WO2025002552A1

WO2025002552A1 - Cartridge for a gas analyzer device or gas analyzer sensor

Info

Publication number: WO2025002552A1
Application number: PCT/EP2023/067684
Authority: WO
Inventors: Sergei DAVYDOV
Original assignee: Halitus Gmbh
Priority date: 2023-06-28
Filing date: 2023-06-28
Publication date: 2025-01-02

Abstract

Provided is a cartridge for a gas analyzer device or sensor, the cartridge comprising: a plurality of optical cells, each optical cell of the plurality of optical cells being configured to analyze a different chemical compound and comprising: a light-reflective inner surface, and a laser and receiver pair arranged in the optical cell in such a way that light is reflected a plurality of times on the light-reflective inner surface, and a mechanical connector configured so that the cartridge is insertable and removable from the gas analyzer device or sensor.

Description

Cartridge for a gas analyzer device or gas analyzer sensor

Technical Field

The present disclosure generally relates to dynamic gas medium monitoring systems based on the principles of laser absorption spectroscopy. In particular, the present disclosure relates to a cartridge for a gas analyzer device or a gas analyzer sensor.

Background

US 10451540 B2 "Multi-pass gas cell with mirrors in openings of cylindrical wall for IR and UV monitoring" sets out principles for multi-pass cylindrical optical cells employing multiple reflections. This approach makes it possible to significantly increase the beam path from the emitter to the receiver through the measured gas medium.

RU 2625258 C2 "Method and device for dynamic gas analysis integrated into a breath mask exhalation line" and RU 2773603 Cl "Method of deturbulation and subsequent analysis of dynamic gas mediums and device for its implementation integrated into a breath mask" describe dynamic gas medium analysis devices and methods. Such methods allow getting continuous data directly from exhaled air without air sampling and side-stream cuvettes with a low detection limit (high measuring sensitivity).

Further, RU 2502065 "Method for analysing the composition of gas mixtures and gas analyzer for its implementation" proposes to use sensors of two types for the analysis of the gaseous environment: an electrochemical sensor and a photoionization sensor, which have the property to accumulate errors under long-term use due to their design features. To obtain reliable results, RU 2502065 proposes to conduct measurements twice: with the help of chemical filters at the sensor inputs that separate an individual component of the gas mixture determined by the given sensor from the gas mixture entering each sensor, and without using the filter, comparing the results obtained and based on this providing a conclusion about the concentration of the determining component in the mixture under study. For this purpose, RU 2502065 proposes to use different actuators and thrusters. Further, GB 2576137 A "Multi -test respiratory diagnostic device" describes a respiratory testing device performing multiple diagnostic tests comprising a housing and a plurality of sensors. The device has at least two configurations: in the first configuration a first respiratory test is performed using a first set of sensors, and in the second configuration a second respiratory test is performed using a second set of sensors. The device may be modular having a primary component and secondary components to create different configurations. The secondary components may adapt the device to make it suitable for the primary component to perform different tests. Spirometry may be performed when a spirometry module is attached to optimise airflow, biomarkers measured with a nitric oxide sensor module attached, impulse oscillometry testing occurs when an oscillometry module with occluder is attached, and capnography performed when a carbon dioxide sensing component is attached. Different mouthpieces may be used in the different arrangements.

Further, US 5886348 "A Non-dispersive infrared gas analyzer with interfering gas correction" introduces a classic scheme for analysing air samples using a nondispersive infrared (NDIR) approach at parts per million (ppm) detectivity level.

Summary

Technical Problem

The teaching of US 10451540 B2 is restricted to using air samples taken by a sidestream gas cuvette. Such a system cannot be integrated directly into the main air line, that is an air way or an air path following a direction of air that is inhaled or exhaled by a user or patient, in other words, a direction toward or exiting from a mouth of the user or patient. The teaching of US 10451540 B2 is also not readily usable for medical use cases, such as when using a corresponding device, for example, in mass medical screenings of the population using exhaled air, where such devices should be quickly and safely available for a next patient.

The teachings of RU 2625258 C2 and RU 2773603 Cl can lead to reduced detection accuracy dues to a condensation of exhaled gas or air on internal surfaces of a gas analysis device. That is, a temperature difference between the device and the airflow may lead to water condensation on the internal surfaces. Water droplets can absorb and scatter the laser beam and significantly distort the measurement results. Further, pressure drops (microphone effect) in an air line may have a negative impact on the sensitive optoelectronic components which are not protected. Also, a direct contact of exhaled air with optical elements may reduce the lifetime of the device. There is also a need to change optical cells at once and fast adapt the measurement device for another task, for example, for a measurement of another substance, chemical molecule, biomarker, or the like.

The teaching of RU 2502065, however, leads to low sampling and acquisition rates, a low detection limit, low selectivity, and error accumulation in a long-term continuous use due to electrochemical sensors, and increased complexity due to the filters' movement mechanisms.

The teaching of GB 2576137 also does not allow for a continuous exhaled air or respiratory gas mixture analysis in a main air pathway during a breathing cycle. In addition, the number of simultaneously detectable and analysable substances or chemical components is limited. The teaching of GB 2576137 also requires using absorption materials to avoid a high humidity inside the device, which requires many consumables and does not allow to use the device longer than 4 to 5 minutes, for example, until a saturation of the absorption material occurs.

Finally, the teaching of US 5886348 also does not provide any means for a continuous exhaled air analysis and pulmonary function tests. This fact significantly reduces the quality and quantity of data used in automated lung assessment. Air exhaled by a human patient can contain more than 1000 chemical compounds (including volatile organic compounds (VOCs)), most of which are at a parts per billion (ppb) level and where at least some thereof can be recognised as biomarkers for diagnostic propose. The teaching in US 5886348 cannot detect chemical compounds at a 10 ppb level and lower without additional instruments and dryers due to the main absorption line of H2O and CO2 that can significantly overlap the absorption of molecules under study.

Solution

The subject-matter of the independent claim solves the above-identified technical problems. The dependent claims describe further preferred em bodiments.

In particular, a cartridge for a gas analyzer device or sensor comprises: a plurality of optical cells, each optical cell of the plurality of optical cells being configured to analyze a different chemical compound and comprising: a light-reflective inner surface, and a laser and receiver pair arranged in the optical cell in such a way that light is reflected a plurality of times on the light-reflective inner surface; and a mechanical connector configured so that the cartridge is insertable and removable from the gas analyzer device or sensor.

Brief of the

Embodiments of the disclosure will now be explained in detail, by way of non-limiting examples only, with reference to the accompanying figures, described below. Like reference numerals appearing in different ones of the figures can denote identical or functionally similar elements unless indicated otherwise.

Figure 1 illustrates a gas analyzer device according to an embodiment.

Figure 2 illustrates a cartridge for a gas analyzer device according to an embodiment.

Figure 3 illustrates an example arrangement of optical cells in a cartridge according to an embodiment.

Figures 4A and 4B illustrate a structural layout of a cartridge according to an embodiment.

Figure 5 illustrates a structural layout of an optical cell according to an embodiment.

Detailed description of Embodiments

Where technical features in the drawings, detailed description or any claim are followed by reference signs, the reference signs have been included for the sole purpose of increasing the intelligibility of the drawings, detailed description, and claims. Accordingly, neither the reference signs nor their absence has any limiting effect on the scope of any claim elements.

It is further noted that dimensions and layout of respective elements of the gas analyzer device (e.g. pressure sensors, dimensions of emitter and sensor and the like) and the cartridge are given as an example and may vary depending on the technical task. The present disclosure generally relates to dynamic gas mixture multiparameter monitoring methods and devices that are suitable for one or more of:

(i) a non-invasive monitoring of a living organism (e.g., patient) with and without the use of various breathing mixtures under physical, physiological, psychological, and stress loads, as well as multiple types of painful conditions, environmental exposure, and nutritional, microbiological and general metabolic states based on the dynamics and composition of exhaled air;

(ii) an assessment of a biological system's functional state, including long-term, for example under the influence of multidirectional overloads;

(iii) expression and screening diagnostics of various diseases and pathologies (e.g., bacterial or viral respiratory tract infections, asthma, lung cancer, COPD, diabetes and others), (iv) a primary diagnosis in determining the severity of the condition to triage victims of emergencies;

(v) a determination of a body's health or metabolism state during and after a workout and physical activity or under the external effects of different nature (including, for example, psychological stress);

(vi) a monitoring of the mental or health state of crew members of autonomous, isolated systems and human-crewed apparatus (including space stations).

The present disclosure is, however, not limited to exhaled gas analysis. In particular, the cartridge is adapted to analyze a predetermined set of chemical compounds and is a replaceable cartridge so that a gas analyzer device or a gas analyzer sensor can easily be configured to analyze different sets of chemical compounds. While the set of chemical compounds may include chemical compounds or components within exhaled air of patients/users, the cartridge configuration is flexible to analyze also chemical compounds in a variety of different industrial settings. For example, using the flexible configuration of directly guiding any gas in the main air line of the cartridge (air is flowing and/or guided through the cartridge) and adapting the optical cells of the cartridge to the chemical compound that is to be analyzed, such specifically configurated cartridges can readily be applied for different industrial and health-care related applications. The present disclosure also relates to a compact interchangeable cartridge comprising a plurality of optical cells, and the cartridge being easily and quickly insertable and removable from a device (gas analyzer device, gas analyzer sensor) in which the cartridge is positioned in an air line. For health care applications, the optical cells can be arranged and positioned inside the cartridge in such a way that an air way or an air path follows a direction of air that is inhaled or exhaled by a user or patient, in other words, a direction toward or exiting from a mouth of the user or patient. In other words, if a user or patient exhales through the device, the exhaled air is guided through the optical cells. For other applications to other gas mixtures, the gas to be analysed is guided or sucked into the cartridge and flows through the optical cell (arranged next to each other). The cartridge may be a tunable diode laser absorption spectroscopy (TDLAS) based cartridge. The skilled person understands that these optical cells may also referred to as multi-pass cells (MPC).

The present disclosure also relates to a gas analyzer device or a gas analyzer sensor including an air measuring device (such as a spirometer) and one or more of the interchangeable cartridges. The compact cartridges are cartridges that can be quickly changed in and out of the device so that the device can be easily and quickly set up to measure and analyze a list of different chemical compounds (by a different type of cartridge). Chemical compounds may include non-organic gases, volatile organic compounds (VOCs), biomarkers, environmental or greenhouse gases, industrial gases, pollutants, compounds of the food, agriculture or beverage industry and the like.

A purpose of the disclosed cartridges and gas analyzer device is to determine a composition and/or changes in the composition of a gas, for example, a respiratory gas or air mixture during exhalation in real-time during the respiratory cycle, based on improved implementation of the principle of dynamic gas medium analysis in determining the quantitative and qualitative composition of exhaled airflow by a continuous analysis of gases absorption spectrum being selected by using one or more of selected compact interchangeable cartridges which are based on TDLAS principles, that is, a selected set of multi-pass optical cells containing a reflective surface, diode lasers and optical sensors. The optical elements (diode lasers and optical sensors) may be selected or adapted to a specific and predetermined set of chemical compounds, for example by using a specific set of diode lasers having respective emission wavelengths for the chemical compounds to be analysed. For example, a first cartridge may be configured with four optical cells having diode lasers emitting at central wavelengths I, 2, X3, X4, respectively with regard to chemical compounds {1,2, 3,4} while a second different cartridge may be configured with four optical cells having diode lasers emitting at central wavelengths X5, X6, X7, X8, respectively with regard to chemical compounds {5, 6, 7, 8}. As an example, in the case of exhaled air analysis, four optical cells in one cartridge can be configured with two organic and two inorganic compounds: {CO, NO, Acetone, Ethane}. The skilled person understands that this is not a limiting example and that the cartridge may have different number of optical cells and/or different wavelength settings.

The disclosed method of dynamic gas analysis can thus implement a continuous analysis of the gas mixture through the entire volume of the analysing gas medium environment of the one or more interchangeable cartridges without sampling or sidestream cuvettes in a compact form factor, allowing, due to the use of laser absorption spectroscopy and preferably a set of pressure, humidity and/or temperature sensors, to work with gas mixtures of arbitrary humidity and flow patterns, as well as different origin and composition.

The dynamic gas mediums analysis method implemented in the disclosed cartridges and gas analyzer device or gas analyzer sensor may be based on absorption spectroscopy and continuous airflow monitoring directly in the air pathway using the compact interchangeable cartridge and preferably a set of pressure sensors. The airflow can be either inhaled or exhaled airflows of different origins and compositions or related to any other gas sucked in or otherwise guided through the cartridge. Such airflows may include the breathing gas mixture delivered to or exhaled by a patient or user (biological object).

A thermal regulation system of the optic and/or optoelectronic elements makes it possible to guarantee these elements' stability and maintain the required accuracy and reliability of the results.

That is, to prevent water vapour condensation due to temperature differences between the flowing (dynamic) gas medium and the optical cells (e.g., on the order of ambient environmental temperature), the cartridge and/or gas analyzer device may further have a thermoregulation system to maintain the set temperature of the optical cells (in a cartridge). Accordingly, the optical cells may be heated by the thermoregulation system when airflow passes through the optical cells. This can suppress a condensation on the inner surface of the optical cells which otherwise would significantly distort optical measurement results due to the emission scattering and its partial absorption. Specifically, the thermoregulation system may include one or more heating elements or wires (e.g. based on resistive Joule heating) at the optical cells (e.g., along or around the optical cell, adjacent to the IR or laser emitter and/or sensor or the like). A temperature sensor (for example at a mouthpiece) may detect a temperature of the dynamic gas medium and the thermoregulation system of the gas analyzer device may thus use a setting for the heating elements to bring the inside of the optical cells (in particular, the internal reflection surface of the optical unit) to a temperature that matches the detected temperature of the dynamic gas medium.

Moreover, in the breath analysis application, as the temperature of the exhaled air is userspecific and may be significantly higher for a patient with a fever, using this thermoregulation system allows to bring the inside of the optical cells to a temperature that matches the detected temperature for the specific user. In other words, if a first temperature of 32°C of the exhaled air is detected for a first user, the thermoregulation system uses a setting to bring the inside of the optical cells (in particular the internal reflection surface of the optical unit) to a temperature that matches this first temperature. On the other hand, if a second temperature of 36°C of the exhaled air is detected for a second user, the thermoregulation system uses a setting to bring the inside of the optical cells (in particular, the internal reflection surface of the optical units) to a temperature that matches this second temperature.

In addition, the thermoregulation system is also useful for gases other than exhaled air. That is, a gas originating in an industrial process or industrial plant, may also have a temperature that differs from the temperature inside the optical cells. The thermoregulation system can thus be configured to maintain a predetermined temperature inside the optical cells, wherein the predetermined temperature is a gasspecific temperature.

In addition or alternatively, the thermal regulation system may also include a cooling system. Specifically, lasers and photodetectors can produce several watts of thermal energy, which preferably should be dissipated to ensure detection accuracy and detection stability. In particular, as the temperature of a laser chip changes, this will shift the spectral emission line at a fixed pump current. Photodetectors are also sensitive to temperature variations and exhibit spectral shifts of detectivity. The thermal regulation system of the cartridge may employ, for example, thermoelectric elements (such as Peltier elements) to provide appropriate heating or cooling, as required. The device may have optical/acoustic/haptic feedback to indicate to the user that the thermoregulation system has sufficiently heated the optical cells in a cartridge. For example, a patient may initially exhale into the gas analyzer device (e.g. into a mouthpiece of the device) and the temperature sensor may detect a temperature of the exhaled air of the patient. As soon as the thermoregulation system has sufficiently heated the optical cell to match this detected temperature, the feedback to the user may indicate that the device is ready to perform an analysis of the exhaled gas medium accurately.

Using the thermal regulation for the optical cells inside a ca rtridge and, therefore in the measurement area of the cartridge (including heating wires or heating elements of the thermal regulation system, or thermoelectric elements such as Peltier elements) allows for a continuous use of the gas analyzer device without changes or drops of humidity and without condensates inside the device. It, therefore, leads to stable measurements. It is noted that the thermal regulation may be provided for the entire optical cell so that the formation of water vapour condensation is avoided in the area around the emitter and sensor as well as the reflecting surfaces of the walls of the optical cell.

An optical cell within a cartridge may have one or more temperature sensors to detect a temperature of the optical cell (e.g., a temperature related to the inner surface of the optical cell, a temperature related to the IR emitter and/or sensor). Using more than one temperature sensor for the optical cell allows one to determine whether the heating or cooling of the optical cell has achieved a thermal equilibrium, for example, when the detected temperatures of two temperature sensors indicate a substantially same temperature. In contrast, if the detected temperatures of two temperature sensors related to a single optical cell and/or related to different optical cells in a cartridge indicate different temperatures, implying that there is not a thermal equilibrium inside the optical cell or the cartridge, then the optical/acoustic/haptic feedback to the user may indicate that the device is not yet ready to accurately perform an analysis of the dynamic gas medium.

Each of the optical cells in a cartridge may comprise a diode laser-based light source and a corresponding receiver (optical sensor). The receiver may further be equipped with an additional monochromatic filter installed in the optical cell. Various photodetectors, such as photovoltaic or pyroelectric, can be used as the receiver (optical sensor). The optoelectronic component list is selected according to the technical requirements for specific use cases.

The optical cell may have a form suitable for a light beam path to have multiple reflections of light originating from the laser-based light source before the reflected light reaches the receiver (multi-pass configuration). These multiple reflections may occur at the optical cell having an internal reflective surface. The internal reflective surface of the optical call may further be provided with a hydrophobic and/or oleophobic coating (layer) on the reflective inner surfaces. This can minimise the risk of condensate and organic contamination, which otherwise can lead to a significant error in measuring the concentration of the detected exhaled chemical compounds. In particular, this can enable the removal of condensate (e.g. any residual condensate after the initial usage of the device before heating) and organic contamination, which can lead to a significant error in measuring the concentration of the bioma rkers (chemical components in the gas medi um) being detected. For example, when liquid microdroplets hit the light-reflective surface, the scattering and absorption coefficients increase, and the measurement accuracy decreases due to distortions in the signal. The hydrophobic and/or oleophobic coating can avoid such problems.

Such a multi-pass configuration increases the interaction of the light emitted from the laser-based light source with the gas mixture and therefore increases the detection accuracy and signal-to-noise ratio. The optical cell may have one of a plurality of forms, such as a ring, a polygon prism, a double ring with the beam path between the outer and inner ring, a cylindrical tube with a spiral beam path along the tube, a cylindrical tube with a straight beam path between the ends of the tube, parabolic or spherical mirrors under optical windows, or the like.

The selection of the optical elements for the optical cells is preferably made according to a list of gases or chemical compounds to be detected and may be chosen according to a technical specification or according to a clinical study, for example according to a specific metabolism process or a specific disease characteristic. Likewise, in an industrial setting, the optical elements for the optical cells are selected according to the chemical compounds of interest. For example, when using a cartridge in a gas analyzer device or sensor for the purpose of environmental monitoring, the optical elements for the optical cells can be selected to assess a concentration of gases and VOCs in the ambient air, for example, specific pollutants, nitrogen oxides, sulfur dioxides, ozone, or other greenhouse gases. As explained, selecting the optical elements for any of these applications can be achieved by a laser-based light source having a selected emission wavelength that corresponds to the chemical compound to be analysed.

Optical cells and cartridges can be installed in parallel or in series, for example, next to each other, so that the gas mixture can flow through the plurality of optical cells. The form or profile of each optical cell, the relative positioning of source and receiver, as well as the wavelength range may be determined for each of the gases or compounds to be detected in such a way to ensure a sufficiently long beam range to obtain a reliable concentration measurement of the specific component (substance, chemical molecule, biomarker), for example, based on the Beer-Lam bert-Bouguer law. Here, a specific placement and alignment of the laser and the receiver can be made during the manufacture of the optical cells and/or the cartridges.

In such a way, in a cartridge having a plurality of optical cells, each being adapted to a specific chemical compound of a gas mixture, each of the individual concentrations of each component of the gas mixture can be determined with high accuracy. In particular, the concentrations of the different gas mixture components may be measured in pre-calculated and non-overlapping spectral ranges for the different optical cells in a cartridge.

The optical cells with respective laser-receiver pairs may be installed in a cartridge in a unique cassette-type device. In otherwords, the device (gas analyzer device orgas analyzer sensor) can be configured in such a way that one or more cartridges can be easily inserted into and removed from the device. As such, the cartridge can easily be taken in and out and therefore exchanged in a device as required. That is, if a different gas mixture is to be analysed and/or the same gas mixture (e.g. exhaled air) is to be analysed with regard to different chemical components, this can be readily achieved by exchanging a first cartridge configured for a first set of chemical components with a second cartridge configured for a second set of chemical compounds (being different from the first set of chemical compounds).

A cartridge may be configured with a cartridge identification element. The cartridge identification element preferably identifies properties of the cartridge, such as a number of optical cells and/or a configuration of the optical cells and/or an indication of specific chemical components measurable or analysable with the cartridge. When a cartridge is inserted into the device, a physical interaction between the device and the inserted cartridge or another cartridge (already present in the device) and the inserted cartridge takes place, for example, by an optical, electrical or magnetic reading out of the cartridge identification element so that a control device of the device may acquire the properties of the cartridge and can appropriately set up or control the device, for example by adjusting a setting of the device. The adjusting of the setting of the device may be related to a setting of a display (e.g. indicating the specific chemical components and corresponding measurement data), setting of a specific control of the cartridge (e.g. with regard to the power supply of the individual electric components, with regard to the data communication and control of respective sensors inside the cartridge) and/or a setting of the thermoregulation system for the optical cells in the specific cartridge.

The cartridge may be connected via a shielded pair, fibre-optic cable, or wireless communication channel to the control unit, which may include a signal modulator via a signal converter. The control unit may use feed-forward and feedback channels and may be connected to an external data server, computer, tablet, smartphone and/or wearable device.

The basic concept of the compact interchangeable cartridge is the ability to adapt the gas analyzer device or sensor to different clinical tasks (e.g., a diagnostic device) or different industrial tasks (monitoring different sets of environmental gases, forexample) quickly. For this, the cartridges may have a mechanical connector configured so that the cartridge is insertable and removable from the gas analyzer device or sensor. For example, a cartridge may be fitted with spring-loaded connectors on the ends of the cartridges, allowing them to be connected to the power and data acquisition systems immediately during installation into the main air line without any additional steps. The cartridge may only be inserted/screwed until a mechanical connector clicks into place, providing an easy-to-use and easy-to-replace chemical component-specific cartridge. For example, to switch the gas analyzer device from a lung cancer diagnosis mode to a diabetes diagnosis mode, a cartridge specific to analyzing chemical components related to lung cancer diagnosis may be simply replaced (for example, within seconds, without a couple of simple movements and without special tools) by another cartridge specific to analyzing chemical components related to a diabetes diagnosis.

The readings from an IR receiver or sensor of an optical cell depend on the concentrations of a (test) component or substance in the gaseous medium. The readings or measurement results may be compared with values of similar indicators accepted as a standard for respective conditions (for example, medical conditions). A signal may be sent to an external monitoring and control unit (for example, the external data server, computer, tablet, smartphone and/or wearable device) when a deviation from the norm occurs.

To implement the dynamic gas analysis method, the device may be equipped with a set of pressure, humidity, and temperature sensors to improve measurement accuracy.

The air passing through the cartridge can have a high degree of turbulence. The cartridge and/or gas analyzer device may have flow guidance members to keep a roughly constant cross-sectional area along the air line of each of the optical cells to avoid significant turbulence. For example, to laminarise the flow in each cartridge, one or more mechanical grids (such as a Honeycomb-based gride) can be used to eliminate or suppress eddy currents. This preferably means that the Reynold numbers of 100 or less are achieved.

The gas analyzer device can operate as follows: A gas mixture to be analysed enters the main air line. Then, as the air passes through the (exhalation) air line, it passes through one or more integrated cartridges. A grid (Honeycomb) can be installed at the cartridge inlet to eliminate airflow eddies. In case of temperature jumps or hot incoming air, the components in the cartridge are preferably thermoregulated. The chemical composition of the air mixture can be recorded and interpreted by transmitting a signal from the laser to a receiver in each optical cell and then a measurement signal or measurement data can be transmitted through an information line or wireless communication channel to the control unit of the gas analyzer device. The control unit may use elements of direct and feedback communication and is connected to an information processing unit, where the signal or data are interpreted. Regarding direct and feedback communication, for example, the control unit of the device can receive feedback on a laser chip temperature, regulate the chip temperature via a Peltier element control, and switch off the lasers altogether when a critical temperature is reached.

The cartridge can be easily disattached/replaced out of the main air line and cleaned if needed.

A replaceable membrane filter can be pre-installed on the cartridge to prevent contamination of the reflective surface of the optical cells.

To assess the volume and speed of the air passing through and to ensure accurate readings, a set of pressure sensors can be built into the cartridge to provide real-time information on the volume of the air coming in, as well as the concentration of detectable components, regardless of pressure variations in the main line. A humidity sensor for exhaled air and a temperature sensor is also installed in the cartridge to provide concentration information regardless of temperature and humidity fluctuations in the airflow.

The gas analyzer device may also be provided with an air-measuring device such as a flowmeter, which can be built into the cartridge.

The device may also be provided with a handle in case of a stand-alone device. The handle also may contain a flowmeter, set of pressure, humidity, and temperature sensors to analyze dynamic gas medium parameters. In addition to pressure sensors, the handle (spirometry handle) may have a flowmeter (spirometer) to measure the exhalation rate, the volume of the passing gas mixture and other functional indicators of the human respiratory system (FEV1, Vital Capacity, Tidal Volume, etc.). The handle may also contain related microelectronic components, an LED display and/or a battery pack.

The gas analyzer device may also be equipped with a built-in sensor set for assessing a condition of a patient or user (biological object) located on the spirometry handle or the cartridge. Such sets may include a single and/or multi-point ECG system, a body temperature sensor, a pulse oximeter, and/or a body electrical resistance evaluation system which may be arranged and positioned on or around the cartridge.

Due to the handling of biological objects, it may often be necessary to provide disinfection of the outgoing air stream. One or more ultraviolet (UV) light sources may be used for this purpose. The location of a UV radiation source in the compact interchangeable cartridge and/or handle can vary along the air line; that is, they can be located in front of the compact interchangeable cartridge, directly in the compact interchangeable cartridge or after the compact interchangeable cartridge. The direction of the radiation should be arranged in such a way so as not to harm the patient and/or the operator (medical personnel).

In the cartridge, an optical cell may also be a nondispersive infrared based (NDIR- based) optical cell having a broad range (for example, in a range between 2 and 12 microns) IR emitter (for example, an absolute black body or IR LED) a nd IR sensor can be located in the NDlR-based optical cell in such a way so as to provide a direct emitting from a broad range I R emitter to IR sensor (that is, without a multi-pass configuration) to have a sufficient optical path length between them. The IR sensor may have at least two channels with pre-installed optical filters, where one of the channels can be used as a reference channel to improve measurement accuracy and signal-to-noise ratio.

NDlR-based optical cells can solve the problem of determining H2O and CO2 concentrations at the ppm level without using more expensive diode lasers. Determining the concentration of H2O and CO2 may be necessary for their further exclusion from the signal of the main detectable molecules in the compact interchangeable cartridge. These optical cells can detect concentrations of other molecules at ppm and above in addition to H2O and CO2.

The NDlR-based optical cell may be designed to position the IR sensor at a focal point with the highest intensity for a reliable concentration determination of the chemical compounds, and the emissions from the NDl R-based optical cell should not reach the sensors of the other optical cells to avoid unnecessary noise. Additional lenses or axicons can be fitted for these purposes.

Based thereon, a cartridge may include at least one NDlR-based optical cell (not having a multi-pass configuration) and one or more TDLAS-based optical cells (having a multi-pass configuration).

The NDlR-based optical cell can also be pre-installed in the gas analyzer device (e.g., in a spirometer handle) or gas analyzer sensor itself without the need to remove them (with the cartridge). This allows the compact interchangeable cartridge to be reduced in size.

The data in the gas analyzer device may be acquired by the cartridge, which may be connected to a microcontroller via a shielded pair, fibre-optic cable, or a wireless communication channel. The microcontroller allows to control the lasers and to process the signal from the IR sensors while measuring concentrations of the gas components and transmitting data from other sensors to the output device. The gas analyzer device may also have a unit for digital processing and storing the acquired data.

The gas analyzer device may also be adapted to be used in emergency and extreme situations to ensure the vital activity of a biological object (patient). Here, various patient monitoring systems may be suitably combined or integrated into the gas analyzer device, and which are adapted to monitor possible deviations of vital signs from normal ones and have feedback with the control unit of breathing mixture and medication delivery. These systems may include wearable systems for obtaining data such as ECG, EEG, blood pressure values and others.

The use of feedback to the breathing mixture control unit may allow the output parameters to be monitored. It may equalise the conditions for measuring gas component concentrations, improving the gas analysis quality. In addition, feedback to a medication supply unit may allow maintaining the patient's condition at minimum vital signs in an emergency or other extreme situation. Here, the use of feedback to the breathing mixture control unit may allow the output parameters of a breath mixture provider to be monitored and regulated. This combination may automatically adjust the breath mixture component concentrations, improving the quality of breath in real time. In addition, feedback to a medication supply unit may allow for maintaining the patient's condition at minimum vital signs in an emergency or other extreme situation.

The gas analyzer device may also be adapted to be used in the automatic regulation and control of technological processes (e.g., semiconductor manufacturing, natural gas transporting, metal processing, and pharmacy). Here, various technological monitoring systems may be suitably combined or integrated into the gas analyzer device, and which are adapted to monitor possible deviations of technical parameters from normal ones, and have feedback with the control unit of technical gas mixtures delivery. These systems may include calorimeters, trunk pressure sensors, spectral gas mixture indicators, temperature sensors, and leakage sensors.

The gas analyzer device can also be provided with an alarm unit for measured parameters exceeding critical values, ensuring a timely response of a patient, medical staff or operator to such a situation.

The gas analyzer device and/or the cartridges and/or the optical cells in the cartridges may further be provided with a thermoregulation system to suitable address a difference in temperature between exhaled air and the optical cells. The thermoregulation system may include heating elements or heating wires and a set of temperature sensors. Such a dynamic thermoregulation system can prevent a condensation from forming inside the optical cell, in particular on the reflective surfaces and/orthe optical elements. Water vapour condensation on the inner surface of the optical cell can significantly distort spectral measurement results due to the emission scattering and its partial absorption on the surface, achieving for example a 200 square centimetres area. For example, water vapour condensation can form due to temperature differences between the exhaled air (on average 32-33 degrees Celsius) and the optical cell (on the order of ambient temperature).

The gas analyzer device and/or the cartridges may further be provided with an additional insulating cover to stabilise the temperature regime inside the optical cells. When the exhalation temperature and the temperature of the optical cells match, the heating process can be stopped automatically.

The gas analyzer device and/or the cartridges may also be provided with cooling elements. In particular, diode lasers in such systems can heat up considerably. As such, a heat sink for the optoelectronic components may stabilise emission wavelengths and improve detection accuracy. It is also important for photodetectors to maintain low chip temperatures to reduce signal-distorting dark currents.

The gas analyzer device and/or the cartridges may also be provided with a casing having a shielded protection. This is advantageous if the device is used or operates in an environment with electromagnetic interference.

Further, the electronic components are protected inside the cartridge housing. For example, the air environment inside the cartridge can be isolated from the outside air and environment. The electronic components can also be fixed inside the cartridge on damping elements such as damping pads (e.g., made of silicone).

Further, in an optical cell of the cartridge, the light source (laser or diode) and receiver (for example, IR sensor) may be placed behind a protective transparent window (for example, IR transparent window) to avoid a direct contact of gas (exhaled or other gas) with the optical elements of the optical cell in a cartridge.

The gas analyzer device may also be equipped with external fixing elements for fixing the device in space. The device can be mounted on horizontal and vertical surfaces.

The compact interchangeable cartridge can also be fitted with fa I l/vi bration sensors and/or an electromechanical alignment with an automatic calibration system for the optical components. This means there is no need to adjust the device after minor jolts and falls manually. For example, the laser and the IR sensor may have 5 degrees of freedom (3 axes and 2 angles) which can be used to adjust their mutual positioning within the optical cell. Automatic adjustment can be based on (i) a lidar approach or (ii) mathematical algorithms for finding the maximum signal value using precision piezoelectric screws.

In addition, sets of flat, spherical or parabolic mirrors can be placed between the point of entry of the laser beam into the optical cell and the emission source to fine-tune the emitter-receiver pair (e.g., laser-photodetector pair).

Moreover, in order to make the device compact and portable, flexible or semi-flexible circuit boards can be used on which all the associated electronics are mounted. These PCBs can be wrapped around the optical cells to keep the entire device round and compact without any protruding parts.

Further, a set of silicone or rubber gaskets can be used at the joints of the parts of the gas analyzer device to prevent dust and moisture from entering the device's interior.

To ensure an uninterrupted operation of the gas analyzer device, a power supply unit can be equipped with a fixed power supply unit connected to the mains or a mobile battery-powered power supply unit, depending on the configuration. The rechargeable batteries can be charged using a wireless charger.

Further, a cover can be placed at the end of the gas analyzer device after the cartridges to prevent external radiation from reaching the optical sensors inside the cartridges.

Figure 1 illustrates an example of a gas analyzer device with two cartridges 2 inserted after each other. As illustrated, each of the cartridges has four optical cells 10 installed. The gas analyzer device further has a spirometer handle 1, a cover 3, a mouthpiece 4, a gas dynamic (temperature, humidity, pressure) sensor 5, a microcontroller and power supply unit 6, a data transmission unit 7, a battery back 8, and a charger 9. The skilled person understands that the number of optical cells in a cartridge is not limited to four optical cells and that a cartridge may also comprise more or less than four optical units. Each of the optical cells may have a diode laser emitting at a different central wavelength (e.g., XI - X4) specific for each of a plurality of chemical compounds (e.g., 1 - 4) to be identified and analysed, for example, to determine a specific concentration of a chemical compound in the gas medium entering the device and flowing or being guided through each of the optical cells in the respective cartridge to leave the device on the opposite side.

According to the gas analyzer device for a medical application, a patient exhales through the mouthpiece 4 into an exhalation line of the device. When the air flows through the exhalation line (including the mouthpiece and area around the gas dynamic sensor 5 in the handle 1) through the compact interchangeable cartridge 2 and therefore through each of the optical cells 10 in the cartridges 2, the dynamic gas characteristics (flow parameters) and chemical composition of exhaled air and/or concentration of specific chemical compounds can be determined by transmitting the optical signal from the respective emitter (diode laser) to the optical sensors 11 of each optical cell 10. Then the detected signals are transmitted on an information line or wireless communication channel to the microcontroller or the control unit 6 (preferably with elements of direct and feedback) and/or the data processing unit 7, where the received signal is decoded, interpreted, and recorded. Acquiring data from the compact interchangeable cartridge begins when the patient has contact with the gas analyzer device (for example, detected by a contact sensor). Between acquiring data sessions, the gas analyzer device preferably determines background characteristics (for example, concentrations of chemical compounds in an ambient air, ambient temperature, humidity, and other related parameters) at a pre-set frequency - in the case of medical use, this approach compares inhaled and exhaled air parameters.

Figure 2 illustrates further details of the cartridges 2 for the gas analyzer device. In particular, Figure 2 shows that each of the cartridges 2 has four optical cells 10 being arranged and positioned after each other (in the air line, with a central axis through each of the optical cell 10). Each of the optical cells 10 is illustrated with a laser beam receiver (optical sensor) 11 under a protective optical window (the corresponding laser is not illustrated in this view). Each of the cartridges is also illustrated with a thermostabilising cover 12. As further illustrated in Figure 2, the cartridges 2 are inserted in the gas analyzer device having the spirometer handle 1.

Figure 3 further illustrates an explosion view of four optical cells 10 arranged after each other in a cartridge 2. Each of the optical cells 10 is formed as a ring in such a preferred embodiment, and each of the optical cells 10 has a diode laser or IR emitter (related to different central wavelengths corresponding to a different chemical compound) and a corresponding optical sensor. The diode laser or IR emitter is preferably positioned at non-diagonal positions so that the emitted light requires multiple reflections at the light-reflecting inner surface (multi-pass configuration) to arrive at the sensor, for example by following a spiral beam path (the plane of the laser beam spreads also along the symmetry axis of a cylinder optical cell) or the like along the inner surface of the optical cell. Further, the diode laser or IR emitter are preferably arranged in such a way that the light is emitted in a limited spatial range so as to avoid that the emitted light reaches a neighbouring optical cell.

As explained above, each of the two cartridges in Figure 1 can be easily removed from the gas analyzer device and replaced by another cartridge that is suitable to analyze the same or different chemical elements or compounds.

Figures 4A and 4B illustrate a structural layout of a cartridge 2 having a thermostabilising cover 12 for the example of four optical cells 10 arranged next to each other, and each optical cell being illustrated with a respective diode laser (light source) for emitting light toward the interior of a respective optical cell through which the gas medium flows by entering one side of the cartridge and leaving at the opposite side of the cartridge. The corresponding light sensors/receivers in the optical cells are not illustrated here.

Figure 5 illustrates a structural layout of an optical cell 10 (as an example of an optical cell in the cartridge 2, as illustrated in Figures 4A and 4B, for example). In particular, Figure 5 illustrates the optical cell with a laser light source and a receiver which are positioned off-diagonally at an optical ring of the optical cell 10. As shown, the laser light source may be provided with a protective glass. The receiver (for example, implemented as a photodetector), may be configured with a protective glass and/or a filter element and/or focusing lens. In addition, Figure 5 also indicates a heating element (of the thermoregulation system), here in the form of tubular heating elements being wound around the optical cell. While not shown in Figure 5, the tubular thermoregulation elements may also be a combination of heating thermoelectric and Peltier elements.

The data acquired from the compact interchangeable cartridges indicates the concentrations of the substances under examination in the gas medium. They can be compared with the values adopted for the substances under examination as a physiological norm for the measuring conditions (e.g., test with or without physical activity). In case of deviations from the baseline, a signal can be given to the external control system and medical professionals.

Further, a disposable membrane filter can be fitted upstream of the exhalation line to prevent contamination of the reflective surface of the optical cells with waste products. A petal valve can be installed in the main air pathway before the cartridges to avoid air backflow. The petal valve can be combined with the mouthpiece and the filter.

To improve the device's ergonomics, an adapter can be installed in front of the cartridges to provide a connection between (i) the spirometer handle 1 and (ii) the mouthpiece 4. A replaceable or disposable membrane filter and/or a petal valve can be installed inside the adapter.

The mouthpiece 4 may be an exchangeable mouthpiece. Using an exchangeable mouthpiece in combination with the gas analyzer device can minimise the risk of possible transmission of infection between patients and can ensure that many patients can be handled, in particular in a short time. Using a mouthpiece can also reduce measurement errors due to the distance of the patient's lips to the instrument (gas analyzer device, cartridges, optical cells) when exhaling, the angle of inclination, or environmental conditions (presence of various gaseous contaminants in the environment, wind strength and direction, etc.). The adapter can optionally be equipped with at least one of the pressure, humidity and temperature sensor.

To prevent contamination of the elements of the gas analyzer device by biological agents (saliva, sputum, blood, etc.) or the like, the adapter can be supplemented with a replaceable membrane filter. The filter can also have a desiccant property to reduce water vapour concentration to ambient levels. This technical solution can partially mitigate the formation of condensation on the internal surfaces of the optical unit. When a petal valve and a membrane filter are used together, the latter is installed upstream of the petal valve.

At least two pressure and humidity sensors can be installed to estimate exhaled air volume, breath manoeuvres and humidity: one in the breathing mixture supply system and one/other in the exhalation pathway behind the filter and front of/between the optical cells, providing real-time information on the volumes and humidity of the air entering compact interchangeable cartridge as well as the concentration of detectable components, regardless of pressure variations in the line.

Disinfection of the cartridges and outgoing airflow can be provided to ensure the safe repeated operation and compliance with sanitary requirements when working with biological objects (patients). For this purpose, one or several sources of UV radiation can be installed, which can be located in front of the compact interchangeable cartridge, directly in the compact interchangeable cartridge or after the compact interchangeable cartridge and/or in the adapter before the membrane filter.

The gas analyzer device based on the cartridges can be used independently or in conjunction with long-wear condition monitoring and emergency systems.

When the gas analyzer device is used in medical facilities, as well as in training systems for professionals working in various types of stress conditions (including the training of mountaineers, scuba divers, emergency personnel, athletes and flight personnel or the like), the feedback can be provided in the form of a warning system for the operating personnel. In such cases, the attending personnel can decide to change the composition of the breathing mixture or administer other preparations.

The gas analyzer device can be used in medicine as diagnostic equipment and in disaster medicine (including resuscitation equipment installed on vehicles); in protective equipment and outfit of emergency staff during the elimination of high-risk fires (when there is a risk of release of harmful substances) and unnatural disasters; in an outfit of scuba divers and divers during underwater works with high physical load and diving to great depths; in the composition of mountaineering oxygen equipment.

Further, a forced air intake (suction) system can be installed in the air line of the gas analyzer device to regulate the airflow speed in the compact interchangeable cartridge. This system can be located after the compact interchangeable cartridge. This solution allows an operator to refresh the gas mixture in the cartridge without additional manipulation or to distribute the passing airflow evenly, if necessary. Furthermore, synchronisation of the forced-air intake system with the pressure sensors can facilitate uniform airflow and a further reduction of aerodynamic resistance in the air line. The proposed cartridge and/or gas analyzer device and/or gas analyzer sensor may apply the following advantages:

1) Acquiring and processing the multiparametric data can be obtained in real-time from an airflow by TDLAS-based high-precision cartridges, temperature, pressure, humidity and flowmeter sensors without air samples and side-stream cuvettes.

2) Absorption spectroscopy, a method of dynamic gas analysis based on continuous analysis of the flowing airflow using a set of optical laser-sensor pairs and gas-dynamic sensors to obtain the ratio between the total volume of a dynamic gas and the quantity of the chemical compound in the gas mixture; this provides information on both the quantitative flow of the gas mixture and the concentration of the chemical components in real-time, which may include the viscous flow regime with variable flow characteristics

3) Absence of a separate movable focusing element eliminates the effects of defocusing due to vibration, side acceleration and other mechanical influences

4) Minimized weight and size: the overall system is based on the compact optical lasersensor pairs built into the main air line.

5) The optoelectronic elements used in the absorption spectroscopy method (e.g., diode lasers, photovoltaic sensors) do not require cryogenic cooling to maintain special operating conditions.

6) Unlike photo-ionisation and semiconductor sensors, absorption spectroscopy avoids accumulating errors over time. Sensors of this type are not affected by external influences and have no inertia, i.e. can take readings during a breathing cycle repeatedly and over a long period.

7) Unlike bulky mass spectrometers, optical gas analyzers can be built directly in an air line.

8) Systems of thermoregulation and thermal stabilisation of optical elements guarantee the stability of the work of these elements and observe the required accuracy and reliability of results. The present disclosure based on laser absorption spectroscopy (incl. TDLAS) with interchangeable cartridges as described above thus allows for an easy adaptation of the device or sensor for specific applications. This technology can be used for realtime continuous detection and assessing the presence and/or concentration of gases and VOCs in main air flows without the need for air sampling in a variety of areas and industries, as described below.

Environmental monitoring: The present disclosure can be used to monitor and quantify the concentration of gases and VOCs in the ambient air, allowing for realtime detection of pollution and identification of its sources. Interchangeable cartridges can be used to adapt the device or sensor for specific applications, such as measuring the concentration of pollutants in urban or industrial areas. For example, TDLAS-based cartridges can be used to measure and monitor the concentration of greenhouse gases like carbon dioxide and methane in the atmosphere. This can be useful for assessing the impact of human activities on the environment and developing strategies to reduce greenhouse gas emissions. Specific TDLAS-based cartridges can also be used to detect and quantify the presence of pollutants in the air, such as nitrogen oxides, sulfur dioxide, and ozone.

Industrial emissions monitoring: The present disclosure can also be used to monitor and quantify the concentration of gases and VOCs emitted from industrial processes and plants. Interchangeable cartridges can be used to adapt the device or sensor for specific applications, such as measuring the concentration of pollutants in stack emissions or off-gas streams. TDLAS-based cartridges can be used to detect and measure the concentration of pollutants such as nitrogen oxides, methane, sulfur dioxide, and carbon monoxide. In addition, TDLAS-based cartridges can be used to measure and monitor the composition of gases in industrial processes.

Petrochemical refining and chemical manufacturing: The present disclosure can also be used to monitor and subsequently control petrochemical and chemical plants' refining processes in real time, allowing online automatic adjustments to be made as needed. Here, interchangeable cartridges can be used to adapt the device or sensor for specific applications, such as measuring the concentration of gases and VOCs in the distillation column's tunes, the off-gas stream, and in a chemical reactor.

Semiconductor manufacturing: The present disclosure can also be used to monitor and subsequently control the semiconductor's manufacturing processes in real time, allowing for online automatic adjustments. For example, the cartridges can be built into production equipment or in gas transmission lines between equipment (equipment for etching or the like).

Food, agriculture, and beverage production: The present disclosure can also be used to monitor and subsequently control the production of food and beverages in real time. Here, interchangeable cartridges can be used to measure the concentration of gases and VOCs in the processing or storage environment. For example, TDLAS-based cartridges can measure the concentration of gases like carbon dioxide and oxygen in food storage environments. TDLAS-based cartridges can also be used to measure the concentration of gases like ethylene, which is produced by fruits and vegetables as they ripen.

Indoor air quality monitoring: The present disclosure can also be used to monitor and measure the concentration of gases like carbon dioxide, carbon monoxide, and volatile organic compounds (VOCs) in indoor environments. This can be useful for assessing indoor air quality and identifying potential sources of indoor air pollution. Interchangeable cartridges thus allow for easy maintenance and cleaning of the detection system in the case of contamination.

Airborne molecular contamination (AMC) monitoring: The present disclosure can also be used to monitor and measure the concentration of gases like water vapour, hydrogen peroxide, and other organic vapours in cleanroom environments. This can be useful for identifying potential sources of AMC and maintaining the cleanliness of cleanroom environments. The present interchangeable cartridge-based system allows for an easy adaptation of the detection system using a gas analyzer device or sensor to different VOCs, biological objects and the chemicals they produce.

Medical diagnostics and patient monitoring: The present disclosure can also be used in medical diagnostics to measure the concentration of gases in exhaled breath. For example, it can be used to measure the concentration of carbon dioxide and oxygen in the breath of patients with respiratory disorders or during anaesthesia. The present disclosure also can be used for diagnostic purposes, for example, acetone measurements in exhaled air for patients with diabetes.

Chemical warfare agent detection: The present disclosure can also be used to detect, identify and/or quantify chemical warfare agents, such as nerve agents or blister agents, in the air. Interchangeable cartridges can be used to customise the device or sensor for specific agents, allowing for a rapid response to potential threats. Explosive and drug detection: The present disclosure can also be used to detect, identify and/or quantify explosive materials and drugs in the air. TDLAS-adapted cartridges in respective gas analyzer devices or sensors can be used to ensure security in public places and to prevent illegal drug traffic. In particular, interchangeable cartridges can be used to customise the sensor for specific explosive materials and drugs.

A cartridge-based gas analyzer device or sensor can be set up on a variety of mobile devices or platforms, such as a portable handheld device, a drone, a mobile robot, a vehicle and the like.

List of Reference Signs

1 - spirometer handle

2 - cartridge

3 - cover

4 - mouthpiece

5 - sensor

6 - microcontroller and power supply unit

7 - data transmission unit

8 - battery pack

9 - charger

10 - optical cell

11 - optical sensor

12 - thermostabilising cover

Claims

1. A cartridge for a gas analyzer device or sensor, the cartridge comprising: a plurality of optical cells, each optical cell of the plurality of optical cells being configured to analyze a different chemical compound based on laser absorption spectroscopy and comprising: a light-reflective inner surface, and a laser and receiver pair arranged in the optical cell in such a way that light is reflected a plurality of times on the light-reflective inner surface; and a mechanical connector configured so that the cartridge is insertable and removable from the gas analyzer device or sensor.

2. The cartridge of claim 1, further comprising: one or more pressure sensors to evaluate a gas dynamic characteristics of a gas mixture or gas medium passing through the optical cells.

3. The cartridge of one of claims 1 - 2, further comprising a thermoregulation system configured to maintain a predetermined temperature inside the optical cells.

4. The cartridge of claim 3, wherein the predetermined temperature is a gas-specific or user-specific temperature.

5. The cartridge of one of claims 1 - 4, wherein the light-reflective inner surface of the optical cell is coated with a coating having hydrophobic properties and/or oleophobic properties.

6. The cartridge of one of claims 1 - 5, wherein the optical cell includes more than one laser and receiver pair.

7. The cartridge of one of claims 1 - 6, wherein the optical cells are configured for analyzing a predetermined chemical compound by a selected laser wavelength.

8. The cartridge of one of claims 1 - 7, wherein the respective receivers of the optical cells in the cartridge are configured to transmit measurement data to a controller of the gas analyzer device or sensor.

9. The cartridge of one of claims 1 - 8, wherein the cartridge further has an enclosure made from a heat-insulating material.

10. The cartridge of one of claims 1 - 9, wherein the light-reflective inner surface is further provided with an optical window with a transmittance of 0.90 or higher in a laser and receiver pair spectrum.

11. The cartridge of claim 10, wherein the optical windows are removable for a subsequent cleaning and reinstalment in seats of the cartridge.

12. The cartridge of one of claims 1 - 11, wherein a cassette-type device is wholly or partly integrated into the cartridge to enable a rapid replacement of one of the optical cells or its components in the cartridge.

13. The cartridge of one of claims 1 - 12, wherein the cartridge further comprises an ultraviolet radiation source not overlapping an absorption spectrum of the receiver.

14. The cartridge of one of claims 1 - 13, wherein the cartridge further comprises a humidity sensor to assess the gas dynamic characteristics.

15. The cartridge of one of claims 1 - 14, wherein the cartridge further comprises one or more temperature sensors.

16. The cartridge of one of claims 1 - 15, further comprising a grid to guide an airflow through the optical cells.

17. The cartridge of one of claims 1 - 16, further comprising a set of silicone or rubber gaskets to prevent dust and moisture from entering the interior of the cartridge.

18. The cartridge of one of claims 1 - 17, further comprising an electromechanical alignment and/or calibration system for optic and/or optoelectrical components of the optical cells.

19. The cartridge of one of claims 1 - 18, further comprising spring-loaded connectors on respective ends of the cartridge.

20. The cartridge of one of claims 1 - 19, further comprising an additional NDlR-based optical cell having a diode and a receiver pair.

21. The cartridge of one of claims 1 - 20, wherein the plurality of optical cells are configured to determine a concentration of a chemical compound in at least one of ambient air, a gas medium emitted from an industrial process or a plant, a gas medium in a cleanroom environment, a gas medium related to processing or storage of food, agriculture, or beverage production, an indoor or airborne gas medium, an exhaled gas, a gas medium including chemical agents. a gas medium indicating explosives or drugs.

22. A gas analyzer device or sensor including one or more cartridges of one of claims 1 - 21.

23. A mobile device including a gas analyzer device or sensor of claim 22.