adapted to medical respiratory devices
  • A61M16/201—Controlled valves
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
  • A61M16/20—Valves specially adapted to medical respiratory devices
  • A61M16/208—Non-controlled one-way valves, e.g. exhalation, check, pop-off non-rebreathing valves
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N1/00—Sampling; Preparing specimens for investigation
  • G01N1/02—Devices for withdrawing samples
  • G01N1/22—Devices for withdrawing samples in the gaseous state
  • G01N1/2202—Devices for withdrawing samples in the gaseous state involving separation of sample components during sampling
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B10/00—Instruments for taking body samples for diagnostic purposes; Other methods or instruments for diagnosis, e.g. for vaccination diagnosis, sex determination or ovulation-period determination; Throat striking implements
  • A61B2010/0083—Instruments for taking body samples for diagnostic purposes; Other methods or instruments for diagnosis, e.g. for vaccination diagnosis, sex determination or ovulation-period determination; Throat striking implements for taking gas samples
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B10/00—Instruments for taking body samples for diagnostic purposes; Other methods or instruments for diagnosis, e.g. for vaccination diagnosis, sex determination or ovulation-period determination; Throat striking implements
  • A61B2010/0083—Instruments for taking body samples for diagnostic purposes; Other methods or instruments for diagnosis, e.g. for vaccination diagnosis, sex determination or ovulation-period determination; Throat striking implements for taking gas samples
  • A61B2010/0087—Breath samples
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/02—General characteristics of the apparatus characterised by a particular materials
  • A61M2205/0216—Materials providing elastic properties, e.g. for facilitating deformation and avoid breaking
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/12—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit
  • A61M2205/123—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit with incorporated reservoirs
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/58—Means for facilitating use, e.g. by people with impaired vision
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/75—General characteristics of the apparatus with filters
  • A61M2205/7545—General characteristics of the apparatus with filters for solid matter, e.g. microaggregates
• • C—CHEMISTRY; METALLURGY
  • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
  • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
  • C12N1/00—Microorganisms; Compositions thereof; Processes of propagating, maintaining or preserving microorganisms or compositions thereof; Processes of preparing or isolating a composition containing a microorganism; Culture media therefor
  • C12N1/06—Lysis of microorganisms
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N1/00—Sampling; Preparing specimens for investigation
  • G01N1/02—Devices for withdrawing samples
  • G01N1/22—Devices for withdrawing samples in the gaseous state
  • G01N2001/2244—Exhaled gas, e.g. alcohol detecting
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
  • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
  • G01N33/483—Physical analysis of biological material
  • G01N33/497—Physical analysis of biological material of gaseous biological material, e.g. breath

Definitions

• the current invention is directed to a system for collecting and analyzing bacteria or biological particles; and more particularly to a system comprising an aerosol collection system for airborne bacterial or biological particle detection that can be used to prepare a sample for diagnosis or directly diagnose a sample for bacterial infection from the environment or from a patient, such as, for example, tuberculosis.
• TB Active Tuberculosis
• M. tuberculosis is classified as a NIAID Category C Priority Pathogen and is transmitted primarily through airborne droplets (as few as 2 droplets can cause TB infection).
• Multiple-drug resistant strains further complicate TB diagnosis and treatment, boosting its threat as a bioterrorism agent. When diagnosed properly TB can be treated.
• sputum expectorate is the most common sampling method used for TB diagnosis.
• BAL bronchoalveolar lavage
• Pneumonia is the leading cause of death among infectious diseases in the United States where ⁇ 1 .1 M people are hospitalized and ⁇ 50, 000 die each year. Pneumonia is an infection of the lower respiratory tract (LRT) and is typically caused by viruses and/or bacteria.
• LRT lower respiratory tract
• a major challenge in diagnosing pneumonia is obtaining a quality sample namely because etiologic agents of pneumonia often colonize the upper respiratory tract (URT) of healthy subjects without causing LRT infection. If a diagnostic sample contains URT contaminants, the sample is discarded (low diagnostic yield) or a false etiologic agent may be identified (low specificity). Sputum or bronchoalveolar lavage (BAL) are the most common samples used to identify the etiologic agent of pneumonia.
• HAP hospital-acquired pneumonia
• Pandemic influenza arises when a new strain, for which little prior immunity exists, begins circulating in the human population. Most recently, the 2009 A(H1 N1 ) swine flu pandemic caused an additional 280,000 deaths. Alarmingly, certain influenza strains, such as the A(H1 N1 ) swine flu and the A(H5N1 ) avian flu, have an increased propensity to infect the lower respiratory tract and cause severe illness. Influenza diagnosis is typically performed on samples collected from the throat and nasal cavities of the upper respiratory tract, using nasopharyngeal (NP) swabs. However, only invasive procedures can collect samples for the proper diagnosis of lower respiratory tract influenza.
• NP nasopharyngeal
• influenza surveillance data collected exclusively from upper respiratory tract samples may miss emerging strains that preferentially target the lower respiratory tract.
• Current methods of obtaining samples from the lower respiratory tract, such as transtracheal aspiration, bronchoalveolar lavage, and lung biopsy are highly invasive.
• the disclosure is directed to systems for collecting and analyzing bacteria or biological particles, and to prepare a sample for diagnosis or directly diagnose a sample for bacterial infection from the environment or from a patient, such as, for example, tuberculosis.
• the invention is directed to a biological sample collector system including:
• a pre-collection assembly configured to engage with a patient such that the entirety of the outflow of breath from the patient including any biological particulates contained therein is captured within the collector system;
• a sample reservoir defining a volume having therein a sample medium for entraining the target biological particulates in the sample medium to form a sample analyte suitable for diagnostic analysis
• a collector in fluid communication between the pre-collection assembly and the sample reservoir, and having at its terminating end a fluid focusing nozzle, the collector being configured to select said biological particulates of greater than a target size from said outflow of breath and direct said target biological particulates into said sample reservoir such that efficient transfer of the target biological particulates into the sample medium is obtained;
• the angle formed between the entry of the fluid focusing nozzle and the collector upstream of said nozzle is configured such that recirculation zones are prevented from forming in the nozzle entrance, wherein the length of the nozzle is configured to prevent the biological particulates from reaching their terminal velocity, wherein the diameter of the nozzle is configured to reduce particle bounce and increase collection at a specified flow rate, and wherein the ratio of the length of the nozzle to the diameter of the nozzle is configured such that the biological particulates do not intercept the walls of the nozzle.
• the sample reservoir is incorporated into a cartridge module in fluid connection with the collector, the cartridge module being removable from said collector system and being configured to cooperatively engage with an input of a diagnostic analyzer.
• the cartridge module containing the sample reservoir comprises a self-sealing mechanism configured to isolate the sample medium from the external atmosphere.
• the portion of the cartridge module containing the sample reservoir includes a mechanism for ejecting the sample medium into the input of the diagnostic analyzer.
• the sample medium contained within the sample reservoir takes a form selected from the group consisting of a tablet, a pelletized salt, a liquid, a film, and a gel.
• the entrance to the sample reservoir is disposed opposite the fluid focusing nozzle.
• an exposed surface of the sample medium contained within the sample reservoir is dimensioned to be on the order of the diameter of the nozzle.
• the sample medium is a liquid and the sample reservoir further comprises an airspace between the end of the nozzle and the exposed surface of sample medium, and wherein the cross- section of the airspace, the cross-section of the nozzle and the distance between the end of the nozzle and the exposed surface of the sample medium are configured such that the velocity of the outflow at the exposed surface of the sample medium is less than 20 m/s.
• the ratio of the distance from the end of the nozzle and the exposed surface of the sample medium and the nozzle diameter is greater or equal to 1 .2 and less than or equal to 1 .6.
• the angle formed between the entry of the fluid focusing nozzle and the collector upstream of said nozzle is less than 30° such that recirculation zones are prevented from forming in the nozzle entrance.
• the ratio of the length of the nozzle to the diameter of the nozzle is less than 2.25.
• the nozzle diameter is configured such that the velocity of the biological particulates at the surface of the sample medium multiplied by the particle diameter is less than 50 to control biological particulate bounce against the surface of the sample medium such that the collection efficiency of the particle size of interest is greater than 0.9.
• the collector has a specified flow capacity
• the pre-collector assembly further comprises a temporary storage volume configured to capture any portion of the outflow of breath from the patient that exceeds the flow capacity of the collector.
• the temporary storage includes a one-way valve mechanism whereby the breath captured in the temporary storage volume is prevented from being inhaled by the patient and releases the captured breath into the collector during an inhalation by the patient.
• the one-way valve is triggered by one of either an automated mechanism or manually by the patient.
• the pre-collector assembly further comprises a second one-way valve that allows an inhalation of breath by the patient through the pre-collector assembly.
• the temporary storage volume is formed of an elastic material, such that the temporary storage volume stores at least a portion of both the volume of the outflow of breath and the work of the outflow of breath as potential energy, and wherein the potential energy may be converted to a kinetic flow by releasing said stored portion of the outflow of breath into the collection system.
• the pre-collector assembly further comprises a filter mechanism for filtering out biological particulates of greater than a target size from said target biological particulates.
• the filter mechanism comprises a one-way valve configured to bend during exhalation by a patient such that particulates greater than the target size impact the valve and are prevented from entering the collector.
• the collector further comprises an aerodynamic impactor having first and second ends and defining a fluid path therein, and wherein the aerodynamic impactor applies an inertial deceleration force to the gaseous sample, and wherein the magnitude of the inertial force can be varied such that at a low inertial force any biological particulates within the sample are passed through the impactor intact and that at an inertial force above a threshold any biological particulates within the sample are lysed to release the internal components thereof.
• the internal components of the target biological particulates contain DNA.
• system further includes a positive control configured to provide an indication that a sufficient volume of the outbreath of the patient has been collected.
• positive control is selected from the group consisting of an indicator for a signature biological material and a physical measurement of the outflow of breath from the patient.
• the pre-collector assembly further comprises a humidity control system configured to prevent particle growth.
• FIG. 1 provides a schematic of an embodiment of a sample collection and analysis system in accordance with embodiments of the invention.
• FIGs. 2a to 2c provide schematics of embodiments of a cartridge module and mechanism of sample transfer in accordance with embodiments of the invention.
• FIGs. 3a to 3c provide schematics of sample reservoirs shown in a cross section of a collector in accordance with embodiments of the invention.
• FIG. 4 provides a schematic of a sample reservoir in a polycarbonate surface fixed at its edges on the flat surface using a tapered ring in accordance with embodiments of the invention.
• FIG. 5 provides a data graph obtained from computational fluid dynamics (CFD) simulations showing the relationship that d2 and x2 have in relationship to collection efficiency and velocity at the sample reservoir surface in accordance with embodiments of the invention.
• CFD computational fluid dynamics
• FIG. 6 provides a schematic of a cross section of a collector and CFD data driven vectors of velocities at the entrance of the collector nozzle in accordance with embodiments of the invention.
• FIG. 7 provides a data graph obtained from CFD simulations showing the relationship between nozzle angle and wall losses in accordance with embodiments of the invention.
• FIGs. 8a and 8b provide schematics of the cross section of collector embodiments with different nozzle throat lengths overlaid on the schematic is CFD data driven particle tracks in accordance with embodiments of the invention.
• FIGs. 9a and 9b provide data graphs showing the relationship of nozzle diameter (d1 ) to collection efficiency and impaction velocity in accordance with embodiments of the invention.
• FIGs. 10a to 10c provide schematics of pre-collector assemblies in accordance with embodiments of the invention.
• FIG. 1 1 a provides a schematic of a pre-collector assembly cross-section whereby a one-way valve acts as a low-pass filter, overlaid on the schematic is CFD data driven 10 ⁇ particle tracks as well as a contour of the air velocity in accordance with embodiments of the invention.
• FIG. 1 1 b provides a data graph showing particle penetration as a function of particle diameter for two different valve bend angles in accordance with embodiments of the invention.
• FIG. 12a provides a schematic of a collector embodiment showing cell breakup and collection and indicating the measurement process for determining the ratio of DNA to cells in the collection reservoir in accordance with embodiments of the invention.
• FIG. 12b provides a data graph showing the increase in extra-cellular DNA due to cell break-up at higher P1/P0 in accordance with embodiments of the invention.
• FIG. 13 provides a schematic of a sample collection system in accordance with embodiments of the invention.
• FIG. 14 provides a data graph showing the detection improvement using embodiments of the invention shown in FIG. 13 compared to a prior-art Anderson collector.
• the sample collection and analysis system concentrates particles emanating from a patient's cough, sneeze, or breathe in a sample for the diagnosis of a respiratory tract infection or other ailment of the patient.
• the sample collection and analysis system (1 ) has a pre-collection assembly (that is patient interface 2), a collector (3) in fluid communication between the pre-collection assembly and a sample reservoir (4) that function in combination to: efficiently capture the volume of air expelled from the subject, direct the expelled air towards a sample reservoir, and separate the desired particle sizes from the expelled air into the sample reservoir.
• expelled particles collected in the sample reservoir are the source of analyte that produces a signal in the transducer of a diagnostic device sensor.
• this analyte can be any one or more of liquid droplets containing organic, inorganic or biological molecules that provide a signature of the illness; liquid droplets that contain fragments or intact live or dead bacterial cells, viruses, or cells originating from the subject; and dry fragments or intact live or dead bacterial cells, viruses, or cells originating from the subject.
• these particles along with the material that makes up the collection reservoir are referred to as the sample (5), which may be transferred to a diagnostic device (6) to produce a diagnostic result of the ailment in question.
• the sample (5) which may be transferred to a diagnostic device (6) to produce a diagnostic result of the ailment in question.
• the sample collection and analysis system is configured to be used as a fully integrated patient-to-diagnosis device. Such operation requires a seamless transfer of sample from the sample collection device to an appropriate diagnostic device. To accomplish this a sample is collected in a sample reservoir. As will be discussed in greater detail, below, the sample reservoir medium can take many forms. Regardless of the sample medium, in embodiments the sample can be transferred to a diagnostic device either continuously or in batch. For continuous transfer a microfluidic system would be integrated whereby the collected material is directly transferred to the diagnostic device, which can either detect the material in batch or real-time, as described previously in U.S Pat. Pub. No. 2013/0217029, the disclosure of which is incorporated herein by reference. However, in batch transfer embodiments a cartridge module (7) may be incorporated into the sample collection system. In many embodiments, the module includes a mechanism that facilitates the transfer of sample. In such embodiments the cartridge module may include one or more of the following design elements:
• a cartridge module may engage with and dispense a sample into the diagnostic device such as a Cepheid XpertTM or a BioFire FilmArrayTM; and
• the mechanism of sample transfer is integrated into the cartridge module, such mechanism being mechanical, electrical, or any mechanism or combination.
• a removal mechanism may include one or more of the following design elements:
• a removal means that includes one or both of a twist-off, snap-off, or other mechanism.
• a self-sealing cartridge module that seals the sample reservoir once removed from the collection system, thus preventing the sample, which might contain biohazards, from being exposed to the external environment or exposing personnel to such biohazards, and also preventing contamination of the sample by external environmental elements.
• removal of the cartridge module (10) from the collector (12) forces a flap through a spring (not shown) to shut-off the orifice (14) leading to the analyte-containing liquid (16) contained within the sample reservoir (18).
• the cartridge module also acts as a storage vehicle.
• the cartridge module preserves the sample reservoir before collection and before transferring (i.e. after collection) the sample to the diagnostic device. Therefore, the cartridge module is configured to withstand a wide temperature range to maintain the integrity of the sample reservoir and the sample it contains (low temperatures for post-collection storage and high temperatures for on shelf storage preelection).
• the dispensing mechanism either allows integration of the cartridge module with a specific diagnostic device, transfer of the sample into a standard use tube or vial after which a standard transfer pipette is used, or any other receptacle.
• a mechanism is built in to the cartridge module to actively force the sample in the sample reservoir out whereby there is a seal created to isolate the transfer from the outside environment.
• the sample reservoir medium is a tablet (as described below)
• a device such as a clicker
• the cartridge module mechanically ejects the tablet into the diagnostic device (such as a tube), which could contain water or other buffers where the tablet containing the collected analyte may be dissolved and ready for detection.
• the cartridge module can contain a mechanism (not shown), such as a plunger of the type used in syringes, whereby a piston drives the analyte-containing liquid to the receptacle.
• the sample collection system (12) comes prepackaged with all parts including the cartridge module (10), as shown in FIG. 2a. After a sample is collected from the patient, the cartridge module is disconnected, as shown in FIG. 2b.
• the cartridge module (10) includes a sample reservoir (16).
• the particles generated by the patient flow through a nozzle.
• the mechanism of creating flow through collector will be described in greater detail below.
• the sample reservoir is placed perpendicular to the flow exiting the nozzle, which causes the flow to bend. The particles cannot follow the change in direction and are directed towards the sample reservoir where they are collected.
• the sample reservoir is a cavity facing the nozzle (20) that focuses the stream of the incoming outflow of breath, and that contains a liquid buffer (16) as the sample reservoir medium.
• the analyte is collected in the medium, which becomes the analysis sample.
• the cartridge module then integrates with a diagnostic device (22) receiving port (24) creating a seal, as shown in FIG. 2c.
• the cartridge module then can be operated to dispense the sample through a mechanism, in one embodiment this mechanism can be a plunger (not shown) as well, that also forces the orifice to open and eject the analyte.
• the sample reservoir is defined as the medium that accepts the separated particles from the patient's cough, sneeze or breath and concentrates them. Therefore, in embodiments the material contained within the reservoir is small enough to allow for the sample to be less than 2 ml_ prior to being fed into the diagnostic device.
• the dimensions of the sample reservoir medium (26, 28, 30 in FIGs. 3a to 3c) are on the order of the nozzle diameter (d1 ).
• the sample reservoir itself (32, 34, 36) is located opposite the nozzle (38, 40, 42), and can be of varying geometries some of which are shown in FIGs. 3a to 3c. Both of the geometries shown in FIGs. 3a and 3b have similar collection characteristics in that the air exiting the nozzle encounters a flat plate.
• the sample reservoir medium (26, 28, 30) in which the particles are collected can vary - some being suited for only specific geometries and not others.
• the common factor in all these sample reservoir media is that they have to be compatible with the downstream diagnostic detection methodology. For instance, if the method used is polymerase chain reaction (PCR) amplification to detect the analyte, then media that do not inhibit the PCR have to be used.
• the geometry in FIG. 3a is suited for use with a flat solid material or films (26).
• One embodiment of this design is the use of a polycarbonate film (44), which is fixed at its edges on a flat surface (46) using a tapered ring (48) (see FIG. 4).
• the analyte lies on the surface of the flat solid material and can be transferred to liquid by placing the film in an extraction liquid. Extraction of intact cells can be performed using sonication for 1 min or DNA can be extracted using DNA extraction kits.
• the material of choice in these cases has to be a material that dissolves.
• the salts of choice are pelletized and inserted in the sample reservoir (34). The analyte is collected on the surface and after the collection the analyte is extracted into liquid by dissolution.
• a polyethylene glycol (PEG) gel or viscous liquid is placed in the sample reservoir. PEG molecules of different lengths are water-soluble at different water content levels. This property can then be used to control the dissolution of the PEG gel that contains the analyte.
• a cavity (50) is disposed in relation to the sample reservoir allowing the airflow to decelerate prior to contacting the collection surface (52) (liquid, film, or solid) of the sample reservoir. This prevents the airflow from carrying droplets from the liquid surface and eventually depleting the sample (30).
• the opening to the cavity (50) has a diameter d2, and the liquid is placed at a distance x2 from the opening.
• FIG. 5 shows velocity and collection efficiency results of a CFD simulation at different nozzle parameters, namely variation to d2/d1 and x2/d1 . As shown, the velocity at the surface decreases with decreasing d2/d1 and with increasing x2/d1 , and the collection efficiency has the same effect.
• the curve shown in FIG. 5 may be used as a nozzle and collector design guide.
• x2/d1 has to be equal to 10 (see dashed line in FIG. 5).
• the collection efficiency is -60%.
• the curves shown in FIG. 5 may be used to configure a cavity that preserves a specific amount of liquid, such as a buffer.
• the surface tension of the liquid surface may be controlled. In particular, as d3 decreases the surface tension forces increase and make it more difficult for the liquid to escape.
• the geometry of the collector may also be engineered to control particle wall losses, particle bounce, particle collection, manufacturability and ease of use. There are multiple parameters in the geometry that are important to the design of the collector. Exemplary embodiments providing the optimization of some of these parameters are provided for the collector embodiments provided in FIGs. 3a and 3b, and may also be applied universally including to the embodiment shown in FIG. 3c.
• the angle of the nozzle is one of the collector geometry parameters that can impact the efficiency of particle collection.
• re-circulation zones are created in the nozzle throat entrance (56) area. This zone results in particle losses at the entrance of the nozzle (56) and prevents these particles from reaching the collection reservoir medium. At lower angles these zones disappear.
• Manufacturing errors, ledges in the nozzle throat entrance create similar disturbances in the entrance area of the nozzle throat and amplify the effect of larger angles resulting in a rise in particle loss on walls.
• FIG. 7 shows the particle losses in relationship to the nozzle angles and can be used in configuring the collector nozzle angle.
• FIG. 7 also shows how ledges affect losses, which can also be used as a design principle in configuring the collector.
• the nozzle throat (60) length (T) determines the velocity of the air and particle at the nozzle exit (62).
• a sufficiently long nozzle throat will allow the air to reach a fully developed flow before exiting the nozzle.
• the nozzle should be short enough to reduce the particle velocity at the nozzle exit (62), and thus particle losses.
• the maximum terminal velocity a particle can reach is that of the gas velocity at the nozzle exit (62).
• the particle velocity at the nozzle exit (62) is another parameter as it determines the final velocity of the particle at the collection surface (or impaction velocity). In particular, a low velocity will tend to eliminate bounce effects.
• the optimal length then allows for fully-developed air flow and a minimal particle velocity and losses on walls.
• FIGs. 8a and 8b illustrate the concept for 10 ⁇ particles by showing the CFD calculated particle tracks (64). These big particles have high relaxation times ⁇ and are unable to adapt to fast flow changes caused by changing flow directions in the nozzle throat entrance (68).
• T/d1 2.25; where T is the nozzle throat length
• Determining the flow rate of the collector may also be used in configuring the overall design of the sample collection system. For example, in embodiments it affects the design of the pre-collector assembly (or patient interface as discussed below). Assuming an appropriate flow rate is determined using the criteria discussed below then the diameter of the nozzle can be set according to certain rules. [0057]
• the nozzle diameter (d1 ) has the largest effect on impaction velocity. A low impaction velocity (vi-dp ⁇ 5), where vi is particle velocity and dp is the particle diameter, is required to eliminate particle bounce: the larger the diameter the lower the impaction velocities (at a constant volumetric flow rate).
• vi.dp can be within at most an order of magnitude of 5 to control particle bounce. Particle bounce results in loss of collection efficiency. If the velocities are too low, it can result in a loss of collection efficiency since the particles can follow the air stream and exit the collector without being driven into the collection reservoir medium. Therefore, particle impaction velocity and collection efficiency may be balanced to obtain the nozzle diameter. For example, FIG. 9 shows the region of operating diameters for flow rates of 5 and 6.5 liters per minute.
• the nozzle to plate distance, x1/d1 has no influence on particle collection or impaction velocity at the 5 liters per minute operating condition, when the ratio is between 1 .2 ⁇ x1/d1 ⁇ 1 .6. At higher ratios small particles can get entrained in the air flow which results in decreasing collection efficiency.
• the sample collection system is configured to the measured cough flowrates.
• the sample collection system is configured to increase the flowrate through the collector.
• a temporary storage area is provided where the excess cough volume may reside before being drawn by the sample collection system.
• adaptation of the sample collection system to cough flowrates is accomplished by creating a temporary storage that allows excess volume that cannot be directed to the sample reservoir of the sample collection system to be stored and drawn at a rate equal to the flowrate of the collector.
• the sample collection system can be composed of two major parts: the pre- collector assembly (or patient interface), and the collector, as shown in FIG. 1 and FIG. 10.
• the pre-collector assembly (PCA) is configured to create a temporary storage whereby the excess cough volume resides before being drawn by the collector.
• the PCA (70) has one or more of the following specifications:
• the inlet includes an inlet (72) that interfaces to an external opening of the respiratory tract.
• the inlet interface (72) creates a seal and allows a cough, sneeze, breath or any other aerosol output of the respiratory tract to be directed towards the sample collection system.
• the inlet can be a mouthpiece.
• the inlet can be a mask.
• the inlet can be a nosepiece that draws exhaled breath through the nostrils.
• the PCA mechanism consists of two one-way valves (80, 82).
• the oneway valves (80, 82) can consist of silicon rubber attached to a surface that restricts its bending to one direction.
• the one-way valves (80, 82) can be electronically controlled.
• the PCA upon exhalation, directs the cough volume through a one-way valve (82) to an expandable reservoir placed at an angle to the direction of main flow from patient (90).
• this reservoir can be an inflatable plastic bag that provides no resistance as it is being inflated.
• this reservoir is made of an elastic material similar in nature to a balloon, such that an elastic resistance is provided.
• the same one-way valve (82) prevents the captured exhaled volume from exiting the reservoir and directs it towards the collector (76).
• the other one-way valve (80) permits the patient to inhale of ambient air through the PCA (70).
• the mechanism is similar to that described above, with the exception that only a single one-way valve (82) is used. This prevents the patient from breathing in while using the PCA. The patient is instead instructed to breath in by removing the PCA.
• the mechanism is similar to that described above, whereas the reservoir (78) is placed inline to the direction of main flow from the patient.
• the one-way valve operates as a gate that opens to allow air in one direction in reaction to a force.
• the force that opens the valve is the air exiting the patient.
• the force that opens a valve is supplied through a spring controlled by the patient using a button placed on the PCA.
• the volume of the reservoir (78) varies based on two parameters: the number of coughs it has to store before the patient can fill it up again and the flow rate of the collector (76)
• Lindsley et al. use a metal chamber equipped with an expanding piston that accommodates the extra air from the patient.
• a metal chamber equipped with an expanding piston that accommodates the extra air from the patient.
• Lindsley's system directs all the air towards the collection device.
• Lindley uses a manual cork after coughing to prevent the air from escaping the metal piston chamber.
• the pre-collector assembly (or patient interface) has another function: a screening device for particles that reach the collector.
• the collector is designed to collect particles of size (dp) in the collection reservoir where dp,c ⁇ dp.
• the goal of the sample collection system is to collect particles of size (dp) where dp,c ⁇ dp ⁇ dp,1 .
• the collector in and of itself cannot achieve this.
• the pre-collector assembly (or patient interface) can be designed to exclude particles of dp > dp,1 from reaching the collection reservoir of the collector. Therefore, in embodiments the sample collection system can be designed to collect particles of size (dp), where dp,c ⁇ dp ⁇ dp,1 .
• dp particles with diameters (dp) ⁇ 5 ⁇ are from the lower respiratory tract (LRT), while those with dp > 10 ⁇ are from the upper respiratory tract (URT).
• LRT lower respiratory tract
• UTR upper respiratory tract
• the PCA includes a low pass filter mechanism, as described above. In this case, the PCA preferentially excludes particles with dp > 5 ⁇ . Alternatively, only very large particle debris such as sputum debris can be blocked in the pre-collector assembly.
• a low-pass filter mechanism (83) comprising a one-way valve (84) is placed in the path of the flow originating at the patient (86) and ending at the collector inlet (88).
• the one-way valve is configured to bend (88) during exhalation.
• the bend angle varies depending on the flow produced by the patient as well as intrinsic properties of the valve, such as the type of material and geometric dimensions.
• particles (90) are captured on the valve surface.
• the angle is chosen to be 55 degrees to reduce the aerodynamic forces acting on it to ⁇ 0.7 N, and the valve is shown to allow 30% of the particles with dp > 20 ⁇ to go through the PCA and reach the collector (Penetration - P, see FIG. 1 1 B).
• P 50% make it past the valve to the collector - the particle tracks (90) show a subset of the 10,000 particles used to calculate P in FIG. 1 1 B.
• the geometry can be refined to decrease the penetration, P.
• One such modification is to change the valve material to allow for a smaller bend angle. A 10 degree drop (from 55 degrees to 45 degrees) in the bend angle decreases the penetration of particles > 10 ⁇ by ⁇ 10% (see FIG.
• FIG. 12A it has been shown that a fraction of intact cells (92) pass through the collector nozzle (94) at conditions of shock break up. Collection of the cellular components (96), specifically genomic DNA, following break-up has never been shown in conventional devices. However, once the cell is broken-up, the cellular components can either be directed toward the collection reservoir (98) or follow the path of air (100).
• the total mass of DNA is compared to the total number of cells in the collection buffer.
• both measurements of the DNA mass (104) and the number of cells (106) are conducted on the same sample following the collection experiment.
• the mass of DNA per cell fDNA in fg/cell
• E. coli contains 5 fg/cell of genomic DNA per cell. In the limit where no cells are lysed, genomic DNA is fully contained in the cells and therefore the measured fDNA should be equal to 5 fg/cell. As the value of fDNA increases, more genomic DNA is extra-cellular, indicating collection of the cellular components of the broken up cells.
• FIG. 12B shows calculated fDNA data in a box-plot for four different experiments, each repeated n times.
• ANOVA test p-values are calculated to statistically analyze the data.
• the fDNA of a cell suspension was performed.
• An average of 4.5 fg/cell is calculated for the control experiments, which is statistically equivalent to the 5 fg/cell expected for E coli.
• This data establishes that: 1 ) the measurement method is valid and produces results that mimic the known mass of genomic DNA in E. coli, and 2) the starting culture does not contain extra-cellular genomic DNA.
• the letters A, B and C in FIG. 12B indicate which distributions are statistically distinguishable: if two distributions have the same letter then they are considered statistically equal. As shown, a statistically significant amount of cellular components is collected at lower P1/P0 in relation to higher P1/P0, indicating that the shock breaks up the cells and that the cellular components are concentrated in the collection reservoir.
• Some embodiments of the sample collection system include establishing a flow through the collector.
• the positive pressure produced by the patient drives the flow through the collector.
• the pre-collector assembly reservoir provides the positive pressure to drive the flow through the collector.
• the reservoir is made of an elastic material, akin to a balloon, that can be inflated by the patient's exhaled matter. Exhaled matter delivered to the elastic reservoir is impeded from backflow by a one-way valve. The inflation of the elastic reservoir stores the work of the patient's exhalation as potential energy. The elastic reservoir then drives the flow through the collector by converting the potential energy to kinetic energy of flow.
• a vacuum pump placed downstream of the collector drives the flow through the collector.
• the pump can be a rechargeable and portable one.
• an industrial vacuum line drives the flow.
• a positive control is included to ensure that exhaled matter was collected.
• the positive control can be a test for a specific signature that could be a specific organic, inorganic or biological molecule.
• the test can also be for a specific signature of a fragment or intact live or dead bacterial cell, virus, or cell originating from the subject. The requirement is that the specific signature is present in all humans.
• One embodiment of such a specific signature is the bacterium S. Mitis and any components thereof that is present in the oral cavity of all patients.
• Another embodiment of the specific signature is the molecule Glutathione that is present in alveolar lining fluid.
• a real-time readout such as a change of color that indicates that enough exhaled matter was collected.
• a readout of the specific signature is indicated when the actual diagnostic device tests for the analyte.
• the positive control can also be a physical measurement. In one embodiment, the positive control can be a measurement of how much volume was expelled from the patient.
• Some particles emitted from the patient are in the form of liquid droplets that contain the analyte.
• the size of these droplets depends on the humidity in the sample collection system.
• placing hydroscopic materials in the PCA lowers the humidity.
• the entire PCA can be made of hygroscopic plastics such as Nylon.
• hygroscopic materials such as silica gel can be placed in various parts of the PCA.
• One such area of the PCA where such materials can be placed is the reservoir described in more detail in previous sections.
• clean dry air from environment is allowed to mix with the patient's output.
• Example 1 Example Embodiment of the Sample Collection System
• FIG. 13 shows one embodiment of a sample collection system that combines multiple aspects.
• the sample collection system (109) consists of a pre-collector assembly (108) and a collector (1 10).
• the pre-collector assembly includes a mechanism of managing flow from the patient depicted in the embodiment shown in FIG. 10c.
• the pre-Collector assembly includes a mechanism of excluding droplets >10 ⁇ with an efficiency of >50% as depicted in FIG. 1 1 .
• the pre-collector assembly consists of a T-junction (1 12) with three ends (1 14, 1 16, 1 18) - one end connecting to the mouthpiece (1 14), the second to a bag (1 16), and the third to the collector (1 18), although the bag and mouthpiece are not shown in FIG. 13.
• the embodied pre-collector assembly includes a one-way valve (120), which is made of a silicone flap (122) that rests on a plastic ring (123), which is inserted into the T-junction. The flap can only open in one direction bending its edges towards the collector (1 10) when the patient flow encounters the valve.
• the collector (1 10) used in this embodiment does not include a cartridge module.
• the sample reservoir (124) is the one described in the embodiment of FIGs.
• the exemplary sample collection system described above can be contrasted with the Andersen impactor, used in Fennelly's collection system, which was developed in 1958 for environmental sampling and, while adept at the collection of bioaerosol, was not designed for diagnostic detection of clinical samples.
• Andersen impactor used in Fennelly's collection system, which was developed in 1958 for environmental sampling and, while adept at the collection of bioaerosol, was not designed for diagnostic detection of clinical samples.
• deposition of bacteria on selective media such as 7H1 1 agar
• structurally damages cells and can render up to 99% non-viable See, e.g., Stewart et al., Applied and Environmental Microbiology, 61 (4):1232-1239, 1995, , the disclosure of which is incorporated herein by reference.
• efficient extraction of PCR-ready DNA is impractical due to the large area of the agar plate.
• the setup is designed for research use and is impractical for clinical use; the impactor is placed in a large ( ⁇ 20" by 8") metal chamber that hinders transport and sterilization.
• Exemplary embodiments of the sample collection system and the Andersen impactor were tested in a lab by sampling aerosolized E. coli from a common reservoir.
• FIG. 14 shows that the limit of detection of the exemplary sample collection system with 35 cycle PCR is at least 10x lower (better limit of detection) than that of the Andersen impactor with culture.

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• 2014
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