POINT-OF-CARE CONCENTRATION ANALYZER

Abstract

An analyzer system includes a cartridge configured to receive a sample. The cartridge has a plurality of chambers to isolate a target analyte from the sample and collect an amount of a first marker that is proportional to the amount of the target analyte in the sample. The system includes an analyzer with a first electromagnetic radiation source, a first detector, and a controller. The first electromagnetic radiation source is configured to provide electromagnetic radiation to form a search space within a detection chamber of the cartridge. The first detector is configured to detect the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space. The controller is configured to identify the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector.

Description

POINT-OF-CARE CONCENTRATION ANALYZER CROSS REFERENCE TO RELATED APPLICATIONS This application claims the benefit of U.S. Provisional Patent Application No. Q62 / 817,433, filed on Tuesday, March 12, 2019, which is incorporated herein by reference in its entirety. TECHNICAL FIELD The present invention relates in general to the automated treatment of samples, measurement and analysis of samples to isolate, label, detect and determine the amount of specific target analytes that may be present at very low concentrations. BACKGROUND Numerous studies and advances in understanding the underlying causes and progression of diseases have demonstrated that detecting infectious agents or identifying an abnormality at an early stage, along with appropriate treatment, substantially improves clinical outcomes. Many conditions that previously required costly symptomatic measurements, such as anatomical imaging, which necessitate administration and interpretation by trained specialists, can now be diagnosed at the cellular and molecular level through the presence and / or concentration of specific biomarkers. These biomarkers include proteins, nucleic acids, or other molecules that are upregulated or downregulated and are highly specific to a disease, condition, or infection. It is often desirable to diagnose certain conditions at the point of care, where time and the administration of the correct treatment are critical to the patient's outcome. This is especially true in acute care settings such as trauma centers, where patients may have suffered an acute myocardial infarction (AMI), acute decompensated heart failure, pulmonary embolism, sepsis, or other conditions requiring a timely response. In non-acute settings, a rapid response time is also desirable, particularly in the case of highly infectious diseases such as Clostridium difficile infection, where quarantine might be necessary. However, even in a doctor's office or primary healthcare setting, it is highly beneficial to determine whether a condition is viral or bacterial before administering antibiotics. In some diseases, the concentration of the biomarker or analyte of interest is relatively high, and simple, low-cost lateral flow devices can be used for sample processing and reading. These devices and the consumable components that interact with the sample are very inexpensive and can be deployed quickly with relatively little or no point-of-care training. However, lateral flow tests also tend to suffer from poor accuracy, resulting in quantitative measurements of marginal quality, even when using an objective reading system to measure the strips. Furthermore, depending on the stage of the disease or infection, the concentration of the target analyte is often too low to be detected by lateral flow in blood, urine, saliva, or other sample types. In these cases, sample treatment and reading are more complex. They often require precise measurement to assess concentration, high efficiency to avoid loss of the target analyte, and centrifugal separation as the primary purification step. In addition to centrifugation, further purification steps typically include incubation with reagents containing binding members or molecules with complementary structures or sequences to bind to the target analyte biomarker. These binding members can be substrates such as micro- or nanoparticles with complementary molecules on their surfaces, molecules conjugated to transduction markers, or both. Once binding occurs, further treatment steps are required to wash and further isolate the target analyte for suspension in a pristine buffer solution or placement on a clean surface before measurement.To carry out these treatment stages, multiple devices are used, including centrifuges, mixers, incubators, precision hQ^n Ln / Lznz / E / YiAi pipettes, and thermocyclers, where the sample is often transferred and dispensed between treatment stages using multiple disposable tips, tubes, plates, and other sample containers. Once the treatment is complete, highly sensitive and precise instruments are used to measure the treated sample and determine the presence and / or abundance of the target analyte. Although the analysis of low-concentration biomarkers can take various forms, in general, the treatment and measurement of the sample have the following main characteristics: 1. A separation step to perform an initial isolation of the target analyte from other components of the sample 2. Introduction of bonding members and reagents 3. Mixing and incubation to label and bind the target analytes to a substrate 4. Introduction of buffers and stages to wash away unbound markers and other contaminants 5. Sterile containers for accurate measurement and containment of the sample during treatment 6. An effective and accurate means for sample transfer 7. A measuring device that provides high sensitivity and accuracy for determining the presence and abundance of the target analyte. Currently, the processing and measurement of low-concentration biomarkers must be performed by trained personnel or using highly specialized equipment in centralized locations. Consequently, the time between sample collection and results is lengthy, the cost of the instrumentation is high, and measurement cannot be performed at the point of care. Accordingly, the present inventors have recognized the need for an improved technique that can address the main characteristics listed above for the treatment and measurement of low-concentration biomarkers. The technique must be suitable for point-of-care environments with minimal fungal materials, accurate measurement, a rapid response time, and sensitivity that overcomes the limitations of the prior technique. U.S. Patent No. 8,264,684 and U.S. Patent Application Publication No. 2016 / 0178520, each incorporated herein by reference, describe prior systems that achieved extremely sensitive detection. This disclosure provides further development in this field. BRIEF DESCRIPTION OF THE INVENTION This document discloses analyzer systems, cartridges, and methods for detecting a target analyte in a sample. Advantageously, the analyzer system embodiments utilize a compact cartridge for sample processing and analysis, resulting in a small analyzer size suitable for point-of-care delivery. Therefore, in one respect, this disclosure provides an analyzing system comprising: a cartridge configured to receive a sample, the cartridge including a plurality of chambers for isolating a target analyte from the sample and collecting an amount of a first marker that is proportional to an amount of the target analyte in the sample; a first source of electromagnetic radiation configured to provide electromagnetic radiation to form a consultation space within a cartridge detection chamber; a first detector configured to detect electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and a controller configured to identify the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector. This, as well as other aspects, advantages, and alternatives, will become evident to those experts in the field by reading the following detailed description. hQ^n Ln / Lznz / E / YiAi BRIEF DESCRIPTION OF THE DRAWINGS The accompanying drawings are included to provide further understanding of the disclosure methods and devices and are incorporated into and form part of this descriptive report. The drawings are not necessarily to scale, and the sizes of various elements may be distorted for clarity. The drawings illustrate one or more embodiments of the disclosure and, together with the description, serve to explain the principles and operation of the disclosure. Figure 1 is a schematic front perspective view of a high sensitivity analyzer according to an embodiment of the disclosure; Figure 2 is a schematic rear perspective view of the analyzer in Figure 1; Figure 3 is a schematic perspective view of an optical system used in the analyzer of Figure 1; Figure 4 is a schematic perspective view of a part of the analyzer in Figure 1 that includes a centrifuge; Figure 5 is a top schematic perspective view of a portion of the analyzer in Figure 1, including a collector; Figure 6 is a schematic bottom perspective view of the collector in Figure 5; Figure 7 is a schematic side view of a portion of the analyzer in Figure 1 that includes a target; Figure 8 is a schematic representation of a liquid system of the analyzer in Figure 1; Figure 9 is a top schematic view of a cartridge according to one realization of the disclosure; Figure 10 is a top schematic view of another cartridge according to an embodiment of the disclosure in a first example of a method according to an embodiment of the disclosure; Figure 11 is a top schematic view of the cartridge in Figure 10 in a second example of a method according to an embodiment of the disclosure; hQ^nm / Lznz / E / YiAi Figure 12 is a top schematic view of the cartridge in Figure 10 in a third example of a method according to an embodiment of the disclosure; Figure 13 is a top schematic view of the cartridge of Figure 10 in a fourth example of a method according to an embodiment of the disclosure; Figure 14 is a top schematic view of the cartridge of Figure 10 in a fifth example of a method according to an embodiment of the disclosure; Figure 15 is a top schematic view of the cartridge of Figure 10 in a sixth example of a method according to an embodiment of the disclosure; Figure 16 is a top schematic view of the cartridge of Figure 10 in a seventh example of a method according to an embodiment of the disclosure; Figure 17 is a top schematic view of the cartridge of Figure 10 in an eighth example of a method according to an embodiment of the disclosure; Figure 18 is a top schematic view of the cartridge of Figure 10 in a ninth example of a method according to an embodiment of the disclosure; Figure 19 is a top schematic view of a cartridge according to another embodiment of the disclosure; Figure 20 is a schematic side view of a portion of the analyzer in Figure 1 that includes magnetic stages; Figure 21 is a schematic side view of several stages in a washing operation using manes according to an embodiment of the disclosure; and Figure 22 is a schematic side view of several stages in another washing operation using manes according to an embodiment of the disclosure. DETAILED DESCRIPTION The following detailed description presents an overview of an illustrative embodiment of a method and system according to the invention. This overview is followed by further descriptions of several illustrative embodiments of methods, systems, and apparatus related to the invention. Overview of an example embodiment froan m / Lznz / E / YiAi Separation and measurement The present invention relates to a sample treatment and analysis system for isolating target analytes and determining their concentration. A cartridge, in the form of a single funnel-shaped disc 150, as shown in Figures 9 to 19, can be used for the entire treatment, measurement, and containment of the resulting processed sample during measurement. The treatment involves high-speed rotation of the disc to centrifuge the dense elements contained in the original sample. During the initial centrifugation stage, as shown in Figure 11, the sample 152 is transferred from a sample chamber 158 to the separation chambers 161 and 162 shown in Figure 12. The cartridge 150 is then rotated at a higher speed, for example, 7000 rpm, to separate the dense elements in the separation area 162.The resulting supernatant in the separation area 161 is then transferred to a mixing chamber 175 containing reagents composed of bonding members. The volumes of the separation chamber 161 and the mixing chamber 175, as well as the supernatant transfer method, are used to measure the amount of sample used in the treatment to maintain accuracy. The centrifugation and transfer process can be visualized by a process quality control camera and analyzed during the process to ensure correct separation and measurement. Reagents and junction members The binding members include several types, which may be in the form of dry reagents or lyophilized granules (180) shown in Figure 13, and may be stored in the mixing chamber. The first type consists of paramagnetic bead substrates functionalized with molecules that have binding sites specific to the target analyte. A second type of binding member includes fluorescent markers conjugated to molecules with binding sites specific to a separate and distinct part of the target analyte. Another component of the reagents may include a control analyte composed of a genome-manipulated protein or another molecule that would not be found in a patient sample containing the target analyte.In conjunction with the control analyte, there is another set of hQ^nm / Lznz / E / YiAi paramagnetic capture beads and markers that are specific to the binding sites of the control analyte, just as the first set of paramagnetic capture beads and markers are specific to the target analyte. The control will undergo the same process and measurement as the target analyte. However, the amount of the control analyte, unlike the target analyte, is known precisely before the process. Therefore, when the control is measured, since its concentration is known a priori, it can serve as a monitor of the effectiveness of the sample treatment and as a means of normalizing process imprecision. Mixing and incubation. Once the supernatant and reagents are in the mixing chamber, a mixing process takes place in which the disk 150 rotates slowly, but at a variable number of revolutions. Specifically, the disk accelerates and decelerates its rotation at a controlled rate to achieve a preferred motion profile during rotation. As shown in Figure 13, a mixing ball 176, denser than the sample, such as one made of brass or glass, can also be incorporated into the mixing chamber. Advantageously, the acceleration and deceleration of the cartridge induces the ball to move through the supernatant, facilitating the dissolution and distribution of the dry reagents and ensuring a homogeneous mixture of all reagents and the target analyte. The geometry of the mixing chamber can be configured along a substantially constant radius from the center of rotation.Furthermore, this chamber can incorporate various features to further facilitate mixing and incubation, ensuring the mixture remains within the mixing chamber throughout the process. The resulting mixture will produce a homogeneous suspension, facilitating the binding of the target analyte to the paramagnetic capture beads and labeled molecules. To ensure accuracy, the mixing process can be carried out for a controlled amount of time. The cartridge 150 also includes a washing chamber 181, which is coupled to the mixing chamber via a channel 173. While the supernatant can flow freely into the washing chamber through channel 173, the washing chamber can be advantageously positioned at a smaller radius from the center of rotation, so that centrifugal force retains the supernatant and reagents in the mixing chamber. Capillary enlargements in the form of flared channel widths 178 and 179, as shown in Figure 14, may be present to further prevent capillary action from drawing the supernatant and mixed suspension from the mixing chamber into the washing chamber. The capillary enlargements 178 and 179 can also serve to store the supernatant that will displace the air trapped in the freeze-dried granules during their manufacture. Once the mixing and incubation processes are complete, the cartridge 150 can be rotated to align with a manifold 108 (Figure 5) that has four channels 111, 112, 113, and 114 and associated seals that move to interact with the cartridge. The manifold can be coupled to a motor 110 for precise rotary motion and can also be attached to a suspension system to ensure contact and sealing of channels 111, 112, 113, and 114 in the cartridge. The manifold can also be mounted on a movable arm 109, as shown in Figure 1, to lower and raise it to and from the cartridge. The manifold can also incorporate features to precisely position it relative to the cartridge to ensure that the various channels align with sufficient positional accuracy.Once the collector is positioned and in contact with the cartridge, the collector motor enables precise rotary movement of the cartridge 150 around the centrifuge motor shaft. At this point, the centrifuge motor can be deactivated, and its bearings and shaft can serve as a precision rotary stage for the cartridge. The collector is connected to a series of pumps and valves to allow the introduction of buffers into the cartridge from external reservoirs using precision syringe pumps. The buffers preferably include a wash buffer, an elution buffer, and deionized water for cleaning and storage. Similarly, the pathways of this cartridge can include a wash buffer inlet pathway 154, a wash buffer outlet pathway 156, an elution buffer inlet pathway 155, and an elution buffer outlet pathway 157, as shown in Figure 9. After the collector 108 is introduced into the cartridge 150, one or more magnets move into position above the mixing chamber. The magnets are positioned above and below the cartridge on a Z-stage with an axis of movement perpendicular to the flat surface of the cartridge, as shown in Figure 20. This allows magnet 130 to move closer to the cartridge 150, increasing its effective attraction on the paramagnetic capture beads, while the other magnet 131 moves away from the cartridge 150, decreasing its effect. The magnetic Z-stage 132 is also coupled to a radial stage 133. The radial stage allows the magnets to be moved closer to or farther from the cartridge's axis of rotation. As discussed later, several channels and chambers in the cartridge are arranged radially or circumferentially.The various Z and radial stages, in combination with the collector motor, allow the hands to be placed in any desired position in relation to the chambers and channels contained in the 150 cartridge. After introducing the magnets, the magnetic and radial Z-stages are controlled, along with partial cartridge rotation, to perform a predefined sequence of movements to extract all the paramagnetic capture beads from the suspension. These beads are now binding the target analyte and the control analyte, as shown in Figure 15. The magnet 130 located at the bottom of the cartridge is brought close to the cartridge surface at a preferred location to extract the beads into a compact bolus. The bead bolus can then be visualized by a process quality control camera and analyzed to ensure that the beads have been correctly extracted from the suspension. Introduction of wash and wash tampons At this point, the wash valve connects the wash pump to the cartridge's wash inlet port 154, and the extraction pump connects to the wash extraction port 156. All other ports remain closed. The wash pump and extraction pump are controlled to empty and extract, respectively, at defined volumetric flow rates. This causes the wash buffer to fill the wash chamber and the channel leading to the mixing chamber, as shown in Figure 16. The sequence continues until the supernatant is expelled from the mixing chamber and re-enters the separation chamber. This washes away most of the unbound markers and contaminants from the bead pellet, which is held in place by the magnet.Once the wash buffer filling sequence is complete, an image of the wash chamber can be taken from a process quality control camera and processed to ensure the complete and correct filling of the wash chamber, channel, and mixing chamber with wash buffer. Magnetic transfer for washing At this point, the magnetic stages and collector motors perform a sequence of movements to draw the bolus of paramagnetic beads out of the incubation and mixing chamber and radially along the channel between the washing and mixing chambers into the washing chamber. Images can be taken and processed at various points in this process to ensure that the bead bolus is the correct size and that the entire bolus has been introduced into the washing chamber. Washing sequence Once the bead bolus has been transferred to the wash chamber, the collector motor, magnetic Z-stage, and radial stages are controlled to perform a sequence of movements to disperse the beads and re-condense the bead bolus using magnets alternately on different sides of the wash chamber along its length. This process is performed to remove any remaining unbound marker or other contaminants that may be trapped in the bead bolus. When the wash sequence is complete, the paramagnetic capture beads are reintroduced into a compact bolus. Clean wash buffer is then pumped into the wash chamber, while the contaminated buffer is expelled through the mixing chamber and into the wash waste chamber 166 located in this cartridge.The wash waste chamber 166 is sized so that the contaminated wash, the original sample, and the supernatant hQ^n Ln / Lznz / E / YiAi never completely fill the wash waste chamber and exit through the wash extraction path located at the end of the wash waste chamber. This ensures that the collector never comes into contact with any sample or any buffer that may have been mixed with the sample. Removal of air accumulation and filling of elution buffer The wash chamber 181 is connected to an elution chamber 184 at the opposite end from the mixing chamber via a connecting passage 187. The elution chamber 184 is also connected to the elution path 155 and the elution extraction path 157. When the wash chamber is full, as discussed previously, the sequence is carried out in such a way as to prevent the wash buffer from entering the channel and the elution chamber 184. This is important because the contaminated wash buffer contains unbound markers and other elements that can be sources of noise during subsequent measurements. Sufficient air space between the wash chamber 181 and the elution chamber 184 can be confirmed by analyzing images taken by the process quality control camera during each wash filling sequence.After the final magnetic wash sequence and after the wash chamber is refilled with clean wash buffer, a sequence is performed to fill the air space (if desired) in the connecting passage 187 between the wash chamber and the elution chamber 184 with wash buffer. The wash extraction line valve is closed, the elution extraction line is opened, and the extraction pump is connected to the elution extraction line 114. A pumping sequence is then performed using the wash and extraction pumps at predefined volumetric flow rates to fill the channel between the wash and elution chambers. The process can be verified by image collection and analysis. Once completed, another sequence takes place where the elution pump fills the elution chamber with elution buffer. Image processing can be performed to ensure that the channel and elution chamber are filled correctly. At this point, a pre-reading of the pure elution buffer can be performed before introducing the sample into the elution chamber, in the same way that the processed sample will be read to serve as a negative control for the assay. The elution buffer is designed to cleave the bonds between the target analyte and its associated marker, as described below. It is important to prevent this process when the sample bead bolus is outside the elution chamber. Magnetic transfer to the detection camera Once the elution chamber is filled with the elution buffer, the magnetic stages and collector motors are controlled in a predefined sequence to extract the bead bolus from the wash chamber 181 through the connecting step 187 into the elution chamber 184. Preparation for measurement Once the bead bolus is in the elution chamber, a process similar to the washing process takes place. While washing steps leave contaminants in suspension to be washed away, the elution process is designed to leave the markers that were once bound to the target analytes (and the control analyte) dissociated and in suspension. The combined motion of the upper and lower magnets, along with the precise rotating motion of the cartridge, causes the bead bolus to disperse and recondense repeatedly along the channel. The elution buffer cleaves the non-covalent bonds between the target analyte and the paramagnetic capture beads, as well as the bonds between the target analyte and its marker, resulting in a homogeneous solution of eluted markers in the elution chamber. The same cleavage occurs for the control analyte.The entire purification process briefly described herein is designed to create a suspension containing only the isolated target analyte and the markers that were once bound to that target analyte in a one-to-one ratio. The paramagnetic capture beads used to capture the target analyte are a source of noise for the readout process. After the elution sequence in which the bonds of the target analyte are cleaved, the dissociated paramagnetic capture beads can be extracted to a preferred location in the elution chamber through the magnets and away from the area where the processed sample will be read. Measurement In the measurement stage, a laser-based confocal optical system is focused within the elution chamber, for example, on a point in the chamber away from the walls and the upper and lower surfaces of the chamber. The measurement and detection of the analyte occur in elution chamber 184; therefore, chamber 184 serves as both an elution and a detection chamber, and both terms are used throughout the disclosure to refer to chamber 184. The cartridge itself may be made of ultralow autofluorescence material, and the elution buffer, pump materials, valves, liquid lines, etc., may be selected so that materials that could be autofluorescent are not shed or leached if introduced into the elution chamber.A small search space is explored through the liquid in the elution chamber by rotating the cartridge back and forth at a predefined number of revolutions via the collector motor. The search space is defined by the lateral extent of the laser spot and the lateral extent of the light cone angle formed by the laser spot. The search space is further defined along the optical axis by the size of the confocal stop, which is positioned conjugately with the field in the optical system. As those familiar with the subject will appreciate, a confocal architecture is used to eliminate light from positions far from the focal plane. The further from the focal plane and the smaller the confocal stop, the more light from distant positions is attenuated. In imaging applications, this reduction of out-of-focus light reduces noise and provides sharp image slices.Light originating from positions far from the focal plane (or image slice) does not represent the structure in the image slice and is therefore noise. The same noise reduction process can be employed in the present invention; however, in this case, the confocal system is not used for imaging. As the laser spot sweeps through the liquid, it may encounter a fluorescent marker of the target analyte. When it does, the laser excites the marker's fluorescence, and individual photons are emitted from the marker and directed by the optical system to a detector where they are counted.On the path to and beyond the focal plane, laser light may encounter self-fluorescent elements, including the glasses and bonding materials that make up the optical system, the cartridge window, the back of the elution chamber, the elution buffer, and any other material that may have entered the elution chamber. Any fluorescence from these components is noise, as it does not originate from a target analyte marker. The confocal architecture attenuates these signals, preferentially allowing the signal from target analyte markers at or near the focal plane to reach it. As a result, when the laser passes over a target marker, the photon current received and counted by the detector rises above the background photon level. Processing algorithms detect and classify this elevated photon count as a molecule of interest.In this way, individual molecules of the target analyte can be counted to determine a concentration of the target analyte in the original sample. The present invention described herein offers substantial advantages over the prior art for accurately detecting and quantifying the number of target analytes in a sample where the concentration of target analytes in the sample is low. Furthermore, the methods and apparatus of the present invention are suitable for deployment in a point-of-care environment. Other aspects of the present invention disclosed herein relate to sample treatment and analysis methods for isolating target analytes and determining their concentration. These methods implement steps that are generally consistent with prior sample treatment and measurement. Illustrative realizations Examples and systems are described herein. The words "example" and "illustrative" are used herein to mean that they serve as examples, cases, or illustrations. Any embodiment or feature described herein as an example or illustration should not necessarily be construed as preferred or advantageous over other embodiments or features. Reference is made to the accompanying figures in the detailed description below, and they form part of it. In the figures, similar symbols normally identify similar components unless the context indicates otherwise. Other embodiments may be used and other changes may be implemented without departing from the scope of the subject matter presented herein. The illustrative realizations described herein are not intended to be limiting. It will be readily understood that the aspects of this disclosure, as generally described herein and illustrated in the figures, may be arranged, substituted, combined, separated, and designed in a wide variety of different configurations, all of which are explicitly contemplated herein. Unless otherwise stated, the terms first, second, etc., are used herein merely as placeholders and are not intended to impose any ordinal, positional, or hierarchical requirements on the items to which these terms refer. Furthermore, reference to, for example, a second item does not require or preclude the existence of, for example, a first item or a lower-numbered item, and / or, for example, a third item or a higher-numbered item. References in this document to an embodiment, realization, example, or example mean that one or more features, structures, or characteristics described in relation to the example are included in at least one implementation. The expressions "an embodiment" or "an example" in various places in this document may or may not refer to the same example. As used herein, a system, apparatus, device, structure, article, element, component, or piece of equipment configured to perform a specific function is actually capable of performing the specified function without alteration, rather than merely having the potential to perform the specified function after further modification. In other words, the system, apparatus, structure, article, element, component, or piece of equipment configured to perform a specific function is specifically selected, created, implemented, used, programmed, and / or designed for the purpose of performing that specific function. As used herein, "configured to" indicates the existing characteristics of a system, apparatus, structure, article, element, component, or piece of equipment that enable the system, apparatus, structure, article, element, component, or piece of equipment to perform the specified function without further modification.For the purposes of this disclosure, a system, apparatus, structure, article, element, component, or equipment described as configured to perform a particular function may be further or alternatively described as adapted for and / or operational to perform that function. The following description provides numerous specific details to ensure a thorough understanding of the disclosed concepts, which can be implemented without some or all of these details. In other cases, details of known devices and / or processes have been omitted to avoid unnecessarily confusing the disclosure. While some concepts will be described along with specific examples, it is understood that these examples are not intended to be exhaustive. Illustrative analyzer system In one aspect, the disclosure provides an analyzer system shown in Figure 1 that includes an analyzer 100 and a cartridge 150. The cartridge 150 is configured to receive a sample and includes a plurality of chambers for isolating a target analyte from the sample and collecting an amount of a first marker that is proportional to the amount of the target analyte in the sample. The analyzer 100 includes an optical system 120, which is most clearly seen in the rear view of the analyzer 100 in Figure 2. Additionally, the components of the optical system 120 are shown separately from other parts of the analyzer in Figure 3 for clarity. As shown, the optical system 120 includes an electromagnetic radiation source 121 configured to provide electromagnetic radiation to form a query space within a detection chamber of the cartridge 150.The optical system 120 also includes a detector 122 configured to detect the hQ^n Ln / Lznz / E / YiAi electromagnetic radiation emitted in the query space by the first marker if the first marker is present in the query space. Other components of the optical system 120 are described in more detail below. The analyzer 100 also includes a controller 140, which is schematically represented in Figure 1. The controller 140 includes a computer-readable non-transient medium with program instructions stored therein to carry out the steps performed by the analyzer 100 and identifies the presence of the target analyte in the sample based on the electromagnetic radiation detected by the detector 122. The controller 140 includes a processor 141, a memory 142, and a network interface 143. The processor 141 of controller 140 includes computer processing elements, such as a central processing unit (CPU), an integrated circuit that performs processor operations, a digital signal processor (DSP), or a network processor. In some embodiments, the processor includes register memory that temporarily stores the instructions being executed and the corresponding data, as well as buffer memory that temporarily stores executed instructions. Memory 142 is computer-usable memory, such as random access memory (RAM), read-only memory (ROM), or non-volatile memory such as flash memory, solid-state drives, or hard disk drives.In some embodiments, memory 142 stores program instructions that can be executed by controller 140 to perform disclosure methods and operations. Network interface 143 provides digital communication between controller 140 and other computing systems or devices. In some embodiments, the network interface operates via a physical wired connection, such as an Ethernet connection. In other embodiments, the network interface communicates via a wireless connection, for example, IEEE 802.11 (Wi-Fi) or Bluetooth. Other communication conventions are also possible. hQ^n Ln / Lznz / E / YiAi In some embodiments, the analyzer 100 includes at least one motor configured to rotate the cartridge in order to manipulate any sample placed in the cartridge and to align the cartridge with parts of the analyzer. In some embodiments, the motor is a centrifugal drive motor, and in other embodiments, the motor is a positioning motor. Additionally, in some embodiments, the analyzer includes both a centrifuge and a positioning motor. For example, the analyzer 100, shown in Figure 1, includes both a centrifuge 101 and a positioning motor 110. In the analyzer 100, the centrifuge 101 is coupled to the cartridge 150 to rotate the cartridge at a speed of at least 100 rpm. Details of the centrifuge 101 are shown more clearly in Figure 4. As illustrated, a centrifuge drive motor 103 is configured to couple to the cartridge using a coupling 102. The coupling 102 may include a retaining mechanism, such as a plurality of registration pins 105 and cantilever clips 104 that engage with the mounting openings 153 of the cartridge 150 (shown in Figure 9). In some embodiments, the cantilever clips 104 are at the end of leaf springs that clamp onto the cartridge when the coupling 102 receives the cartridge 150. The cantilever clips 104 may be configured to couple to the cartridge 150 in an outward direction.As the centrifuge 101 rotates, the cantilever clips 104 are pushed outwards by the centrifugal force, increasing the clamping force on the cartridge 150. Consequently, the cartridge 150 can be securely clamped into the coupling 102 when inserted into the analyzer 100. The coupling 102 is connected to the centrifuge drive motor 103 to rotate the coupling 102 and the cartridge 150 attached to it. Additionally, the centrifuge drive motor 103 may include electronically driven phase sensors 106 and a flag wheel 107 for high-speed precision control of the centrifuge 101 during operation. In some embodiments, the coupling 102 is driven directly by the centrifuge drive motor 103, while in other embodiments, a power transfer system, such as a gearbox or belt drive, may be used to couple the coupling 102 to the centrifuge drive motor 103. As explained below, the coupling 102 may also be driven by a collector 108 (see Figure 1).The specific realizations of the operations of centrifuge 101 are described in more detail below. In some embodiments, the analyzer includes a collector 108 with a plurality of pathways that are each configured to couple to a respective pathway of the cartridge. Figure 5 shows a representation of the manifold 108 coupled to the cartridge 150. Additionally, a bottom view of the manifold 108 is shown in Figure 6 to illustrate the ports 111 to 114. In some embodiments, the manifold includes delivery ports 111 and 112 for administering fluid to the cartridge 150 and withdrawal ports 113 and 114 for withdrawing fluid from the cartridge 150. In some embodiments, delivery ports 111 and 112 are used to supply one or more fluids to the cartridge 150, while withdrawal ports 113 and 114 withdraw fluid from the cartridge 150 by extracting gas from the cartridge 150. In other embodiments, the withdrawal ports withdraw fluid, or both fluid and gas, from the cartridge 150.To transfer liquids to and from the cartridge, the manifold 108 includes liquid lines 115 that are connected to lines 111 to 114. Each of the manifold 108's ports may include a seal that covers the corresponding port of cartridge 150 to isolate fluid transfer between manifold 108 and cartridge 150. For example, each of ports 111 to 114 may include an O-ring or other feature to create a seal between the manifold and the cartridge ports surrounding the respective port of cartridge 150. In some embodiments, the ports of cartridge 150 are already open when cartridge 150 is placed in the analyzer. In other embodiments, the manifold is configured to pierce cartridge 150, thereby opening each of its ports. hQ^n Ln / Lznz / E / YiAi In some embodiments, the collector 108 is mounted on a movable arm 109 (shown in Figure 1), which allows the collector 108 to detach from the cartridge 150 when the cartridge 150 is rotated at high speeds by the centrifuge 101. The collector 108 can be coupled to the cartridge 150 by means of an alignment structure. For example, the collector 108 may include pins that are received in the mounting openings 153 of the cartridge (see Figure 9). In other embodiments, the pins 104 of the coupling 102 can pass through the mounting openings 153 of the cartridge 150 into receiving holes in the collector 108. Such a structure provides a secure connection between the collector 108, the cartridge 150, and the coupling 102. Other mounting structures are also possible, as those skilled in the art will appreciate. In some embodiments, the analyzer 100 includes a positioning motor 110 coupled to the cartridge 150. In some embodiments, the positioning motor 110 can be coupled to the collector 108, which is coupled to the cartridge 150. The positioning motor 110 can be configured to pivot the cartridge 150 so as to align the detection chamber 184 (see Figure 9) of the cartridge 150 with the electromagnetic radiation from the first electromagnetic radiation source 121. Furthermore, the positioning motor 110, in conjunction with one or more magnets or by means of the sample fluid dynamics, can also be used to circulate the target analytes through the chambers of the cartridge 150, as described in more detail below. The positioning motor 110 can be a step-up motor or another actuator with dedicated positioning control.For example, in some embodiments, the location of the positioning motor 110 can be specified within 2° of rotation, or within 1° of rotation, or in smaller increments of 1°. Specific examples of embodiments of the use of the positioning motor 110 are described in more detail below. In some embodiments, the positioning motor 110 is directly coupled to the manifold 108, while in other embodiments, a power transfer system, such as a gearbox or belt drive, may be arranged between the positioning motor 110 and the manifold 108. In the hQ^n Ln / Lznz / E / YiAi analyzer 100 shown in Figure 1, the positioning motor 110 is coupled to the cartridge 150 via the manifold 108. In particular, the manifold 108 is arranged on the shaft of the positioning motor 110. Consequently, the manifold 108 and the cartridge 150 can move synchronously while maintaining a closed fluid connection between them. In some embodiments, the analyzer 100 includes an optical system 120 (Figures 2 to 3) that directs electromagnetic radiation from the first electromagnetic radiation source 121 to the detection chamber 184 of the cartridge 150, and that directs the electromagnetic radiation emitted by the marker to the first detector 122. The optical system 120 may include one or more mirrors and lenses for manipulating and directing the electromagnetic radiation to and from the examination space. Furthermore, the optical system may include a lens 123, as shown in Figure 7, for focusing the electromagnetic radiation from the first electromagnetic radiation source onto the examination space in the cartridge 150. In some embodiments, the lens 123 is coupled to a movable stage 124, which allows movement of the lens relative to the cartridge 150. In some embodiments, the optical system 120 is a confocal system. For example, the electromagnetic radiation source 121 is represented as a point in the focal plane of the objective lens 123 within the detection chamber 184. Light emitted from a marker in the detection chamber 184, excited by the electromagnetic radiation source 121, is collected by the objective lens 123 and directed by the optical system 120 onto a confocal stop 125 within the optical system 120, as shown in Figure 3. The confocal stop 125 then projects onto the detector 122. The confocal arrangement preferentially passes light from the marker into the focal plane of the objective lens 123 while excluding light from beyond the focal plane. In this way, the arrangement increases the signal-to-noise ratio by passing the marker signal while excluding light from elements of the liquid suspension, the cartridge, and the optical system that do not originate from the marker.As experts in the field know, this arrangement can also utilize dichroic filters 126 to reflect the laser light and allow the light emitted by the marker to pass through, permitting only the marker light to reach the detector while preventing the laser light from reaching it. Additionally, if more than one radiation source is used for the detection of additional markers, one or more additional dichroic filters 126 can be used to reflect the electromagnetic radiation from the laser and the marker from the first electromagnetic radiation source and the marker, while allowing electromagnetic radiation from a second electromagnetic radiation source and a second marker to pass through, as shown in Figures 2 and 3. In some embodiments, all components of the Analyzer 100 are arranged in a common housing. The common housing may be small enough to fit on a countertop. For example, in some embodiments, the dimensions of the common housing do not exceed 1 meter in any direction. Additionally, in some embodiments, the common housing fits inside a cube measuring 76.2 cm x 76.2 cm x 76.2 cm (30 in x 30 in x 30 in). In some embodiments, the controller 140 includes a network interface 143 for receiving control information from a user and for sending analysis data to the user. For example, in some embodiments, the analyzer communicates with a user through software on an external device, such as a smartphone, tablet, laptop, or desktop computer. The analyzer receives information from and sends information to the user from the external device by communicating with the external device through the network interface. This communication can be wireless or wired, such as via USB or another channel. In some embodiments, the analyzer 100 may include input and / or output devices for communicating directly with a user, such as a keyboard for receiving input and a display for sending information.In addition, some embodiments include a touchscreen for both sending and receiving information from a user. Some embodiments also include a network interface, an input, and a display. In some embodiments, the disclosure method includes directing portions of the sample through the chambers of cartridge 150 without cartridge 150 containing any valves. Additionally, in some embodiments, cartridge 150 has no valves. In some embodiments, the liquids within cartridge 150 are, at least in part, moved through the cartridge using pumps 116 to 118 and valves coupled to the cartridge's administration and extraction lines, as described in more detail below. Figure 8 shows a schematic view of the liquid transfer components of the analyzer 100. Manipulation of sample portions within cartridge 150 can also be facilitated by using external driving forces, such as handles, or by moving cartridge 150 and using inertia and fluid dynamics to move sample portions around the cartridge. As shown in Figure 8, in some embodiments, cartridge 150 includes a plurality of ports 154 to 157 for introducing and removing liquid from cartridge 150. For example, in some embodiments, cartridge 150 includes inlet ports 154 and 155 and outlet ports 156 and 157. Inlet ports 154 and 155 can be configured to align with administration ports 111 and 112 of manifold 108. Similarly, outlet ports 156 and 157 of cartridge 150 can be configured to align with extraction ports 113 and 114 of manifold 108. The use of the inlet and outlet ports of cartridge 150 is described in more detail below. In another aspect, the disclosure provides a plurality of chambers to isolate a target analyte from the sample and collect an amount of a first marker that is proportional to the concentration of the target analyte in the sample. In some embodiments, the 150 cartridge is flat, and the cartridge chambers lie in a single plane. For example, in some embodiments, the 150 cartridge is a flat cartridge, and the cartridge chambers are arranged circumferentially around the cartridge. The term "circumferentially," as used herein, refers to the angular or circumferential direction, as opposed to a radial or axial direction. Unless otherwise stated, the term "circumferentially" is not intended to mean that it extends around the entire circumference of the cartridge, but rather to indicate the circumferential direction in the plane of rotation. In some embodiments, at least one group of chambers may be sequentially connected circumferentially around a portion of the cartridge. In some embodiments, the cartridge may include a base, a body disposed on the base, and a cover disposed on the body, where the body includes an open pathway extending through it and defining the plurality of chambers of the cartridge. In some embodiments, the body may be a single, integral piece. Thus, for example, in some embodiments, the side walls of all the chambers and interconnecting channels of the cartridge may be formed from a single, integral piece that constitutes the body. Furthermore, in some embodiments, the body and base together form a single, integral piece, and the cover is attached to it. Similarly, in other embodiments, the body and cover form a single, integral piece, and the base is attached to it.For example, in the present embodiment, the body and base can be a single molded piece of 5 mm thick cyclic polymer, and the cover can be a laminate of 188 micrometers thick cyclic polymer. The laminate can be joined to the body by laser welding or ultrasonic welding to provide a bond as strong as the materials being joined together. In some embodiments, the base, body, and cover can be layers of a laminated structure. For example, in some embodiments, the base and cover are laminated onto opposite sides of the body. In some embodiments, the cover and base of the 150 cartridge extend and enclose the cartridge's microliquid chambers and channels, although they may include pathways, as described above, for administering or withdrawing liquids from the cartridge. In some embodiments, the cartridge is configured to receive a sample in the range of 50 microliters to 1 milliliter. For example, in some embodiments, the cartridge is configured to receive a sample in the range of 100 to 300 microliters. In particular, the cartridge may include a metered chamber for receiving the sample. hQ^nm / Lznz / B / YiAi In some embodiments, the cartridge includes reagents stored within at least one of the plurality of chambers. For example, in some embodiments, the cartridge includes reagents that are stable and dry before insertion into the analyzer. For example, the reagents may be lyophilized or dried on the surface of one or more chambers of the cartridge. Or they may be in the form of lyophilized granules placed in one or more of the chambers or the cartridge. While the cartridge is shown and described herein as a disc rotating inside the analyzer, in other embodiments the cartridge is not a disc. Furthermore, some aspects of disclosure are carried out without the use of a cartridge at all. For example, in some embodiments, aspects of disclosure are carried out in separate, individual elements that form the different chambers. Process quality control camera In some embodiments, the analyzer 100 includes a process quality control camera to monitor the movement of substances through the cartridge 150. For example, the process quality control camera can be mounted on the cartridge 150 to provide a view of the substances inside. In some embodiments, the process quality control camera is configured to generate a representation of only the light detected in the visible wavelength spectrum; that is, the camera is not enabled to detect infrared or ultraviolet light. In some embodiments, the controller 140 is configured to analyze images from the process quality control camera to confirm that the sample treatment is being carried out as expected or to detect any unexpected circumstances. For example, the controller 140 can be configured to detect the presence of an unwanted air bubble in the cartridge.The following describes other illustrative realizations of the use of the process quality control camera. In some embodiments, the analyzer includes a strobe light positioned to illuminate the field of view of the process quality control camera. For example, the strobe light can be configured to activate at a frequency corresponding to the rotational speed of cartridge 150, in order to monitor a specific region of cartridge 150 as it rotates. In particular, in some embodiments, the strobe light can be used while centrifuge 101 is rotating cartridge 150. Optical quality control camera In some embodiments, the analyzer 100 includes an optical quality control camera to monitor the performance of the optical system 120. For example, the optical quality control camera may use a mirror on a slide to intercept the optical path before or after the confocal stop to obtain an image of the laser at the confocal stop. This allows visualization that the electromagnetic radiation has the correct intensity, is focused at the correct location, and has the correct intensity profile. To obtain the image of the laser at the confocal stop, the target can be positioned so that the electromagnetic radiation source is reflected off the surface of a window in the cartridge 150. When this is done, some of the radiation will be reflected off the window toward the target due to the difference in the refractive index of the window and the medium on the other side of the window.This radiation will be captured by the optical system at the confocal spot. The cartridge window can be sized to the correct thickness to simulate the thickness of the detection chamber window and the height of the liquid layer between the window and the focused spot of electromagnetic radiation. The image of the electromagnetic radiation at the confocal spot can be analyzed by controller 140. Controller 140 can be used to analyze the optical quality control chamber images to verify that the electromagnetic spot is of the correct size, shape, intensity, and position relative to the confocal spot, ensuring there are no anomalies in the optical system. The measured size, shape, intensity, and position can be compared with known and accepted values ​​for these parameters.If the measured values ​​are outside the accepted values ​​or approaching the limits of the accepted values, the controller can notify the analyzer user or prevent the use of the analyzer. Example method honn Ln / Lznz / E / YiAi Figures 10 to 18 illustrate a sample cartridge and a method using various embodiments of the disclosure where the sample is blood. In other embodiments, the cartridge chambers and methods used may be suitable for other sample types. For example, the analyzers, methods, and cartridges of the disclosure may be suitable for use with other biological fluids, such as urine, dilute stool, or oral fluid. Other sample types are also possible. Additionally, samples may be undiluted or diluted. Sample Loading and Separation As shown in Figure 10, cartridge 150 is initially loaded with sample 152 into an inlet chamber 158. The inlet chamber 158 includes an inlet port 151 that receives sample 152 prior to analysis. In some embodiments, the cartridge 150 receives sample 152 before its insertion into the analyzer 100, for example, by a medical professional or a robot using a syringe. In other embodiments, sample 152 is loaded into the inlet chamber 158 after the analyzer 100 receives cartridge 150. As mentioned above, in some embodiments, the inlet port 151 can be sealed prior to the insertion of sample 152, and the seal can be punctured or removed to allow insertion of sample 152. In other embodiments, the inlet port 151 can be a simple opening that is available to receive sample 152 without being opened.In some embodiments, the inlet port 151 can be sealed after the sample has been introduced. In other embodiments, the manifold 108 contains a seal to cover the port when the manifold is in contact with the cartridge. In some embodiments, the inlet chamber 158 is a metered chamber configured to receive a specific amount of sample, while in other embodiments, the inlet chamber 158 is oversized and can accommodate more sample than is used in the analysis. The inlet chamber 158 in the illustrated example in Figures 9 to 18 is configured to receive approximately 200 µL of liquid. Once sample 152 is loaded into the inlet chamber 158, as shown in Figure 10, and cartridge 150 is inserted into analyzer 100, the cartridge hQ^n Ln / Lznz / E / YiAi Cartridge 150 is coupled to centrifuge 101 so that centrifuge 101 can rotate cartridge 150. As explained in more detail below, the geometry of the chambers and channels within cartridge 150 is designed to influence the transfer of liquid through the cartridge. To facilitate understanding of these geometries, the following description refers to cylindrical and polar directions. In particular, the use of the terms interior, inward, exterior, outward, and similar descriptions refers to a radially inward and radially outward direction with respect to the center of rotation of the cartridge, which is typically located near the geometric center of the cartridge.The description also refers to a first circumferential direction and a second circumferential direction, which relate to the direction in which the cartridge is configured to be rotated by the centrifuge, where the cartridge is configured to rotate in the first circumferential direction. For example, an area at a first circumferential end of a chamber will pass through a stationary reference position before an area at the second circumferential end of the same chamber. In the embodiment shown in Figures 9 to 18, the first circumferential direction is clockwise; however, other embodiments of the cartridge can be configured to rotate in opposite directions, so that in those embodiments the first circumferential direction is counterclockwise. With cartridge 150 loaded into analyzer 100, centrifuge 101 is activated to rotate cartridge 150 in order to move sample 152 from inlet chamber 158 through inlet channel 159 to separation area 160, as shown in Figure 11. The rotation of cartridge 150 causes sample 152 to move radially outward as a result of centrifugal force, i.e., the industrial phenomenon that causes objects to move outward when they rotate. If the sample volume is greater than the amount required for analysis, any excess can flow out of separation area 160 through overflow channel 165. In some embodiments, inlet chamber 158 may be offset from the center of cartridge 150 to facilitate sample transfer to separation area 160.In other embodiments, the inlet chamber 158 is located in the center of the cartridge 150 so that the rotation of the disc-shaped cartridge 150, once loaded with the sample, will keep the sample and any other liquid received in the cartridge 150 away from the inlet path 151. Additionally, in some embodiments, the inlet path 151 may be centered within the cartridge 150. In some embodiments, to move the sample from the inlet chamber 158 to the separation area 160, the cartridge may, for example, rotate from 0 rpm to 1000 rpm at a speed of 2000 rpm / s and maintain that speed for a few seconds, for example, from 2 to 10 seconds. Therefore, the sample transfer can occur very rapidly. The rotation speeds and accelerations provided are illustrative and the actual speeds chosen will depend on the sample being processed and may vary in rotation from 100 to 10.000 rpm with accelerations that vary between 100 rpm / s and 8000 rpm / s. In some embodiments, the separation area may include an inner separation chamber 161 and an outer separation chamber 162 configured to contain the different constituents of the sample after they are separated. In some embodiments, the center of the inner separation chamber may be located 19 mm from the center of rotation, and the center of the outer separation chamber may be located 28 mm from the center of rotation. As the centrifuge rotates the cartridge 150, the denser constituents of the sample are pushed radially outward into the outer separation chamber 162, while the less dense components move radially into the inner separation chamber 161. In some embodiments, the inner and outer separation chambers 161 and 162 of the separation area 160 are separated by a narrow neck 163 located, for example, 22 mm from the center of rotation.The narrow neck 163 has a smaller cross-sectional area than either of the chambers. For example, in some embodiments, the narrow neck 163 may have a cross-sectional area of ​​3 mm², while the inner separation area 162 has an average cross-sectional area of ​​12 mm² and the outer separation area 162 has an average cross-sectional area of ​​30 mm². In this illustrative embodiment, the neck 163 is sized to readily allow denser components to move downwards while less dense components move upwards rapidly through the neck 163. However, as explained below, the narrow neck 163 restricts the movement of denser components to the inner separation area 161 when the cartridge is rapidly decelerated. To generate an accurate sample concentration value for further processing, the exact sample volume must be known. If the sample cannot fill the separation area 160 and is unintentionally wasted, or if the separation area is sized to accept more than the sample volume, obtaining accurate concentration values ​​can be difficult. Therefore, in some embodiments, the cartridge 150 may include various features for measuring a precise amount of liquid in the separation area 160. For example, some embodiments of the 150 cartridge may include one or more features to prevent air from becoming trapped in the cartridge, particularly during sample transfer from the inlet chamber 158 to subsequent chambers. If air becomes trapped in the separation area 160 while the sample is being loaded, some of the sample may prematurely flow through the overflow channel 165, and accurate sample measurement in the separation area 160 may fail. Therefore, it is advantageous to prevent air from becoming trapped in the cartridge during loading. In some embodiments, the inlet channel 159 is coupled to a first circumferential end of the inner separation chamber 161. As the sample moves outward from the inlet chamber 158 through the inlet channel 159 and into the separation area 160, the rotation and / or acceleration of the cartridge 150 in the first circumferential direction by the centrifuge 101 may cause the sample to flow in the second circumferential direction. Consequently, if the inlet channel 159 is coupled to the center of the inner separation chamber 161, additional precautions may be necessary to prevent the formation of trapped air in a corner at the first circumferential end toward the inner side of the inner separation chamber 161.However, if the inlet channel 159 is coupled to the first circumferential end of the inner separation chamber 161, as shown in cartridge 150 in Figures 9 to 18, the inclusion of an inner corner that is further in the first circumferential direction than the opening of the inlet channel 159 is avoided. Similarly, air that might become trapped in that corner is also avoided. Additionally, in some embodiments, the inlet channel 159 can be reduced in size and depth compared to the separation area 160. This reduction can slow the flow of the sample into the separation area 160, allowing air to be purged from the separation area 160 during filling. Furthermore, the reduced size and depth can also help prevent the formation of a liquid sheet along a cross-section of the separation area 160, which could also lead to trapped air. For example, in one embodiment, the depth of the inlet channel 159 can be 0.5 mm, while the depth of the inner separation chamber 161 is 2 mm.Therefore, the sample stream flowing into the inner separation chamber 161 from the inlet channel 159 will not span the entire depth of the inner separation chamber 161, allowing air to flow around the stream and out of the separation area 160. Additionally, in some embodiments, the cross-sectional area of ​​the inlet channel 159 may be narrower than the cross-sectional area of ​​the narrow neck 163 between the inner separation chamber 161 and the outer separation chamber 162. For example, the inlet channel 159 may have a cross-sectional area of ​​0.5 mm² while the narrow neck 163 has a cross-sectional area of ​​3 mm². Consequently, the volumetric flow rate of the sample in the separation area 160 is unlikely to exceed the narrow neck 163 and trap air in the outer separation chamber. To prevent air from becoming trapped in the outer separation chamber 162, in some embodiments, the inner edge 164 of the outer separation chamber 162 extends at an angle that projects inwards when the inner edge hQ^n Ln / Lznz / E / YiAi 164 approaches the narrow neck 163 that separates the inner separation chamber 161 from the outer separation chamber 162. Consequently, as the outer separation chamber 162 fills with the sample due to the rotation of the cartridge, the air in the outer separation chamber 162 will float inwards to the inner edge 164 and then follow the inner edge 164 to the narrow neck 163. The air will then pass through the narrow neck 163, through the inner separation chamber 161, and out of the separation area 160. In some embodiments, controller 140 is configured to take an image of the separation area 160, or a portion thereof, using the process quality control camera after the separation area 160 is filled. The controller can be further configured to analyze the image to confirm that the volume of any air bubbles within the separation area 160 is free of air bubbles or that the air volume in the separation area is below a predetermined threshold. For example, the controller can be configured to calculate the shape of any air bubbles within the separation area 160 and calculate the total air volume within the separation area 160. If the calculated air volume is above a predetermined threshold, the controller can be configured to interrupt the analysis.Similarly, the controller can be configured to continue the analysis if the calculated air volume is below a predetermined threshold or is zero. In some embodiments, the separation area 160 and surrounding channels may include one or more features for precise sample measurement and controlled separation of sample components. For example, in some embodiments, the overflow channel 165 may be positioned to allow precise measurement of the sample quantity 152 in the separation area 160. If the quantity of sample 152 received in the cartridge 150 is greater than that required for analysis, the excess will be discharged through the overflow channel 165. In some embodiments, the overflow channel 165 leads to a waste chamber 166 where the excess liquid can be stored. hQ^nm / Lznz / E / YiAi Due to the rotation of the cartridge 150 and the centrifugal force on the sample, the separation area 160 fills from the outer end to the inner end. Consequently, placing the opening of the overflow channel 165 at a particular radial position in the inner separation chamber 161 dictates the amount of sample that can be loaded into the separation area 160. For example, as the centrifuge 101 rotates the cartridge 150, the sample will move toward the outer end of the outer separation chamber 162 and produce a fill line that moves inward as the separation area 160 fills. Once the fill line reaches the radial position of the overflow channel 165, for example, at a radial distance of 17 mm, any additional volume of sample entering the separation area 160 will exit through the overflow channel 165.Therefore, the amount of sample to be analyzed can be accurately measured based on the radial position of the overflow channel 165. Separation of the constituents of the sample As shown in Figure 12, after the sample has been loaded into the separation area 160, the centrifuge 101 can continue to rotate the cartridge 150 to separate the sample 152 into different constituents. For example, the centrifuge 101 can rotate the cartridge 150 to send denser constituents of the sample outwards, leaving the less dense constituents radially inwards. In some embodiments, the speed of the centrifuge 101 can be increased to further separate the constituents of the sample 152. For example, in one embodiment, after loading the sample, the centrifuge 101 can accelerate the cartridge 150 from a speed of 1000 rpm to an acceleration of 2000 rpm / s. Upon reaching 1000 rpm, centrifuge 101 can further accelerate cartridge 150 to 5000 rpm / s at a speed of 7000 rpm and maintain that speed for 90 seconds to separate the constituents.In another embodiment, the centrifuge 101 can omit the initial transfer rotation speed and proceed directly from 0 rpm to a separation speed of 10,000 rpm at an acceleration of 2,000 rpm / s. The separation stage can be carried out at rotation speeds hQ^n Ln / Lznz / E / YiAi from 1,000 rpm to 20,000 rpm depending on the sample being analyzed, the radius of the separation chamber from the center of rotation, and the strength of the cartridge 150 to resist fracture. The separation time can be carried out within a range of 10 seconds to 5 minutes. In some embodiments, the sample 152 may be whole blood, and continuous rotation of the cartridge 150 may separate the red blood cells from the plasma, as depicted in Figure 12. For example, in the separation area 160 of the illustrated embodiment, the inner separation chamber 161 may function as a plasma compartment, and the outer separation chamber 162 may function as a red blood cell trap. In response to the high-speed rotation of the cartridge 150, the denser red blood cells are pushed radially outward, while the less dense blood plasma moves radially inward into the plasma compartment 161. The angled inner rim 164 of the outer separation chamber 162 can help separate the sample constituents in a manner similar to how air removal from the outer separation chamber 162 was promoted, as described above. As the centrifuge 101 rotates the cartridge 150, the denser constituents will move outward and the less dense constituents will move inward. Consequently, similar to the airflow path in the outer separation chamber 162 during the filling process, the lighter components of the sample will move inward and then follow the angled inner rim 164 of the outer separation chamber 162 until they reach the narrow neck 163 and pass through the inner separation chamber 161. In some embodiments, controller 140 can be configured to take an image of the separation area or a portion thereof using the process quality control camera after the separation process. Controller 140 can further be configured to analyze the image to determine the filling level of the denser constituents of the sample in the separation area 160. In some embodiments, controller 140 is configured to confirm that certain denser constituents of the sample have moved out from a predetermined filling level. The controller can also be configured to continue the analysis in response to this confirmation. For example, when the sample is whole blood, controller 140 can be configured to analyze the image and determine the red blood cell fill level in the separation area. If the red blood cell fill level is outside a predetermined radius, controller 140 can be configured to continue the analysis. Conversely, if the red blood cell fill level is within the predetermined radius, controller 140 can be configured to send a control signal to centrifuge 101 to continue rotating the cartridge to further separate the blood sample components. For example, an image can be taken and analyzed at a separation time of 90 seconds.If the red blood cell level is within a threshold distance of, for example, 22 mm from the center of rotation, the 140 controller can be configured to send a control signal to rotate for an additional 30 seconds before taking an additional image and reassessing the red blood cell level. In some embodiments, the duration or speed of this additional control signal can be based on the identified red blood cell fill level. Alternatively, the 140 controller can be configured to interrupt the analysis. In some embodiments, the method is configured to transfer a portion of the sample that excludes red blood cells. Including red blood cells will add hemoglobin to the plasma, which can affect the analysis. Therefore, identifying the red blood cell fill level allows the quality of the blood plasma being transferred for further analysis to be determined. Similarly, in some embodiments, the image of the separation area 160 after the separation process can be analyzed by the controller to determine the clarity of the blood plasma in the inner separation chamber. Additionally, the controller 140 can be configured to continue the analysis upon confirmation that the blood plasma has reached a clarity threshold. hQ^n Ln / Lznz / E / YiAi Furthermore, in some embodiments, the 140 controller can be configured to analyze the image of the separated blood sample to determine the blood's hematocrit level based on the radial distance of the red blood cell line and the rotation time. Those skilled in the field will readily appreciate that, for a given camera geometry, rotation speed, and rotation time, blood with a lower hematocrit level will exhibit a separation line with a larger radius than blood with a higher hematocrit level. For a given cartridge geometry and rotation parameters, different hematocrit levels can be performed and evaluated to generate a calibration table that is stored in the 140 controller.When a sample of unknown hematocrit is passed to the separation line, after a predefined centrifugation time, it can be compared with the values ​​stored in the controller to determine the hematocrit level of the sample being analyzed. Additionally, the 140 controller can be configured to continue the analysis upon confirmation that the hematocrit level is below a predetermined threshold. Supernatant transfer As shown in Figure 13, a portion of the sample 152 can be removed from the separation area 160 through a siphon 167 extending from the separation area 160. The siphon 167 can be in the form of a microliquid channel with a cross-sectional area of ​​1 mm² leading to a second chamber, such as the mixing chamber 175. The siphon 167 can include a first section 168 extending from the separation area 160, a peak 169, and a second section 170 extending from the peak 169 to the mixing chamber 175. The first section 168 of the siphon 167 extends from a siphon inlet 171 away from the inner separation chamber 161 toward the peak 169 in a direction having an inward radial component. Additionally, the second section 170 extends from peak 169 to an outlet point 172 of the siphon that is more radially outward than the inlet 171 of the siphon.For example, the siphon inlet 171 might be at a radial position of hQ^n Ln / Lznz / E / YiAi mm from the center of rotation, while the siphon peak might be 16 mm from the center of rotation and the siphon outlet 172 might be at a radial distance of 30 mm from the center of rotation. Other radial distances can be chosen to suit the application requirements, provided that the siphon outlet 172 is at a greater radial distance than the siphon inlet 171 and the peak 169 is at a smaller radial distance than both the siphon inlet 171 and the siphon outlet 172. Therefore, the peak 169 is the innermost radial point of the siphon 167, and the siphon outlet 172 is radially outward compared to the siphon inlet 171.Therefore, because the rotation of the centrifuge generally drives the sample radially outwards, once a portion of the sample passes over peak 169, the siphon 167 will drive a portion of the sample from the inner separation chamber 161 to the mixing chamber 175. In some embodiments, the siphon can be primed, i.e., a portion of the sample can be forced past the peak to initiate siphoning action via capillary action. In other words, capillary force can draw the sample into the first section 168 of the siphon 167 and over the peak 169 until the siphoning action draws more liquid from the inner separation chamber 161. The cross-sectional area of ​​the siphon 167 can be smaller, for example, from about 0.1 mm² to about 0.3 mm² or about 0.2 mm², to facilitate capillary action. In other embodiments, the siphon 167 can be primed by using pumps that draw the sample into the siphon 167 until the sample passes the peak. Additionally, in some embodiments, the siphon can be primed by acceleration. For example, in one embodiment, after cartridge 150 completes the separation stage at 7000 rpm, it is slowed down by centrifuge 101 at 3000 rpm to 2000 rpm / s to prepare for the siphon stage. As cartridge 150 rotates in the first circumferential direction, inertia will cause the sample to continue moving in that direction. Therefore, if the cartridge 150 is slowed down rapidly from 3000 rpm to 0 rpm, for example, to 8000 rpm / s, inertia will cause the sample 152 to continue moving in the first hQ^n Ln / Lznz / E / YiAi circumferential direction and the sample will flow through the first section 168 of the siphon 167 due to its extension along the first circumferential direction and through the peak 169 which is radially outward from the filling level of the separation area 160.At this point, the centrifuge 101 can reverse its direction of rotation to -1000 rpm at an acceleration of 2000 rpm / s and maintain that speed. The centrifugal force will cause the liquid in channel 170 to move radially outward toward the siphon outlet 172, which is radially outward from the siphon inlet 171. The separation area 160 will continue to drain until the fill level is radially outward from (or below) the connection where the first section 168 of the siphon 167 opens into the inner separation chamber 161. This priming and siphoning method is significantly faster than capillary action and / or pump-based priming and siphoning, as the entire process can be completed in a few seconds. In some embodiments, peak 169 is radially into the overflow channel 165, preventing the sample from flowing through the siphon 167 while the separation area 160 is being filled.Other rotation speeds and accelerations may be used as long as the acceleration is sufficient to force the liquid over the siphon's peak 169 and the cartridge 150 continues to rotate, drawing liquid out of the separation area 160. As previously stated, the first section 168 of the siphon 167 extends in the first circumferential direction and radially inward. Additionally, in some embodiments, the shape of the first section 168 of the siphon 167 is specifically designed to facilitate priming of the siphon 167. For example, in some embodiments, a portion of the first section 168 at the end connected to the inner separation chamber 161 is substantially parallel to the first circumferential direction, for example, within 10 degrees of parallel. As the first section 168 extends toward the spout 169, it gradually curves inward. As previously stated, after the cartridge 150 is braked, the sample is pushed in the first circumferential direction.Therefore, with the first part of the first section 168 substantially hQ^n Ln / Lznz / E / YiAi aligned with the first circumferential direction, the sample flows into siphon 167 with great momentum. As a result of this momentum, the sample is able to reach and flow past peak 169, thereby priming siphon 167. In some embodiments, the position of the connection between the first section 168 of the siphon 167 and the inner separation chamber 161 is selected to transfer a measured quantity of sample through the siphon 167. For example, in the embodiment depicted in Figure 13, the siphon 167 will transfer an exact quantity of the sample, e.g., 50 microliters, based on the distance between the opening of the overflow channel 165 and the opening of the first section 168 of the siphon 167 in the radial direction. As the sample is transferred through the siphon 167, the fill level in the inner separation chamber 161 will decrease (i.e., move radially outwards) and be replaced by air from the inlet channel 159 or the overflow channel 165. Once the interface between the sample and the air reaches the first section 168 of the siphon 167, no further amount of the sample will be drawn from the inner separation chamber 161.Therefore, the position where the first section 168 opens into the inner separation chamber 161 can be used to define a measured quantity of the sample being transferred to the subsequent chambers. The position of the opening of the first section 168 of siphon 167 in the inner separation chamber 161 can also be selected to limit the transfer through siphon 167 to only certain constituents of the sample. For example, in the embodiment where the sample is whole blood and separation chambers 162 and 161 are used to separate red blood cells from plasma, the opening of the first section 168 can be positioned radially inward from the separated red blood cells. Inadvertent inclusion of red blood cells in the sample being transferred to the mixing chamber can result in hemoglobin contamination during the mixing process. Therefore, it is advantageous to position the opening of the first section 168 to prevent the inclusion of red blood cells in the sample being transferred through siphon 167.Therefore, when the outer separation chamber 162 is a red blood cell trap configured to receive the red blood cells after the separation process, the opening of the first section 168 can be positioned radially inward from the red blood cell trap and into the plasma container. Similarly, the volume of the outer separation chamber 162 can be selected based on normal red blood cell volumes, for example, a hematocrit level of 52%, to ensure that the red blood cell trap volume can accommodate the volume of red blood cells present in most whole blood samples. In some embodiments, the outer separation chamber 162 extends away from the narrow neck 163 in the first circumferential direction. Consequently, as the cartridge 150 slows down and the less dense components of the sample are pushed through the siphon 167, the denser constituents are similarly pushed toward the closed end of the outer separation chamber 162 and away from the narrow neck 163 and the inlet of the siphon 171. For example, in embodiments using whole blood, as the blood plasma above the narrow neck 163 is transferred through the siphon 167, the red blood cells are pushed toward the closed end of the red blood cell trap formed by the outer separation chamber 162. As indicated, a large braking force can be used to prime the siphon. As the cartridge is braked, the denser components in the outer separation chamber move toward the closed end and away from the narrow neck 163. However, a density gradient may exist in the outer separation chamber, where the liquid density is greater toward the more radially outward portions of the outer separation chamber 162. In this case, some backflow may occur at the top of the outer separation chamber, where the separated components at the top of the chamber move toward the narrow neck 163. If these components move far enough toward the neck 163, they can be carried into the upper separation chamber 161 and siphoned from the upper separation chamber 162 into the mixing chamber 176.Although this can be controlled by rotating the machine longer to pack the dense components more tightly or by slowing it down, it can be advantageous to add baffles 191 in the lower separation chamber, as shown in Figure 14. The baffles 191 can extend substantially across the depth of the outer separation chamber 162 and be positioned to impede the movement of dense constituents within the outer separation chamber. To facilitate air removal during the initial filling of the lower separation chamber and to facilitate separation within the lower separation chamber, the baffles 191 can be separated from the outer walls of the outer separation chamber 162. The baffles can be round, oval, square, or rectangular. Furthermore, multiple rows of baffles can be arranged at different radial distances to form a grid.Additionally, the rows can be shifted in the circumferential direction. Figure 19 shows an alternative embodiment of the siphon 167 that includes a vent channel 174 at the peak of the curve 169. The vent channel 174 extends from the peak of the curve 169 inward toward the center of the cartridge and is used to facilitate pump-based transfer of the sample from the separation area 160 to the mixing chamber 175. When the collector 108 is not attached, the vent channel 174 is open to the air. When the collector 108 is presented into the cartridge 150, the vent can be covered by a seal and closed. In an illustrative method of operating the siphon 167 that includes the vent channel 174, after separation of the blood plasma, the collector 108 is presented and made contact with the cartridge 150.The extraction pump 118 draws gas from the cartridge 150 through the outlet 156, which draws the sample from the separation area 160 through the siphon line 167 and into the mixing chamber 175. After a predefined exact extraction volume, the collector 108 is lifted and disconnected from the cartridge 150 and the vent channel 174 is opened to the air. Then, the centrifuge 101 rotates the cartridge 150 so that the sample remaining in the siphon line 167 moves downwards on both sides of the siphon line due to centrifugal force and away from the vent channel 174. The vent channel 174 allows the movement of the sample to allow the air drawn in through the vent channel to displace the sample in the siphon line 167 as the sample moves away from the center of rotation towards the mixing chamber 175 and towards the separation area 160.By rotating the cartridge, in the absence of the vent channel 174, the siphoning action would drain the separation area 160 to the point where the air reaches the inlet to the siphon line, as previously described. In the vented embodiment of the siphon line 167, the amount of sample transferred to the mixing chamber can be determined by the pump's extraction volume rather than by the geometry of the separation area and the siphon line. Therefore, the volume of sample transferred is selectable rather than fixed. Sample mixture From the separation area 160, the blood plasma moves to the mixing chamber 175, which may contain reagents. For example, the mixing chamber 175 may contain lyophilized paramagnetic capture beads 177, a detection marker, a control analyte, and a control marker. Once in the mixing chamber 175, the blood plasma is mixed with the reagents by rapid acceleration and deceleration of the cartridge 150, all while continuing to rotate in the first circumferential direction, as shown in Figure 14. In some embodiments, mixing of the blood plasma with the reagents is facilitated by a mixing ball 176 disposed in the mixing chamber 175. The acceleration and deceleration of the cartridge 150 as it rotates in the first circumferential direction causes the mixing ball 176 to move back and forth through the mixing chamber 175, bouncing off its walls. For example, in one embodiment, the centrifuge 101 can rotate the cartridge 150 at a speed between 200 rpm and 500 rpm, accelerating and decelerating at 1500 rpm / s. This corresponds to a mixing frequency of 5 Hz. The turbulent motion of the mixing ball 176 initially rehydrates and releases the paramagnetic capture beads, the detection marker, the control analyte, and the control marker into the plasma. The mixing ball 176 also helps to facilitate the binding kinetics of the target analyte to the paramagnetic capture beads 177 and to the hQ^nm / Lznz / B / YiAi detection marker.After the mixing step, the target analyte and the detection marker can be combined with the paramagnetic capture beads dispersed throughout the blood plasma. In some embodiments, rehydration of the reagents and incubation of the target analyte are carried out in less than 20 minutes, for example, in less than 10 minutes or less than 5 minutes. In some embodiments, the mixing chamber 175 has geometric features that enhance the mixing capacity of the mixing ball 176 by varying the direction of the mixing ball 176. For example, in some embodiments, the outer surface of the mixing chamber 175 includes a rough or textured surface to promote rebound of the mixing ball as it rolls back and forth. Similarly, in some embodiments, the outer surface of the mixing chamber 175 may include an inwardly projecting radial surface to cause the mixing ball to bounce as it passes over the projection.Additionally, in some other embodiments, the ends of the mixing chamber 175 are inclined radially inward to push the mixing ball inward at the ends of the mixing chamber and cause the mixing ball to reverse direction and pass through the mixing chamber again near the radially inward side of the mixing chamber. For example, both ends may be sloped in such a way as to allow a figure-eight pattern of the mixing ball as the cartridge rotates back and forth. The term "mixing ball" is used herein with reference to the movement of this feature, and not with respect to any particular shape. Therefore, the mixing ball 176 may be spherical in some embodiments, but may have a different shape in others. For example, the mixing ball 176 may be oval, cubic, or star-shaped. In some embodiments, the mixing ball is nonmagnetic. The term "nonmagnetic," as used herein, includes materials that are neither magnetic nor paramagnetic. Additionally, in some embodiments, the surface of the mixing ball includes a substance that has low reactivity. For example, in some embodiments, the mixing ball 176 may include brass, glass, or Teflon. Plastic, ceramic, or other hard materials with a density higher than that of the sample may also be used for the mixing ball.In other embodiments, particularly those where paramagnetic capture beads are not used, the mixing ball 176 may include ferromagnetic materials, such as steel. Similarly, in some embodiments, the mixing ball is coated with a substance having low reactivity. In some embodiments, the mixing chamber and surrounding channels include one or more features for retaining the sample in the mixing chamber during a mixing process. For example, in the cartridge 150 shown in Figures 9 to 19, both the channel upstream of the mixing chamber, which is formed by the siphon 167, and the channel 173 downstream of the mixing chamber extend radially inward from the mixing chamber 175. Consequently, the centrifugal force when the cartridge 150 is rotated by means of the centrifuge 101 pushes the sample outward and into the mixing chamber 175. Similarly, to prevent the sample from moving out of the mixing chamber by capillary action, at least one of the channels 167 and 173 directly connected to the mixing chamber 175 may include a capillary enlargement 178 and 179. For example, in the cartridge 150 as shown in Figure 14, both the channel 167 upstream of the mixing chamber and the channel 173 downstream of the mixing chamber include the respective capillary enlargements 178 and 179. Each of the capillary enlargements 178 and 179 is formed by a section of the respective channel 167 and 173 that expands in the direction away from the mixing chamber 175. The expanding cross-sectional area of ​​the capillary enlargement 178 and 179 results in reduced capillary force as the sample moves away from the mixing chamber 175.The use of capillary swellings 178 and 179 reduces the effect of capillary action and retains the incubated liquid in the chamber after mixing and incubating the paramagnetic capture beads, the hQ^n Ln / Lznz / E / YiAi detection markers, the control analytes, and the control markers. This allows time for the magnet 130 to draw the paramagnetic beads out of the suspension without the incubated liquid leaving the chamber 175, as described in more detail below. In the embodiment shown in Figures 9 to 19, the capillary swellings are diamond-shaped. In other embodiments, other shapes that expand as they project away from the mixing chamber 175 are also possible. Additionally, the use of two capillary enlargements can help balance the forces on the sample to retain it in the mixing chamber 175. For example, the mixing chamber 175 can be filled to such an extent that the fill line lies on both sides of the mixing chamber 175 within the capillary enlargements 178 and 179. Consequently, if the sample is moved to one side of the mixing chamber, so that the fill line in one of the channels moves radially inward into an enlarged section of the respective capillary enlargement (e.g., 178), the capillary force within that channel will be reduced. Simultaneously, the fill line in the channel on the opposite side of the mixing chamber 175 must move radially outward into a smaller cross-sectional area of ​​the opposite capillary enlargement (e.g., 179) where the capillary force will be stronger.Therefore, capillary forces on the sample from both capillary enlargements will cause the sample to remain within the mixing chamber. To help facilitate this balancing effect, in some embodiments, the two capillary enlargements 178 and 179 are in the same radial position. Capillary dilations 178 and 179 can also serve as a reservoir to hold a portion of the sample during the initial stages of the mixing process. In some embodiments, the reagents can be stored stably and dry within the cartridge 150. For example, the reagents can be lyophilized prior to the disclosure analysis method. In such a case, the mixing of the blood plasma and the lyophilized reagents within the mixing chamber 175 may result in the release of air that was captured during the lyophilization process. Again, due to the centrifugal force generated by the rotation of the cartridge, this air will move radially into and out of the sample as the mixing process occurs.Therefore, the total volume occupied by the sample when it first enters the mixing chamber is greater than later in the mixing process, once the air has been released. Capillary enlargements 178 and 179 can act as a reservoir to hold a portion of the sample until the air has been released and allowed to escape. In some embodiments, controller 140 can be configured to take an image of the mixing chamber 175, or a portion thereof, using the process quality control camera after transfer from the separation area 160. Controller 140 can further be configured to analyze the image and determine the fill level of the mixing chamber 175. Knowing the exact volume of the sample being analyzed can be useful for determining a precise concentration of the target analyte. Therefore, controller 140 can be configured to continue the analysis in response to the determination that the volume in the mixing chamber 175 exceeds a threshold value. Additionally, controller 140 can be configured to use the volume of the sample being analyzed to normalize the resulting analysis data. In some embodiments, the volume of the sample portion transferred to the mixing chamber 175 is greater than the volume of the mixing chamber, so that a portion of the sample remains in channel 167 upstream of the mixing chamber and channel 173 downstream of the mixing chamber. Therefore, the controller 140 can be configured to identify the sample meniscus line in both channels from the image taken by the process quality control camera and calculate the volume based on the position of these meniscus lines. Magnetic movement of the sample In some embodiments, the analyzer 100 may include one or more magnets 130 (106) configured to move the paramagnetic capture beads as described in more detail below. As illustrated in the cross-section of the analyzer 100 shown in Figure 20, each of which may be coupled to the movable plates 132 and 133. The magnets 130 and 131 may be positioned above or below the cartridge to allow movement of the paramagnetic capture beads 177 from outside the cartridge 150. The linear movement of the magnet 130 in the radial and axial directions, combined with the rotation of the cartridge 150 by the collector's positioning motor 110, allows the magnet 130 to be positioned over any part of the cartridge 150 without the need to move the magnet 130 in the circumferential direction.Therefore, in some embodiments, the platen 133 may be enabled to move magnets 130 and 131 back and forth along the radial direction of the cartridge 150 using the radial magnet platen 133, as well as toward and away from the cartridge 150 in the axial direction to introduce or remove the magnetic attraction of the paramagnetic capture beads 177 using the axial magnet platen 132. In other embodiments, the movable platens may operate to move in three dimensions in order to move over any part of the cartridge 150 without the need for the cartridge 150 to rotate. In some embodiments, the magnet may be an electromagnet, while in other embodiments, the magnet may be a permanent magnet. Additionally, in some embodiments, the electromagnets may be activated using alternating current or DC current 126 to further facilitate the manipulation of the paramagnetic beads. Once the contents of the mixing chamber 175 have been thoroughly mixed and the target analytes have bound to the dispersed paramagnetic capture beads 177 (as shown in Figure 14), magnets 130 and 131 can be inserted to move the paramagnetic capture beads 177 through the cartridge 150. With magnet 130 positioned adjacent to the mixing chamber 175, the cartridge 150 can be rotated back and forth over magnet 130 in order to gather the paramagnetic capture beads 177 into a bolus, as shown in Figure 16. In some embodiments, controller 140 is configured to take an image of the bolus of beads after the paramagnetic capture beads have been collected using magnet 130.Additionally, in some embodiments, controller 140 is configured to measure the size of the paramagnetic bead pellet and continue the analysis if the pellet size is within a predetermined range. Otherwise, controller 140 can identify an error and interrupt the analysis. In some embodiments, after the paramagnetic capture beads 177 are secured by the magnet 130, a wash buffer 182 can be pumped through the mixing chamber 175 to remove the blood plasma from it, as shown in Figure 16. In some embodiments, during the purging of blood plasma from the mixing chamber 175, the bolus of paramagnetic capture beads 177 can be held in a particular location within the mixing chamber 175 to prevent dispersion of the bolus. For example, the bolus can be placed in a corner of the mixing chamber 175 during the blood plasma purging.In some embodiments, the wash buffer 182 is supplied to the mixing chamber 175 via a wash chamber 181. The mixing chamber 175 and the wash chamber 181 may be radially offset from each other. Additionally, in some embodiments, the microliquid channel between the mixing chamber 175 and the wash chamber 181 may extend along a radial line and have a cross-sectional area of ​​1 mm². In other words, the microliquid channel between the mixing chamber 175 and the wash chamber 181 does not extend circumferentially. Consequently, the liquid in the mixing chamber is not forced to flow through the channel from the mixing chamber 175 to the wash chamber 181 during acceleration or deceleration of the cartridge 150 during the mixing stage.Furthermore, as explained above, the channel 173 prior to the mixing chamber may include a capillary enlargement 178 that helps to retain the sample in the mixing chamber 175. In some embodiments, the wash buffer 182 is introduced into the cartridge 150 through the manifold 108 using a wash pump 116 and the elution buffer 185 can be pumped to the cartridge 150 through the manifold 108 using an elution pump 117, as shown in Figure 8. In one embodiment, the wash pump 116 can pump 150 microliters of wash buffer 182 through the wash delivery line 111 of the manifold 108 and to the cartridge 150 through the wash inlet line 154 to fill the wash chamber. Similarly, in another embodiment, for example, the elution pump 117 can pump 25 microliters of elution buffer 185 through the elution delivery route 112 of the manifold 108 to the cartridge 150 through the elution inlet route 155 to fill the elution chamber.As explained above, each of the administration lines 111 and 112 can be carefully positioned to couple with the respective inlet lines 154 and 155 to form a sealed connection. In some embodiments, controller 140 can be configured to take an image of at least a portion of wash chamber 181 after it is filled with wash buffer 182. Additionally, controller 140 can be configured to analyze the image of wash chamber 181 to confirm the absence of air within the chamber or to confirm that the volume of any air bubbles within the chamber is below a predetermined threshold. For example, controller 140 can be configured to calculate the shape of any air bubbles within wash chamber 181 and calculate the total air volume within the chamber. If the calculated air volume is above a predetermined threshold, the controller can be configured to pump more liquid or interrupt the analysis.Similarly, the controller can be configured to continue the analysis if the calculated air volume is below a predetermined threshold or is zero. A similar process can be used with respect to the air in elution chamber 184. Specifically, controller 140 can be configured to analyze the image of elution chamber 184 to confirm the absence of air in elution chamber 184 or to confirm that the volume of any air bubbles within elution chamber 184 is below a predetermined threshold. For example, controller 140 can be configured to calculate the shape of any air bubbles within elution chamber 184 and calculate the total air volume within elution chamber 184. If the calculated air volume is above a predetermined threshold, the controller can be configured to interrupt the analysis.Similarly, the controller can be configured to continue the analysis if the calculated volume of air in the elution chamber 184 is below a predetermined threshold or is zero. The analyzer 100 may also include an extraction pump 118 that is coupled to the cartridge 150 via the manifold 108. In particular, the cartridge 150 may include a wash outlet 156 and an elution outlet 157 that are connected to the extraction pump 118 via the manifold 108. Specifically, the wash outlet 156 may be coupled to the wash extraction line 113 of the manifold 108, and the elution outlet 157 may be coupled to the elution extraction line 114 of the manifold 108. The inlet and outlet lines may form two respective liquid lines through the cartridge 150. Specifically, the wash inlet line 154 and the wash outlet line 156 may form a wash line 183. Similarly, the elution inlet line 155 and the elution outlet line 157 may form a wash line 183. Elution 157 can form an elution line 186 through cartridge 150.The operation of the wash pump 116 and the extraction pump 118 can control the flow of wash buffer 182 through the wash line 183, while the operation of the elution pump 117 and the extraction pump 118 can control the flow of elution buffer 185 through the elution line 186. Notably, in some embodiments, wash buffer 182 or elution buffer 185 is not actually extracted through the respective wash outlet 156 and elution outlet 157, but instead, only gas is removed through these outlets as a way of controlling the movement of the respective liquids through the wash line 183 and the elution line 186. For example, the waste chambers in the cartridge may be large enough that it is not necessary to extract liquid from the cartridge.Additionally, in some embodiments, each of the washing line 183 and the elution line 186 can be coupled to a respective extraction pump, instead of both being coupled to a single extraction pump. Furthermore, a single extraction pump can be connected to the washing line 183 at a given time and, alternatively, connected only to the elution line 186 at a different time. In some embodiments, the wash pump 116 and the extraction pump 118 are carefully controlled to prevent the wash buffer 182 from entering the detection chamber 184. Additionally, in some embodiments, the analyzer operates the wash pump 116 and the extraction pump 118 to maintain an air mass in the connection passage 187 while the wash fluid is introduced into the wash chamber, as shown in Figure 16. For example, in some embodiments, the controller operates the wash pump 116 and the extraction pump 118 at similar flow rates to transfer the wash buffer along the wash line to prevent the wash fluid from being diverted outside the wash line. Likewise, in some embodiments, the elution pump 117 and the extraction pump 118 are controlled to prevent the elution buffer 185 from entering the wash chamber 181. Furthermore, in some embodiments, the elution buffer and the wash buffer are introduced into the cartridge simultaneously and are controlled to prevent cross-contamination. For example, in some embodiments, as the wash buffer 182 and the elution buffer 185 are introduced into the respective wash line 183 and elution line 186, the wash pump 116, the elution pump 117, and the extraction pump 118 are controlled to form an air bubble in the connecting passage 187 that connects the wash line 183 and the elution line 186. In particular, in some embodiments, this connecting passage 187 extends between the wash chamber 181 and the detection chamber 184. The air bubble forms a pool that prevents the washing buffer 182 and the elution buffer 185 from mixing, acting as an air spring.Furthermore, the air bubble can be visibly monitored to verify that the liquids are not mixing, as explained in more detail below. In some embodiments, this air bubble is maintained until the target analyte is moved into the detection chamber 184. The use of an air mass or air bubble in the connecting passage eliminates the need for a valve to control the flow between the washing chamber and the elution chamber. In some embodiments, controller 140 can be configured to take an image of the connecting passage 187 between the washing chamber 181 and the elution chamber 184 to confirm the presence of an air mass within it. If, after analyzing the image of connecting passage 187, the controller identifies the presence of an air mass in the passage, controller 140 can be configured to continue the analysis. Conversely, if controller 140 does not identify an air mass in the passage, it can be configured to discontinue the disclosure analysis. In some embodiments, at least one of the wash or elution lines includes an air trap. For example, in some embodiments, the depth of the wash line 183 increases in an area between the wash inlet 154 and the wash chamber. This increased depth of the wash line 183 provides space for air pumped into the wash line to be trapped. For example, in some embodiments, the analyzer holds the cartridge horizontally so that the depth direction is parallel to gravity. Consequently, any air in the wash line 183 will float upward and enter the air trap created by the increased depth of this section of the wash line. The elution line 186 may have a similar air trap in the vicinity of the elution inlet 155. With the paramagnetic capture beads 177 collected in a bolus in the mixing chamber 175, as shown in Figure 15, the magnet 130 can be moved along the movable stage 133 in conjunction with the rotation of the cartridge 150 to carry the bolus of paramagnetic capture beads 177 to the wash chamber 181. In some embodiments, the controller 140 can be configured to take an image of at least a portion of the wash chamber 181 after the bolus of paramagnetic capture beads 177 has been transferred to the wash chamber 181. Additionally, in some embodiments, the controller 140 is configured to measure the size of the bolus of paramagnetic beads in the wash chamber 181 and continue with the analysis if the size of the bolus of beads in the wash chamber 181 is within a predetermined range. Otherwise, controller 140 may identify an error and interrupt the analysis. Once the paramagnetic capture beads 177 are arranged in the wash chamber 181, the cartridge 150 can be rotated back and forth to effectively wash the paramagnetic capture beads 177, removing all contaminants from the sample except the target analyte, the detection marker, and any controls used in the system, as schematically shown in Figure 17. In some embodiments, the spent wash buffer can be swept out of the wash chamber 181, and a fresh volume of wash buffer 182 can be added to the wash chamber 181 before repeating the wash step. The wash step can be performed multiple times, for example, three or more times. In some embodiments, a second magnet 131 can be introduced during the washing stage to disperse and recondense the paramagnetic capture beads 177 during a series of stages in a washing operation. In particular, the magnet 130 and the second magnet 131 can be arranged on opposite sides of the washing chamber 181 in order to disperse and recondense the paramagnetic capture beads 177 as they move through the washing chamber 181. The distribution of the paramagnetic capture beads 177 allows the washing buffer to wash them more effectively than if the beads were held together in a bolus. Consequently, the time and number of cycles required for the washing stage can be reduced compared to conventional washing methods. Figures 21 and 22 illustrate two illustrative embodiments of a washing operation according to the invention. Figure 21 illustrates a washing operation in which two hands 130 and 131 move relative to the washing chamber 181 in a toothed pattern. In particular, Figure 21 illustrates five discrete locations P1 to honn Ln / Lznz / E / YiAi P5 that occupy the first magnet 130 and the second magnet 131 during the toothed washing operation. In position P1, the second magnet 131 is away from the wash chamber 181, while the first magnet 130 is adjacent to the wash chamber 181, causing the paramagnetic capture beads to form a bolus adjacent to the first magnet 130. Magnets 130 and 131 are then moved axially so that the second magnet 131 moves toward the wash chamber 181, while the first magnet 130 moves away from the wash chamber 181. Along with this movement, the cartridge 150 can also be rotated so that magnets 130 and 131 are also repositioned laterally with respect to the wash chamber 181. As the first magnet 130 moves away from the paramagnetic capture beads 177, the bolus disperses in the wash solution, allowing unwanted blood plasma constituents to separate and be washed away from the capture beads. paramagnetic 177.The dispersion of the paramagnetic capture beads 177 is illustrated in Figure 21 between positions P1 and P2. As the second magnet 131 approaches the washing chamber 181, the paramagnetic capture beads 177 are drawn out of suspension and reform into a tight bolus. The dispersion and recondensation steps can then be repeated in the opposite direction as magnets 130 and 131 move from position P2 to position P3. Similarly, this process can be continued in a jagged pattern for several additional steps. Figure 22 illustrates another embodiment of a washing operation in which the two magnets 130 and 131 move relative to the washing chamber 181 in a square wave pattern. In particular, Figure 22 illustrates nine discrete locations P1 to P9 occupied by the first magnet 130 and the second magnet 131 during the toothed washing operation. Again, at position P1, the second magnet 131 is away from the washing chamber 181 while the first magnet 130 is adjacent to the washing chamber 181, causing the paramagnetic capture beads to form a bolus adjacent to the second magnet 131. The cartridge 150 is then rotated so that the magnets 130 and 131 move relative to the washing chamber 181.Advantageously, the cartridge 150 can be rotated at a speed sufficient to spread the paramagnetic capture beads 177 across the surface of the wash chamber 181, thereby dispersing the paramagnetic capture beads across the surface of chamber 181 in the wash solution. Magnets 130 and 131 are then moved to position P3 so that the second magnet 131 approaches the wash chamber 181 while the first magnet 130 moves away from the wash chamber 181. Again, as the first magnet 130 moves away from the paramagnetic capture beads 177, the bolus is dispersed in the wash solution so that unwanted constituents of the blood plasma can be separated and washed away from the paramagnetic capture beads 177.Similarly, when the second magnet 131 approaches the wash chamber 181, as shown in position P3, the paramagnetic capture beads 177 are drawn out of suspension and pressed against the wall of the wash chamber. Although the washing operations shown in Figures 21 and 22 involve recondensing the paramagnetic capture beads into a tight bolus, in other embodiments, the paramagnetic capture beads can be directed through the washing chamber without exclusively merging into a bolus during the operation. For example, during the operation, the beads may remain relatively dispersed in the washing liquid but moved back and forth and along the length of the washing chamber by the magnets. As previously stated, in some embodiments, the magnet 130 and the second magnet 131 are positioned on opposite sides of the cartridge 150, for example, above and below the cartridge 150. In other embodiments, the magnets 130 and 131 are arranged on the same side of the cartridge 150 but on opposite sides of the wash chamber 181 with respect to the radial direction. Additionally, in some embodiments, the magnets 130 and 131 extend the paramagnetic capture beads 177 along the length of the wash chamber 181. Furthermore, in some embodiments, the distance between the first magnet 130 and the second magnet 131 is varied by using the movable platen 132 during the wash stage. This relative movement of the manes 130 and 131 can promote the interruption of the ball of pearls of hQ^n Ln / Lznz / E / YiAi capture paramagnetic 177, improving the washing operation. After the washing operation, the paramagnetic capture beads 177 can be reassembled by the first magnet 130 and moved through the connecting step 187 into the detection chamber 184, which is filled with elution buffer 185, as shown in Figure 19. While holding the paramagnetic capture beads 177 with one or more magnets 130 and 131, the cartridge 150 can be rotated back and forth to pass the paramagnetic capture beads 177 through the detection chamber 184 and the elution buffer 185, which removes the bonds between the paramagnetic capture beads 177 and the target analyte and between the marker and the target analyte. This leaves a suspension of pure fluorochrome conjugate in the elution buffer 185 within the detection chamber 184. To improve the elution of the target analyte and markers, a magnetic elution operation similar to the washing operations described above can be used. For example, magnets 130 and 131 can be moved relative to the detection chamber 184 in a particular pattern, such as those shown in Figures 21 and 22. Controlling the paramagnetic beads in a manner similar to the washing operation improves the magnetic elution operation. Once the elution process has been carried out, the paramagnetic capture beads 177 can be moved out of the detection chamber 184 or to one end of the detection chamber 184 to avoid interfering with the optical system 120. The optical system 120 of the analyzer 100 can then be activated to analyze the solution in the detection chamber 184 in order to determine the presence or concentration of the target analyte in the liquid volume in the detection chamber 184, as explained above. In another aspect of the disclosure, the optical system 120 of the analyzer 100 includes a second electromagnetic radiation source 128 and a second detector 129 for multiplexing operation. In some embodiments, the analyzer's second electromagnetic radiation source 128 and the second detector 129 can be used to determine the presence of a second target analyte in the sample. In other embodiments, the second electromagnetic radiation source 128 and the second detector 129 can be used to measure the concentration of a control analyte in the cartridge 150. For example, the cartridge 150 may contain a precise and known quantity of the control analyte. Consequently, the measured concentration of the control analyte can be used as a comparator for the target analyte. Therefore, this measured concentration can be used to adjust the detected concentration of the target analyte. For example, if the measured concentration of the control analyte is only 95% of the known actual concentration of the control analyte, the controller 140 can use this percentage difference to adjust the detected concentration of the target analyte. For example, the controller 140 can determine that the analyzer 100 also detects only 95% of the target analyte in the sample and adjust the calculated concentration accordingly. In some embodiments, the electromagnetic radiation from the first electromagnetic radiation source 121 and the second electromagnetic radiation source 128 are directed at the cartridge using the same target. In fact, in some embodiments, the electromagnetic radiation from both sources is directed at the same examination space. In some embodiments, the first electromagnetic radiation source 121 and the second electromagnetic radiation source 128 emit electromagnetic radiation of different wavelengths, for example, of different colors. The disclosure provides systems and methods for the highly sensitive detection and quantification of one or more target analytes, such as markers of biological states. Singleplex and Multiplex Tests In one respect, the disclosure provides systems and methods that can perform a singleplex assay on a sample to detect and analyze a single type of target analyte in the sample. In other respects, the disclosure provides systems and methods that can perform a multiplex assay on a sample to detect and analyze multiple (e.g., two, three, or more) different types of target analytes in the sample. The use of the hQ^nm / Lznz / E / YiAi multiplexed systems and methods described herein can provide faster detection and analysis of multiple target analytes, using a reduced sample volume and a reduced reagent volume than might be required to perform a similar analysis of those target analytes using singleplex assays.Additionally, the multiplexed systems and methods described in this document may allow the analysis of a sample that includes a target analyte to compare it with a control assay of a known concentration. To detect and analyze several different types of target analytes in a sample, the multiplexed analyzer system can distinguish one type of target analyte from the others. This can be achieved, in part, by titrating the different target analytes with different markers, which have excitation wavelength bands and / or emission wavelength bands that differ from each other. In some implementations, the different markers have excitation wavelength bands and / or emission wavelength bands with relatively little or no overlap. In other implementations, there may be some overlap between the excitation wavelength bands and / or the emission wavelength bands of the markers.Multiplexing can also be achieved by implementing more than one liquid circuit in the same cartridge, with each circuit spatially distinct and carrying reagents for different target analytes. With different liquid circuits, the different target markers do not need to have different excitation and emission wavelengths. The additional circuits can collect samples from the same sample chamber or from different sample chambers. Electromagnetic radiation power and deposit size In the optical system, the electromagnetic radiation source 121 can be adjusted so that the wavelength of the electromagnetic radiation is sufficient to excite a fluorescent marker bound to the target analyte. In some embodiments, the electromagnetic radiation source 121 is a laser that emits light in the visible spectrum. In some embodiments, the laser is a continuous-wave laser with a wavelength of 639 nm, 532 nm, 488 nm, 422 nm, or 405 nm. Any continuous-wave laser with a wavelength suitable for exciting a fluorescent fraction as used in the methods and compositions disclosed herein may be used without departing from the scope of disclosure. The laser power setting is generally between 1 mW and 100 mW. However, those skilled in the art will appreciate that the laser power can be adjusted to achieve the optimum signal-to-noise ratio for the measurement.To achieve this, the laser power must be set to achieve as many excitation emission cycles as possible during the marker's residence time in the examination space. The detector's storage time must also be set accordingly. A storage time longer than the time it takes to photobleach the marker or longer than the marker's residence time in the examination space will simply allow excess noise to be collected. A laser power setting that is too low or too high, or a storage time setting that is too long, will not produce the highest possible signal-to-noise ratio. As the query space in analyzer 100 passes over the labeled target analyte, the photons emitted by the fluorescent particles are recorded in detector 122 with a time delay indicative of the time the query space spends over the labeled particle. Detector 122 records the photon intensity, and the sampling time is divided into periods, where periods are arbitrarily uniform time segments with freely selectable time channel widths. The number of signals contained in each period is evaluated. One or more of several statistical analytical methods are used to determine when a marker or particle is present or when a period section contains an artifact. Period sections containing artifacts are discarded, while individual periods or period sections containing a marker are counted.The number of markers counted is indicative of the number of target analytes present in the sample. Query volume A query volume can be thought of as the effective volume of the sample in which a target analyte of interest can be detected when present. Although there are several ways to calculate the query volume of a sample, the simplest method for determining the effective volume (V) of the query volume is to calculate the effective cross-sectional area of ​​the detection volume. Because the detection volume is typically swept through the sample by passing the detection volume through the stationary sample, the volume is usually the result of the cross-sectional area of ​​the detection volume that is swept over a certain distance during the measurement time.As previously stated, the lateral extent of the cross-sectional area of ​​the query volume (perpendicular to the direction of laser movement relative to the sample and perpendicular to the direction of laser light propagation) is limited by the numerical aperture at which the laser source is viewed in the sample space. The longitudinal size of the query volume (along the laser propagation direction) is determined by the size of the chosen confocal stop. If the concentration (C) of the sample and the number (N) of molecules detected over a period of time are known, then the sample volume is the number of molecules detected divided by the sample concentration, or V = N / C (where the sample concentration has units of molecules per unit volume). For example, in some embodiments of the system described herein, all detected photons are counted and summed in 100-microsecond segments (photon counting periods). If a molecule of interest is present in the 100-microsecond segment, the detected photon count is typically significantly higher than that of the background. Therefore, the distance the detection volume has moved relative to the sample is the appropriate distance to use for calculating the sampled volume in a single segment, i.e., the query volume. In this example, if the sample is analyzed for 60 seconds, then 600,000 segments are effectively scanned. Dividing the effective volume by the number of segments yields the resulting volume, which is essentially the single-segment volume, i.e., the query volume.Mathematically, the single-segment volume, i.e., the query volume (Vs), is equal to the number (N) of molecules detected divided by the sample concentration multiplied by the number of segment periods (Cn, where n represents the number of segment periods during which the N molecules were counted). For illustrative purposes only, let's assume that a known standard of a femtomolar concentration passes through 600,000 segments and 20 molecules of the standard are detected. Consequently, the query volume, Vs, is equal to N / (Cn) or 20 / (602.214 × 105) or 55.351 pm3. Therefore, in this example, the query volume, which is the effective sample volume corresponding to a photon counting container, is 55.351 pm3. Detectors. In some embodiments, the light emitted by a fluorescent marker after exposure to electromagnetic radiation is detected. The emitted light can be, for example, ultraviolet, visible, or infrared. For instance, the first detector 122 can capture the amplitude and duration of photon bursts from a fluorescent fraction and convert these bursts into electrical signals. Detection devices such as CCD cameras, video input module cameras, and Streak cameras can be used to produce images with contiguous signals. Other embodiments use devices such as a bolometer, a photodiode, a photodiode array, avalanche photodiodes, and photomultipliers that produce sequential signals. Any combination of the aforementioned detectors can be used. Molecules for concentration analysis The instruments, kits, and methods disclosed can be used for the sensitive detection and determination of the concentration of several different types of target analytes, such as markers of biological states. Examples of molecules or analytes that can be detected using the analyzer and related methods disclosed herein include biopolymers such as proteins, nucleic acids, carbohydrates, and small molecules, both organic and inorganic. In particular, the instruments, kits, and methods described herein are useful for detecting target analytes of proteins and small molecules in biological samples and determining the concentration of such molecules in the sample. The molecules detected by the present systems and methods may be free or may be part of a complex, for example, an antibody and antigen complex, or more generally a protein and protein complex, for example, troponin complexes or prostate-specific antigen (PSA) complexes. In some embodiments, the disclosure provides compositions and methods for the sensitive detection of biological markers and for the use of such markers in diagnosis, prognosis and / or determination of treatment methods. Markers can be, for example, any composition and / or molecule, or a complex of compositions and / or molecules, that is associated with a biological state of an organism (e.g., a condition such as a disease or a non-pathological state). A marker can be, for example, a small molecule, a polypeptide, a nucleic acid such as DNA and RNA, a lipid such as a phospholipid or a micelle, a cellular component such as a mitochondrion or chloroplast, etc. The markers contemplated by this disclosure may be previously known or unknown. For example, in some embodiments, the methods herein may identify novel polypeptides that can be used as markers for a biological state or condition of interest, whereas in other embodiments, known polypeptides are identified as markers for a biological state or condition of interest.Using disclosure systems, one may be able to observe such markers, for example, polypeptides with high potential for use in determining the biological status of an organism, but which are only present at low concentrations, such as those that leak from diseased tissue. Other potentially useful markers or polypeptides may be those that are related to the disease, for example, those generated in the tumor environment and the host. Any suitable marker that provides information regarding a biological status can be used in disclosure methods and compositions. A marker, as the term is used herein, encompasses any molecule that can be detected in a sample from an organism and whose detection or quantification provides information about the organism's biological status. Biological states include, but are not limited to, phenotypic states; conditions affecting an organism; developmental states; age; health; pathology; disease detection, processing, or staging; infection; toxicity; or response to chemical, environmental, or pharmacological factors (such as drug response phenotyping, drug toxicity phenotyping, or drug efficacy phenotyping). The term organism, as used herein, refers to any living thing composed of at least one cell. An organism can be as simple as a single-celled organism or as complex as a mammal. An organism for the purposes of this disclosure is preferably a mammal. Such a mammal may be, for example, a human being or an animal such as a primate (e.g., a monkey, chimpanzee, etc.), a domesticated animal (e.g., a dog, a cat, a horse, etc.), a farm animal (e.g., a goat, a sheep, a pig, cattle, etc.), or a laboratory animal (e.g., a mouse, a rat, etc.). Preferably, an organism is a human being. Scoreboards In some embodiments, the disclosure provides methods and compositions that include markers for the detection and quantification of highly sensitive molecules, e.g., markers. Many strategies can be used to label target analytes to enable their detection or discrimination within a mixture of particles. Labels can be attached using any known means, including methods that utilize nonspecific or specific interactions between the labeler and the target analyte. Labels can provide a detectable signal or affect the mobility of the particle in an electric field. Labeling can be performed directly or via bonding members. In some embodiments, the marker comprises a molecule-binding member, wherein the binding member is attached to a fluorescent moiety. The compositions and methods disclosed herein may utilize highly fluorescent moiety. Suitable moiety fractions for the compositions and methods disclosed herein are described in more detail below. Fluorescent molecules may be attached to the binding members by any known means, such as direct conjugation, or indirectly (e.g., biotin and streptavidin). The fluorescent fractions may be fluorescent dye molecules. Examples of fluorescent molecules include, but are not limited to, molecules of ALEXA FLUOR® 488, ALEXA FLUOR® 532, ALEXA FLUOR® 647, ALEXA FLUOR® 680, or ALEXA FLUOR® 700 Brilliant Violet™ (BD Biosciences) such as Brilliant Violet 421™, Brilliant Violet 510™, Brilliant Violet 570™, Brilliant Violet 605 dyes, and ATTO™ (ATTO TECH GmbH) such as ATTO™ 532. In some embodiments, the dye molecules are ALEXA FLUOR® 647 dye molecules. Union members In some embodiments, the binding member comprises an antibody. In some embodiments, the antibody is a monoclonal antibody. In other embodiments, the antibody is a polyclonal antibody. The antibody can be specific for any suitable marker. In some embodiments, the antibody is specific for a marker selected from the group consisting of cytokines, growth factors, cancer markers, inflammation markers, endocrine markers, autoimmune markers, thyroid markers, cardiovascular markers, diabetes markers, infectious disease markers, neurological markers, respiratory markers, gastrointestinal markers, musculoskeletal markers, dermatological disorders, and metabolic markers. hQ^n Ln / Lznz / E / YiAi Any suitable binding member with the required specificity for the shape of the molecule, such as a marker, to be detected can be used. If the molecule, for example, a marker, has several different shapes, several binding member specificities are possible. Suitable binding members are well-known in the field and include antibodies, aptamers, lectins, and receptors. One useful and versatile type of binding member is an antibody. Capture and detection pairs of binding members, such as capture and detection antibody pairs, can be used in embodiments of the disclosure. Therefore, in some embodiments, a heterogeneous assay protocol is used in which two binding members, such as two antibodies, are typically employed. One binding member is a capture member, usually immobilized on a solid support, and the other binding member is a detection member, typically with a detectable marker attached. The antibody pairs can be designed and prepared using methods well known in the field. The compositions of the disclosure include antibody pairs where one member of the antibody pair is a marker as described herein, and the other member is a capture antibody. In some embodiments, it is useful to employ an antibody that cross-reacts with a variety of species, either as a capture antibody, a detection antibody, or both. Such embodiments include measuring drug toxicity by determining, for example, the release of cardiac troponin into the blood as a marker of cardiac damage. A cross-reacting antibody allows toxicity studies to be conducted in one species, for example, a non-human species, and the results to be directly transferred to clinical studies or observations in another species, for example, humans, using the same antibody or antibody pair in the assay reagents, thereby reducing inter-assay variability.Therefore, in some embodiments, one or more of the antibodies for use as a marker-binding member of the molecule of interest, for example, cardiac troponin, such as hQ^nm / Lznz / E / YiAi cardiac troponin I, may be a cross-reactive antibody. In some embodiments, the antibody cross-reacts with the marker, for example, cardiac troponin, from at least two species selected from the group consisting of human, monkey, dog, and mouse. In some embodiments, the antibody cross-reacts with the marker, for example, cardiac troponin, from the entire group consisting of human, monkey, dog, and mouse. The foregoing detailed description outlines various features and functions of the systems, devices, and methods disclosed with reference to the accompanying figures. In the figures, similar symbols normally identify similar components unless the context indicates otherwise. The illustrative embodiments described in the detailed description, figures, and claims are not intended to be limiting. Other embodiments may be used and other changes may be made without departing from the scope of the subject matter presented herein. It will be readily understood that the aspects of this disclosure, as generally described herein and illustrated in the figures, may be arranged, substituted, combined, separated, and designed in a wide variety of different configurations, all of which are explicitly contemplated herein. While several aspects and achievements have been disclosed herein, other aspects and achievements will be evident to those skilled in the art. The various aspects and achievements disclosed herein are for illustrative purposes only and are not intended to be limiting, with the actual scope indicated by the following claims. ACHIEVEMENTS Implementation 1. An analyzer system for measuring the concentration of a target analyte in a sample, the analyzer system comprising: an engine; a coupling attached to the motor to rotate by means of the motor drive; hQ^n Ln / Lznz / E / YiAi a cartridge retained in the coupling and including a liquid system configured to receive a sample, isolate a target analyte from the sample, and collect an amount of a first marker that is proportional to an amount of the target analyte in the sample, including the liquid system: an inlet chamber, a mixing chamber downstream of the inlet chamber and configured to mix at least a portion of the sample to bind the target analyte with the first marker, and a washing chamber downstream of the mixing chamber and connected to the mixing chamber by a channel, wherein the washing chamber is radially offset from the mixing chamber to prevent flow of the sample into the washing chamber during a mixing process taking place in the mixing chamber; a first source of electromagnetic radiation configured to provide electromagnetic radiation to form a consultation space within a cartridge detection chamber; a first detector configured to detect electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and a controller configured to identify the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector. Embodiment 2. The analyzer system according to embodiment 1, wherein a channel extending from the mixing chamber to the washing chamber includes a capillary enlargement, the capillary enlargement having a cross-sectional area expanding in the direction away from the mixing chamber. Embodiment 3. The analyzer system according to embodiment 1, wherein the cartridge liquid system further includes a separation area disposed between the inlet chamber and the mixing chamber, the separation area including a radially inner separation chamber and a radially outer separation chamber that are connected by a narrow neck. Embodiment 4. The analyzer system according to embodiment 3, wherein a siphon extends from the radially inward separation chamber to the mixing chamber. Embodiment 5. The analyzer system according to embodiment 4, wherein a siphon vent extends from the siphon in the vicinity of a siphon peak. Implementation 6. An analyzer system for measuring the concentration of a target analyte in a sample, the analyzer system comprising: an engine; a coupling attached to the motor to rotate by means of the motor drive; a cartridge retained in the coupling and including a liquid system configured to receive a sample, isolate a target analyte from the sample, and collect an amount of a first marker that is proportional to an amount of the target analyte in the sample, including the liquid system: an inlet chamber, and a mixing chamber downstream of the inlet chamber and configured to mix at least a portion of the sample to bind the target analyte with the first marker, a mixing ball disposed in the mixing chamber; and a controller including a processor and a computer-readable non-transient medium having stored program instructions which, when executed by the processor, cause the execution of a set of operations including: motor rotation to rotate the cartridge, and intermittently accelerate and decelerate the rotation of the centrifuge to move the mixing ball in the mixing chamber back and forth recursively through the mixing chamber. Embodiment 7. The analyzer according to embodiment 6, wherein hQ^n Ln / Lznz / E / YiAi further comprises lyophilized reagents arranged in the mixing chamber. Embodiment 8. The analyzer according to embodiment 6, wherein the mixing ball is not magnetic. Implementation 9. An analyzer system for measuring the concentration of a target analyte in a sample, the analyzer system comprising: an engine; a coupling attached to the motor to rotate by means of the motor drive; a cartridge retained in the coupling and including a liquid system configured to receive a sample, isolate a target analyte from the sample, and collect an amount of a first marker that is proportional to an amount of the target analyte in the sample, including the liquid system: A liquid line including a liquid inlet path configured to receive a liquid, a first chamber and a liquid outlet path, a detection chamber, and a connecting passage between the first washing chamber and the detection chamber; and a controller including a processor and a computer-readable non-transient medium having stored program instructions which, when executed by the processor, cause the execution of a set of operations including: pump liquid along the wash liquid line and into the first chamber while maintaining an air mass in the connection passage. Realization 10. The analyzer system according to realization 9, wherein the liquid line is a wash line. Realization 11. The analyzer system according to realization 9, wherein the connection step extends directly from the first chamber. Realization 12. The analyzer system according to realization 9, wherein the connection step extends directly to the detection chamber. hQ^n Ln / Lznz / E / YiAi Implementation 13. An analyzer system for measuring the concentration of a target analyte in a sample, the analyzer system comprising: an engine; a coupling attached to the motor to rotate by means of the motor drive; a cartridge retained in the coupling and including a liquid system configured to receive a sample, isolate a target analyte from the sample, and collect an amount of a first marker that is proportional to the amount of the target analyte in the sample; a liquid line including a liquid inlet pathway configured to receive a liquid, a first chamber and liquid outlet pathway, a detection chamber, and a connecting step between the first washing chamber and the detection chamber; and a plurality of paramagnetic beads configured to provide a substrate for the target analyte with the first chamber; a first magnet arranged on a movable plate; and a controller that includes a processor and a computer-readable non-transient medium that has stored program instructions which, once executed by the processor, cause the execution of a set of operations that include: facilitating the relative movement of the first magnet and the cartridge to extract the paramagnetic beads from the suspension and form a bolus, the relative movement being facilitated by at least one of the movements of the first magnet through the first surface or the rotation of the cartridge. Embodiment 14. The analyzer system according to embodiment 13, wherein the controller is further configured to facilitate the elastic movement of the first magnet and the cartridge to transfer the paramagnetic beads and the target analyte from the first chamber to a second chamber. hQ^n Ln / Lznz / E / YiAi Embodiment 15. The analyzer system according to claim 14, further comprising a second magnet. Embodiment 16. The analyzer system according to Embodiment 15, wherein the controller is further configured to perform a washing operation, including the washing operation: move the first magnet away from the first surface of the cartridge so that the paramagnetic beads are dispersed in the second chamber; move a second magnet towards a second surface of the cartridge so that the paramagnetic beads accumulate near the second magnet; Move the second magnet away from the second surface of the cartridge so that the paramagnetic beads are dispersed in the second chamber; and move the first magnet towards the first surface of the cartridge so that the paramagnetic beads accumulate near the first magnet. Implementation 17. An analyzer system for measuring the concentration of a target analyte in a sample, the analyzer system comprising: an engine; a coupling attached to the motor to rotate by means of the motor drive; a cartridge retained in the coupling and including a liquid system configured to receive a sample, isolate a target analyte from the sample, and collect an amount of a first marker that is proportional to the amount of the target analyte in the sample; a quality control camera configured to take an image of the cartridge during an analysis operation; a first source of electromagnetic radiation configured to provide electromagnetic radiation to form a consultation space within a cartridge detection chamber; a first detector configured to detect electromagnetic radiation emitted in the query space by the first marker if the first marker is present in the query space; and hQ^nm / Lznz / B / YiAi a controller configured to: analyze an image taken by the quality control camera and continue an analysis operation in response to the image analysis, and identify the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector. Embodiment 18. The analyzer system according to embodiment 17, wherein the controller is configured to further rotate the cartridge in response to the image analysis. Embodiment 19. The analyzer system according to any of embodiments 1 to 18, wherein the motor includes a centrifuge coupled to the cartridge and configured to rotate the cartridge at a speed of at least 100 rpm to separate the sample components. Embodiment 20. The analyzer system according to any of embodiments 1 to 19, further comprising a manifold including a plurality of paths and configured to connect each of the plurality of paths to a respective corresponding path of the cartridge. Embodiment 21. The analyzer system according to any of embodiments 1 to 18, wherein the motor includes a positioning motor coupled to the cartridge and configured to pivot the cartridge to align the detection zone of the cartridge with the electromagnetic radiation of the first electromagnetic radiation source. Embodiment 22. The analyzer system according to any of embodiments 1 to 21, further comprising an optical system configured to direct electromagnetic radiation from the first electromagnetic radiation source to the cartridge detection chamber and to direct the electromagnetic radiation emitted by the marker to the detector. Realization 23. The analyzer system according to realization 22, wherein the optical system is a confocal system. Embodiment 24. The analyzer system according to any of embodiments 1 to 23, wherein all components of the analyzer system are arranged in a common housing and wherein the dimensions of the common housing are no greater than 1 meter in any direction. Implementation 25. The analyzer system according to any of implementations 1 to 24, wherein the controller includes a network interface for receiving control information from a user and for sending analysis data to the user. Embodiment 26. The analyzer system according to any of embodiments 1 to 25, wherein the cartridge is flat and the cartridge chambers are in a single plane. Embodiment 27. The analyzer system according to any of embodiments 1 to 26, wherein the cartridge is a disc and the cartridge chambers are positioned circumferentially around the disc. Embodiment 28. The analyzer system according to any of embodiments 1 to 27, wherein the cartridge has no valves. Embodiment 29. The analyzer system according to any of embodiments 1 to 28, wherein the cartridge is configured to receive a sample in a range of 50 microliters to 1 milliliter. Realization 30. The analyzer system according to any of embodiments 1 to 29, wherein the cartridge includes reagents stored therein. Implementation 31. A cartridge for preparing and containing a sample for measuring the concentration of a target analyte, the cartridge comprising: A liquid system configured to receive a sample, isolate a target analyte from the sample, and collect an amount of a first marker that is proportional to the amount of the target analyte in the sample, including the liquid system: a mixing chamber, a first channel in communication with the mixing chamber and a second channel in communication with the mixing chamber; and a mixing ball disposed within the mixing chamber, where the mixing ball is larger than the first channel and the second channel. Embodiment 30. The cartridge of embodiment 25, wherein the cartridge hQ^nm / Lznz / E / YiAi comprises: a base, a body disposed on the base, and a sleeve disposed on the body, wherein the body includes an open path extending through it and defining the plurality of cartridge chambers. Embodiment 31. The cartridge according to any of embodiment 30, wherein the cartridge is flat and the cartridge chambers are in a single plane. Embodiment 32. The analyzer system according to either embodiment 30 or 31, wherein the cartridge is a disc and the cartridge chambers are positioned circumferentially around the disc. Implementation 33. The analyzer system according to any of implementations 30 to 32, wherein the cartridge has no valves. Implementation 34. The analyzer system according to any of implementations 30 to 33, wherein the cartridge is configured to receive a sample in a range of 50 microliters to 1 milliliter. Realization 35. The analyzer system in accordance with any of embodiments 30 to 34, wherein the cartridge includes reagents stored therein. Implementation 36. A method for detecting the presence of a target analyte in a sample, the method comprising: introducing the sample into a cartridge, the cartridge including a liquid system for isolating the target analyte from the sample and collecting an amount of a first marker that is proportional to an amount of the target analyte in the sample, the liquid system comprising: a first chamber, a second chamber, and a channel extending from the first chamber to the second chamber; attach the target analyte to a substrate composed of paramagnetic beads; honn Ln / Lznz / E / YiAi place a first magnet near a first cartridge surface and adjacent to the first chamber; facilitating the relative movement of the first magnet and the cartridge to extract the paramagnetic beads from the suspension and form a bolus, the relative movement being facilitated by at least one of the movements of the first magnet through the first surface or the rotation of the cartridge; direct electromagnetic radiation from a first source of electromagnetic radiation to form a consultation space within the cartridge; to receive, in a first detector, the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and to identify, using a controller, the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector. Embodiment 37. A method for mixing a liquid in a flat, disc-shaped cartridge, the method comprising: introducing a liquid into a mixing chamber of the cartridge through a channel extending radially inwards from the mixing chamber, the mixing chamber including a mixing ball inside; rotate the cartridge in a first circumferential direction to propel the liquid radially outwards and retain the liquid in the mixing chamber; intermittently accelerate and decelerate the rotation of the cartridge to recursively move the mixing ball back and forth through the mixing chamber. Embodiment 38. The method according to embodiment 37, wherein the mixing chamber is provided with lyophilized reagents before the introduction of the liquid and wherein the mixing resulting from the movement of the mixing ball through the mixing chamber releases gas from the lyophilized reagents into the liquid. Embodiment 39. The method according to embodiment 38, wherein the released gas hQ^n Ln / Lznz / E / YiAi moves radially into and out of the mixing chamber. Embodiment 40. The method according to any of embodiments 37 to 39, wherein the mixing ball is not magnetic. Implementation 41. A method for detecting the presence of a target analyte in a sample, the method comprising: introducing the sample into a cartridge, the cartridge including a liquid system for isolating the target analyte from the sample and collecting an amount of a first marker that is proportional to an amount of the target analyte in the sample, the liquid system comprising: a liquid line comprising a liquid inlet pathway configured to receive a liquid, a first chamber and liquid outlet pathway, a detection chamber, and a connecting passage between the first chamber and the detection chamber; transfer the target analyte to the first chamber; pump liquid along the liquid line and into the first chamber while maintaining an air mass in the connecting passage; transfer the target analyte to the detection chamber; direct electromagnetic radiation from a first source of electromagnetic radiation to form a consultation space within the cartridge detection chamber; to receive, in a first detector, the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and to identify, using a controller, the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector. Implementation 42. The method in accordance with implementation 41, wherein the connection step extends directly from the first camera. hQ^n Ln / Lznz / E / YiAi Implementation 43. The method according to implementation 41 or 42, wherein the connection step extends directly to the detection chamber. Embodiment 44. The method according to any of embodiments 41 to 43, further comprising transferring the target analyte to the detection chamber, wherein the target analyte is carried to the detection chamber by means of paramagnetic beads that are transported using magnets. Embodiment 45. The method according to embodiment 44, wherein the detection chamber is arranged in an elution line including an elution inlet path and an elution outlet path, and wherein the method further includes pumping elution fluid into the elution line to separate the target analyte from the paramagnetic beads. Embodiment 46. The method according to any of embodiments 41 to 45, wherein the liquid is pumped along the liquid line by introducing liquid into the liquid line at the liquid inlet path and extracting liquid from the liquid line at the liquid outlet path. Implementation 47. A method for detecting the presence of a target analyte in a sample, the method comprising: introducing the sample into a cartridge, the cartridge including a liquid system for isolating the target analyte from the sample and collecting an amount of a first marker that is proportional to an amount of the target analyte in the sample, the liquid system comprising: a first chamber, a second chamber, and a channel extending from the first chamber to the second chamber; attach the target analyte to a substrate composed of paramagnetic beads; place a first magnet near a first cartridge surface and adjacent to the first chamber; facilitating the relative movement of the first magnet and the cartridge to extract the paramagnetic beads from the suspension and form a bolus, the relative movement being facilitated by at least one of the movements of the first magnet through the first surface or the rotation of the cartridge; direct electromagnetic radiation from a first source of electromagnetic radiation to form a consultation space within the cartridge; to receive, in a first detector, the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and to identify, using a controller, the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector. Embodiment 48. The method according to embodiment 47, further comprising facilitating the relative movement of the first magnet and the cartridge to transfer the paramagnetic beads and the target analyte from the first chamber to a second chamber Implementation 49. The method according to implementation 47 or 48, further comprising performing a washing operation in the second chamber to isolate the target analyte from other constituents of the sample. Implementation 50. The method according to Implementation 49, wherein the washing operation includes: move the first magnet away from the first surface of the cartridge so that the paramagnetic beads are dispersed in the second chamber; move a second magnet towards a second surface of the cartridge so that the paramagnetic beads accumulate near the second magnet; Move the second magnet away from the second surface of the cartridge so that the paramagnetic beads are dispersed in the second chamber; and move the first magnet towards the first surface of the cartridge so that the paramagnetic beads accumulate near the first magnet. Implementation 51. A method for detecting the presence of a target analyte in a sample, the method comprising: introducing a sample into a cartridge, the cartridge including a liquid hQ^n Ln / Lznz / E / YiAi system for isolating the target analyte from the sample and collecting an amount of a first marker that is proportional to an amount of the target analyte in the sample, the liquid system comprising: an entrance camera, a separation area connected to the entrance camera, including an interior separation camera and an exterior separation camera, and a detection camera beyond the separation area; transfer the blood sample from the inlet chamber to the separation area; Rotate the cartridge using the centrifuge to move the red blood cells from the blood sample into the outer separation chamber and move the blood plasma into the inner separation chamber; Take an image of the blood sample in the separation area using a camera; analyze, using a controller, the image of the blood sample in the separation area to determine a position of the red blood cells within the separation area; transfer the blood plasma from the inner separation chamber to a mixing chamber; isolate the target analyte from blood plasma; transfer the target analyte to the detection chamber; direct electromagnetic radiation from a first source of electromagnetic radiation to form a consultation space within the cartridge detection chamber; to receive, in a first detector, the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and to identify, using a controller, the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first hQ^n Ln / Lznz / E / YiAi detector. Embodiment 52. The method according to embodiment 51, further comprising, in response to the determined position of the red blood cells, rotating the cartridge further using the centrifuge to move the 5 red blood cells further into the outer separation chamber. Embodiment 53. The method according to embodiment 51 or 52, further comprising analyzing, using the controller, the image of the blood sample to determine the clarity of the blood plasma in the inner separation chamber after rotating the cartridge with the centrifuge, wherein the transfer of the sample portion from the separation area to the mixing chamber is carried out in response to the clarity of the blood plasma being above a predetermined value. Embodiment 54. The method according to embodiment 53, further comprising taking an image of the blood plasma in the mixing chamber; and analyzing, using the controller, the image of the blood plasma in the mixing chamber to calculate a volume of blood plasma in the mixing chamber.

Claims

1. An analyzer system for measuring the concentration of a target analyte in a sample, the analyzer system comprising: a motor; a coupling coupled to the motor for rotation by driving the motor;a cartridge retained in the coupling and including a liquid system configured to receive a sample, isolate a target analyte from the sample, and collect an amount of a first marker that is proportional to an amount of the target analyte in the sample, the liquid system including: an inlet chamber, a mixing chamber downstream of the inlet chamber and configured to mix at least a portion of the sample to bind the target analyte with the first marker, and a washing chamber downstream of the mixing chamber and connected to the mixing chamber by a channel, wherein the washing chamber is radially offset from the mixing chamber to prevent flow of the sample into the washing chamber during a mixing process taking place in the mixing chamber;a first source of electromagnetic radiation configured to provide electromagnetic radiation to form a search space within a cartridge detection chamber; a first detector configured to detect the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and a controller configured to identify the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector.

2. The analyzer system according to claim 1, wherein a channel extending from the mixing chamber to the washing chamber includes a capillary enlargement, the capillary enlargement having a cross-sectional area expanding in the direction away from the mixing chamber.

3. The analyzer system according to claim 1, wherein the cartridge liquid system further includes a separation area disposed between the inlet chamber and the mixing chamber, the separation area including a radially inner separation chamber and a radially outer separation chamber that are connected by a narrow neck.

4. The analyzer system according to claim 3, wherein a siphon extends from the radially inward separation chamber to the mixing chamber.

5. A method for mixing a liquid in a flat, disc-shaped cartridge, the method comprising: introducing a liquid into a mixing chamber of the cartridge through a channel extending radially inwards from the mixing chamber, the mixing chamber including a mixing ball therein; rotating the cartridge in a first circumferential direction to propel the liquid radially outwards and retain the liquid in the mixing chamber; intermittently accelerating and decelerating the rotation of the cartridge to move the mixing ball back and forth recursively through the mixing chamber.

6. The method according to claim 5, wherein the mixing chamber is provided with lyophilized reagents before the introduction of the liquid and wherein the mixing resulting from the movement of the mixing ball through the mixing chamber releases gas from the lyophilized reagents into the liquid.

7. The method according to claim 6, wherein the released gas moves radially into and out of the mixing chamber.

8. The method according to claim 5, wherein the mixing ball is non-magnetic. hQ^n Ln / Lznz / E / YiAi 9. A method for detecting the presence of a target analyte in a sample, the method comprising: introducing the sample into a cartridge, the cartridge including a liquid system for isolating the target analyte from the sample and collecting an amount of a first marker that is proportional to the amount of the target analyte in the sample, the liquid system comprising: a liquid line including a liquid inlet pathway configured to receive a liquid, a first chamber and a liquid outlet pathway, a detection chamber, and a connecting passage between the first chamber and the detection chamber; transferring the target analyte to the first chamber; pumping liquid along the liquid line and into the first chamber while maintaining an air mass in the connecting passage; and transferring the target analyte to the detection chamber.directing electromagnetic radiation from a first electromagnetic radiation source to form a search space within the cartridge detection chamber; receiving, in a first detector, the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and identifying, using a controller, the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector.

10. The method according to claim 9, further comprising transferring the target analyte to the detection chamber, wherein the target analyte is carried to the detection chamber by means of paramagnetic beads that are transported using magnets.

11. The method according to claim 10, wherein the detection chamber is arranged in an elution line including an elution inlet path and an elution outlet path, and wherein the method further includes pumping elution fluid into the elution line to separate the target analyte from the paramagnetic beads.

12. The method according to claim 9, wherein the liquid is pumped along the liquid line by introducing liquid into the liquid line at the liquid inlet path and extracting liquid from the liquid line at the liquid outlet path.

13. A method for detecting the presence of a target analyte in a sample, the method comprising: introducing the sample into a cartridge, the cartridge including a liquid system for isolating the target analyte from the sample and collecting an amount of a first marker that is proportional to an amount of the target analyte in the sample, the liquid system comprising: a first chamber, a second chamber, and a channel extending from the first chamber to the second chamber; attaching the target analyte to a substrate composed of paramagnetic beads; placing a first magnet near a first surface of the cartridge and adjacent to the first chamber; facilitating relative movement of the first magnet and the cartridge to extract the paramagnetic beads from the suspension and form a bolus, the relative movement being facilitated by at least one of the movements of the first magnet through the first surface or by rotation of the cartridge;directing electromagnetic radiation from a first source of electromagnetic radiation to form a search space within the cartridge; receiving, in a first detector, the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and identifying, using a controller, the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector.

14. The method according to claim 13, further comprising facilitating the relative movement of the first magnet and the cartridge to transfer the paramagnetic beads and the target analyte from the first chamber to a second chamber.

15. The method of claim 14, further comprising performing a washing operation in the second chamber to isolate the target analyte from other constituents of the sample.

16. The method according to claim 15, wherein the washing operation includes: moving the first magnet away from the first cartridge surface so that the paramagnetic beads are dispersed in the second chamber; moving a second magnet towards a second cartridge surface so that the paramagnetic beads accumulate near the second magnet; moving the second magnet away from the second cartridge surface so that the paramagnetic beads are dispersed in the second chamber; and moving the first magnet towards the first cartridge surface so that the paramagnetic beads accumulate near the first magnet.

17. A method for detecting the presence of a target analyte in a sample, the method comprising: introducing a sample into a cartridge, the cartridge including a liquid system for isolating the target analyte from the sample and collecting an amount of a first marker that is proportional to an amount of the target analyte in the sample, the liquid system comprising: an inlet chamber, a separation area connected to the inlet chamber, the separation area including an inner separation chamber and an outer separation chamber, and a detection chamber downstream of the separation area; transferring the blood sample from the inlet chamber to the separation area; rotating the cartridge using the centrifuge to move the red blood cells from the blood sample to the outer separation chamber and move the blood plasma to the inner separation chamber;Taking an image of the blood sample in the separation area using a camera; analyzing, using a controller, the image of the blood sample in the separation area to determine the position of the red blood cells within the separation area; transferring the blood plasma from the inner separation chamber to a mixing chamber; isolating the target analyte from the blood plasma; transferring the target analyte to the detection chamber; directing electromagnetic radiation from a first electromagnetic radiation source to form a search space within the cartridge's detection chamber; receiving, in a first detector, the electromagnetic radiation emitted in the search space by the first marker if the first marker is present in the search space; and identifying, using a controller, the presence of the target analyte in the sample based on the electromagnetic radiation detected by the first detector.

18. The method according to claim 17, further comprising, in response to the determined position of the red blood cells, rotating the cartridge further using the centrifuge to move the red blood cells further into the outer separation chamber.

19. The method according to claim 17, further comprising analyzing, using the controller, the image of the blood sample to determine the clarity of the blood plasma in the inner separation chamber after rotating the cartridge with the centrifuge, wherein the transfer of the sample portion hQ^nm / Lznz / E / YiAi 88 from the separation area to the mixing chamber is carried out in response to the clarity of the blood plasma being above a predetermined value.

20. The method according to claim 17, further comprising taking an image of the blood plasma in the mixing chamber; and 5 analyzing, using the controller, the image of the blood plasma in the mixing chamber to calculate a volume of blood plasma in the mixing chamber.

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