Analyte sensor for detecting creatinine and detection method

Abstract

To provide an analyte sensor capable of monitoring creatinine inside an organism.SOLUTION: An analyte sensor comprises: a sensor tail including at least a first working electrode, a creatinine responsiveness active area placed on a front surface of the first working electrode, and a first membrane for allowing permeation of creatinine so as to cover the creatinine responsiveness active area; and an oxygen scavenger placed on the sensor tail and also in the neighborhood of the creatinine responsiveness active area. The creatinine responsiveness active area includes a first electron transfer agent, a first polymer, and a plurality of enzymes to work in cooperation to facilitate detection of creatinine, especially, an enzyme system containing creatinine amide hydrolase, creatine amidinohydrolase, and sarcosine oxidase. An oxidase enzyme functions as the oxygen scavenger, especially as glucose oxidase when detecting creatinine in a fluid containing glucose.SELECTED DRAWING: Figure 2A

Description

[Background technology]

[0001] Detection of various analytes in an individual may sometimes be essential to monitor the state of health and well-being. Deviations from normal analyte levels are often indicative of an underlying physiological condition, such as a metabolic state or disease, or exposure to a particular environmental condition. While a single analyte may be dysregulated alone for a particular physiological condition, multiple analytes may be dysregulated simultaneously due to the same physiological condition or as a result of coexisting (related) physiological conditions. When multiple analytes are dysregulated simultaneously, the degree of dysregulation may vary from analyte to analyte. Thus, each analyte must be monitored to properly assess the health status of an individual.

[0002] Periodic in vitro analyte monitoring using collected bodily fluids may be sufficient to monitor a given physiological condition for many individuals. However, in vitro analyte monitoring may be inconvenient or painful for some individuals, especially if the collection or sampling of bodily fluids is required to be performed fairly frequently (e.g., several times a day). Continuous analyte monitoring using implanted in vivo analyte sensors is a more desirable approach for individuals with severe analyte dysregulation and / or rapidly fluctuating analyte levels, but may be beneficial to other individuals due to the convenience offered. Continuous analyte monitoring allows an individual or physician to proactively address abnormal analyte levels before they have a chance to lead to more serious health effects, such as organ damage or failure. Subcutaneous, interstitial, or cutaneous analyte sensors can often provide sufficient measurement accuracy for this purpose while minimizing user discomfort.

[0003] Many analytes are interesting targets for physiological analysis if the appropriate detection chemistry can be identified. To this end, amperometric sensors configured to assay glucose in vivo have been developed and improved in recent years to aid in monitoring the health of diabetic patients. Other analytes that are commonly dysregulated in conjunction with glucose in diabetic patients include, for example, lactate, oxygen, pH, A1c, ketones, etc. Sensors configured to detect analytes that are commonly dysregulated with glucose are known, but currently have rather low accuracy.

[0004] In vivo analyte sensors are typically configured to analyze a single analyte to provide a specific analysis, often using enzymes to provide high specificity for a given analyte. Because of such analytical specificity, most current in vivo analyte sensors configured to assay glucose are ineffective at assaying other analytes that are often dysregulated along with glucose or due to dysregulated glucose levels. At best, current analyte monitoring approaches require the diabetic patient to wear two different in vivo analyte sensors, one configured to analyze glucose and the other configured to analyze another analyte of interest. Analyte monitoring approaches using multiple in vivo analyte sensors can be very inconvenient for users. Furthermore, when multiple in vivo analyte sensors are used for analyte monitoring, the equipment cost burden increases and there is a statistically high likelihood that at least one of the individual in vivo analyte sensors will fail.

[0005] Diabetic patients are often particularly susceptible to comorbidities, which may result from mismanagement of insulin levels or even from adequately managing diabetes over time. As an example, diabetic neuropathy may result from high blood glucose levels and may ultimately lead to kidney failure. Diabetic neuropathy is the leading cause of kidney failure in the United States, experienced by a significant number of diabetics within the first 10-20 years of the disease. Diagnostic tests to assess kidney function are currently based on measuring elevated creatinine levels in blood and / or urine samples. Although it is desirable to detect potential kidney failure as early as possible, current diagnostic testing approaches are typically performed over an extended period of time (months to years) to ensure that creatinine levels are persistently increased or trend upward over time. The infrequent frequency of traditional creatinine monitoring may increase the risk of developing kidney failure if abnormalities in kidney function are not detected early enough. [Brief description of the drawings]

[0006] The accompanying drawings are included to illustrate certain aspects of the present disclosure and should not be considered as exclusive embodiments. The disclosed subject matter is capable of considerable modification, alteration, combinations, and equivalents in form and function without departing from the scope of the present disclosure. [Figure 1] 1 shows a diagram of an exemplary sensing system that can incorporate an analyte sensor of the present disclosure. [Figure 2A] 1 shows an example of a cooperative enzyme system that can be used to detect creatinine according to the present disclosure. [Figure 2B] Same as above. [Figure 3A] 1 shows a cross-sectional view of an exemplary analyte sensor having an active area suitable for detecting creatinine. [Figure 3B] Same as above. [Figure 3C] Same as above. [Figure 4A]FIG. 1 shows a cross-sectional view of an exemplary analyte sensor having a single working electrode and an active area suitable for detecting creatinine and glucose. [Figure 4B] Same as above. [Figure 4C] Same as above. [Diagram 5] FIG. 1 shows a cross-sectional view of an exemplary analyte sensor having two working electrodes and an active area suitable for detecting creatinine and glucose. [Figure 6A] FIG. 1 shows a perspective view of an exemplary analyte sensor featuring electrodes arranged concentrically with respect to one another. [Figure 6B] Same as above. [Figure 6C] Same as above. [Figure 6D] Same as above. [Figure 7A] 1 shows a diagram of a membrane and a creatinine-responsive active area having an oxygen scavenger disposed thereon. [Figure 7B] Same as above. [Figure 8] 1 shows an exemplary plot of current response for three replicates of a sensor containing a creatinine-responsive active region coated with glucose oxidase when exposed to various creatinine concentrations. [Figure 9] 1 shows an exemplary plot of the current response of a single sensor containing a creatinine-responsive active region coated with glucose oxidase when exposed to various creatinine concentrations. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0007] Detailed Description The present disclosure generally describes analyte sensors that use multiple enzymes to detect one or more analytes, and more specifically, analyte sensors that use multiple enzymes to detect at least creatinine and optionally other analytes, and corresponding methods for their use.

[0008] As mentioned above, due to the common specificity of enzymes for a particular substrate or class of substrates, analyte sensors using enzymes are typically used to monitor a single analyte, such as glucose. Other analytes can also be monitored if the appropriate detection chemistry can be identified. Monitoring multiple analytes can be complicated by the need to use a corresponding number of analyte sensors to detect each analyte individually. This approach can be problematic or undesirable, especially when monitoring multiple analytes in vivo, due to issues such as the cost of multiple analyte sensors, user discomfort when wearing multiple analyte sensors, and an increased statistical probability of failure of an individual analyte sensor.

[0009] Glucose-responsive analyte sensors are a well-studied and still evolving field to help diabetic patients better manage their health. Despite the prevalence of comorbidities in diabetic patients, sensor chemistries suitable for in vivo monitoring of other analytes that are often dysregulated along with glucose have lagged significantly behind the more developed glucose sensing chemistries. For example, creatinine may be an analyte of particular interest for monitoring in individuals prone to renal failure, particularly diabetic patients at risk for diabetic neuropathy.

[0010] The present disclosure provides an analyte sensor that is responsive to creatinine. Specifically, the present disclosure provides an analyte sensor that can be worn on the body for continuous or near-continuous in vivo monitoring of creatinine levels. Analysis of creatinine levels using the analyte sensors disclosed herein may provide an individual or a health care provider with a more accurate indication of kidney function over time than is possible with periodic ex vivo laboratory measurements. Analyzing creatinine levels in accordance with the present disclosure may enable early medical intervention to limit potential kidney damage and improve an individual's overall health outcomes.

[0011] Electrochemical detection of creatinine using a single enzymatic reaction is not feasible due to the lack of known enzymes that can directly transfer electrons from creatinine to the working electrode. The present disclosure remedies this deficiency by providing a sensor chemistry suitable for detecting creatinine with good response stability over a wide creatinine concentration range. In particular, the present disclosure utilizes an enzyme system that includes multiple enzymes that can act in concert to facilitate the detection of creatinine. As used herein, the term "in concert" refers to a coupled enzyme reaction in which the product of a first enzyme reaction serves as a substrate for a second enzyme reaction, which serves as the basis for measuring the concentration of the substrate (analyte) reacted during the first enzyme reaction. Although defined in terms of two coupled enzyme reactions, it should be understood that in some cases, three or more enzyme reactions may be coupled in a similar manner. For example, the product of a first enzyme reaction may serve as a substrate for a second enzyme reaction, which may serve as a substrate for a third enzyme reaction, which serves as the basis for measuring the concentration of the substrate (analyte) reacted during the first enzyme reaction. As described further below, a suitable enzyme system for detecting creatinine according to the present disclosure uses three enzymes acting in concert with a fourth enzyme or other oxygen scavenger to facilitate oxygen clearance that does not directly participate in the concerted enzymatic reaction, but instead prevents undesirable side reactions with oxygen from occurring.

[0012] When a single enzyme cannot facilitate detection, such as in the case of creatinine, it may be desirable to utilize two or more enzymes acting in concert with each other to detect the analyte of interest. Circumstances in which a single enzyme may be ineffective in facilitating detection of an analyte include, for example, situations in which it is inhibited by one or more reaction products or cannot cycle between oxidized and reduced states when placed in an analyte sensor, and / or where no enzyme is known to facilitate the desired reaction pathway required for detection to facilitate detection. In the case of creatinine, the enzymatic conversion of creatinine to creatine occurs hydrolytically and does not result in a change in oxidation state to provide a current to the working electrode to facilitate detection of this analyte. An enzyme system including multiple enzymes acting in concert according to the disclosure herein may alleviate this difficulty.

[0013] The creatinine sensor disclosed herein may be advantageous for monitoring creatinine levels (and kidney function) in individuals potentially at risk for kidney damage or failure, but may be particularly beneficial for diabetic individuals due to the prevalence of diabetic neuropathy. While monitoring creatinine levels alone may be beneficial, it is also possible for diabetic patients to monitor both glucose and creatinine levels to improve health outcomes, especially given that glucose monitoring is already routinely performed by diabetic patients. The present disclosure provides for monitoring both glucose and creatinine using one or more in vivo analyte sensors responsive to each analyte, and in a particularly advantageous configuration, a single analyte sensor responsive to both analytes in vivo may be used. Advantageously and surprisingly, analyte sensors incorporating both glucose and creatinine sensing functions on a single sensor tail may be fabricated using the disclosure herein.

[0014] As further described below with reference to Figures 2A and 2B, the creatinine-responsive active area of ​​the present disclosure can utilize an oxygen scavenger to facilitate detection of creatinine using the enzyme system shown therein. An oxidase enzyme can function as an oxygen scavenger in certain sensor configurations. Glucose oxidase may be a particularly advantageous oxygen scavenger since glucose is widely present in bodily fluids that also contain creatinine, where glucose can function as a reagent to remove oxygen (see reaction 1 below). The oxygen scavenger can be electrically isolated from the creatinine-responsive active area by a membrane so that it does not generate a signal at the working electrode with the creatinine-responsive active area (i.e., in removing oxygen by promoting an oxidation reaction). To facilitate effective oxygen removal within the creatinine-responsive active area, the oxygen scavenger can be disposed on the membrane. In addition to being disposed on the membrane, the oxygen scavenger may be disposed at a second location on the sensor tail remote from the membrane, where the remote oxygen scavenger may function differently at the remote location (e.g., by facilitating glucose detection at the glucose-responsive active area). Depending on how and where the remote oxygen scavenger is disposed, the oxygen scavenger may be active or inactive to facilitate detection of another analyte, particularly glucose, in addition to its oxygen scavenging function. If inactive to facilitate glucose detection, glucose oxidase may be electrically isolated from the working electrode, such that the oxidation reaction (oxygen scavenging) promoted by this enzyme does not result in current generation at the working electrode. If glucose oxidase is active for both facilitating glucose detection and oxygen scavenging, glucose oxidase may be present in a glucose-responsive active area disposed on a second working electrode or disposed on a working electrode with a creatinine-responsive active area, resulting in separate signals from each. Strategies for placing both creatinine- and glucose-responsive active regions on a single sensor tail are discussed further below.

[0015] Even when the appropriate detection chemistry is known, incorporating two different types of active regions into a single analyte sensor may not be straightforward. Analyte sensors often use a membrane covering the active region to act as a mass transport limiting membrane and / or to improve biocompatibility. Using a mass transport limiting membrane to limit the access of the analyte to the active region can avoid overloading (saturation) of the sensor, thereby improving detection performance and accuracy. When a single analyte sensor is used to assay multiple analytes, different permeability values ​​may be exhibited by various analytes passing through a given mass transport limiting membrane, and the sensitivity of each analyte may vary greatly. Incorporating different mass transport limiting membranes into each active region may be problematic in some cases. Surprisingly and advantageously, glucose and creatinine may be successfully analyzed using mass transport limiting membranes that are compositionally the same at each location, thereby simplifying the manufacture of analyte sensors capable of detecting both analytes.

[0016] Before describing the analyte sensors of the present disclosure in more detail, a brief overview of suitable in vivo analyte sensor configurations and sensor systems using analyte sensors is provided to allow a better understanding of the embodiments of the present disclosure. FIG. 1 shows a diagram of an exemplary sensing system that may incorporate the analyte sensors of the present disclosure, specifically analyte sensors including creatinine-responsive active regions and optionally glucose-responsive active regions. As shown, the sensing system 100 includes a sensor control device 102 and a reader device 120 configured to communicate with each other via a local communication path or link that may be wired or wireless, unidirectional or bidirectional, and encrypted or unencrypted. The reader device 120 may, according to some embodiments, configure an output medium for displaying analyte concentrations and alerts or notifications determined by the sensor 104 or its associated processor, as well as allowing for one or more user inputs. The reader device 120 may be a general-purpose smartphone or a dedicated electronic reader instrument. Although only one reader device 120 is shown, in certain cases, there may be multiple reader devices 120. The reader device 120 may also communicate with the remote terminal 170 and / or the trusted computer system 180 via communication paths / links 141 and / or 142, respectively, which may also be wired or wireless, unidirectional or bidirectional, and encrypted or unencrypted. Additionally or alternatively, the reader device 120 may communicate with a network 150 (e.g., a cellular network, the Internet, or a cloud server) via communication path / link 151. The network 150 may be further communicatively connected to the remote terminal 170 via communication path / link 152 and / or to the trusted computer system 180 via communication path / link 153. Alternatively, the sensor 104 may communicate directly with the remote terminal 170 and / or the trusted computer system 180 without the presence of the intervening reader device 120.For example, the sensor 104 may communicate with the remote terminal 170 and / or the trusted computer system 180 via a direct communication link to the network 150, according to some embodiments, as described in U.S. Patent Application Publication No. 2011 / 0213225, which is incorporated herein by reference in its entirety. Any suitable electronic communication protocol, such as near field communication (NFC), radio frequency identification (RFID), BLUETOOTH or BLUETOOTH low energy protocols, WiFi, etc., may be used for each of the communication paths or links. The remote terminal 170 and / or the trusted computer system 180 may be accessible by individuals other than the primary user who are interested in the user's analyte levels, according to some embodiments. The reader device 120 may include a display 122 and an optional input component 121. The display 122 may include a touch screen interface, according to some embodiments.

[0017] The sensor control device 102 includes a sensor housing 103 that can house circuitry and a power source for operating the sensor 104. Optionally, the power source and / or active circuitry may be omitted. A processor (not shown) may be communicatively connected to the sensor 104, the processor being physically located within the sensor housing 103 or the reader device 120. The sensor 104 protrudes from an underside of the sensor housing 103 and extends through an adhesive layer 105. The adhesive layer 105 is adapted to adhere the sensor housing 103 to a tissue surface, such as skin, according to some embodiments.

[0018] The sensor 104 is adapted to be at least partially inserted into a tissue of a subject, such as into the dermis or subcutaneous layer of the skin. The sensor 104 may include a sensor tail of sufficient length to insert to a desired depth into a given tissue. The sensor tail may include at least one working electrode and a creatinine-responsive active area disposed thereon. Optionally, a glucose-responsive active area may be disposed on the sensor tail to facilitate detection of the analyte, optionally in combination with a second working electrode. A counter electrode may be present in combination with the at least one working electrode. Particular electrode configurations on the sensor tail are described in more detail below with reference to FIGS. 3A-7B.

[0019] As described in more detail below, the creatinine-responsive active region and optional glucose-responsive active region, if present, can be covered by at least one mass transport limiting membrane. The glucose-responsive active region, if present, can include a glucose-responsive enzyme. The mass transport limiting membrane can also cover an oxygen scavenger (e.g., glucose oxidase), in which case the oxygen scavenger can be interposed between separate membrane layers.

[0020] The creatinine-responsive active region may include an enzyme system including multiple enzymes that can act in concert to facilitate detection of creatinine, as described below with reference to Figures 2A and 2B. According to various embodiments, the creatinine-responsive active region, and, if present, the glucose-responsive active region, may include a polymer to which an enzyme is covalently attached. Glucose oxidase located outside the glucose-responsive active region may also be covalently attached to a polymer in the analyte sensors disclosed herein. According to the present disclosure, creatinine and optionally glucose may be monitored in any biological fluid of a subject, such as dermal fluid, interstitial fluid, plasma, blood, lymphatic fluid, synovial fluid, cerebrospinal fluid, saliva, bronchoalveolar lavage fluid, amniotic fluid, etc. In certain embodiments, the analyte sensors of the present disclosure may be adapted to assay dermal fluid or interstitial fluid to determine the concentration of creatinine and / or glucose in vivo.

[0021] With further reference to FIG. 1 , the sensor 104 may automatically transfer data to the reader device 120. For example, analyte concentration data (i.e., creatinine and / or glucose concentration) may be stored in memory as the data is acquired until it is transmitted (e.g., every minute, every five minutes, or at other predefined time periods) and may be communicated automatically and periodically, such as at a specific frequency or after a specific time period has elapsed. In other embodiments, the sensor 104 may communicate with the reader device 120 in a non-automatic manner rather than according to a set schedule. For example, data may be communicated from the sensor 104 using RFID technology when the sensor electronics come within communication range of the reader device 120. The data may remain stored in the memory of the sensor 104 until communicated to the reader device 120. Thus, the user need not be in constant proximity to the reader device 120, but may instead upload data at a convenient time. In still other embodiments, a combination of automatic and non-automatic data transfer may be implemented. For example, data transfer may continue automatically until the reader device 120 is no longer within communication range of the sensor 104.

[0022] An introducer may be temporarily present to facilitate introduction of the sensor 104 into the tissue. In an exemplary embodiment, the introducer may include a needle or similar sharp. It should be appreciated that in alternative embodiments, other types of introducers, such as a sheath or blade, may be present. More specifically, the needle or other introducer may be temporarily present in the vicinity of the sensor 104 prior to tissue insertion and then withdrawn. While present, the needle or other introducer may facilitate insertion of the sensor 104 into the tissue by opening an access path for the sensor 104 to follow. For example, according to one or more embodiments, the needle may facilitate penetration of the epidermis as an access path to the dermis to allow implantation of the sensor 104 to occur. After opening the access path, the needle or other introducer may be withdrawn so as not to present a sharps hazard. In an exemplary embodiment, a suitable needle may be solid or hollow, beveled or non-beveled, and / or circular or non-circular in cross section. In more particular embodiments, suitable needles may be comparable in cross-sectional diameter and / or tip design to acupuncture needles, which may have a cross-sectional diameter of about 250 microns. However, it should be recognized that suitable needles may have larger or smaller cross-sectional diameters as required for a particular application.

[0023] In some embodiments, the tip of the needle (while present) may be angled on the end of the sensor 104 such that the needle penetrates the tissue first, opening an access path for the sensor 104. In other exemplary embodiments, the sensor 104 may reside within a lumen or channel of the needle, which similarly opens an access path for the sensor 104. In either case, the needle is then withdrawn after facilitating insertion of the sensor.

[0024] A suitable enzyme system that can be used to detect creatinine according to the disclosure herein is described in further detail with reference to Figures 2A and 2B. As shown, creatinine can react reversibly and hydrolytically to form creatine in the presence of creatinine amidohydrolase (CNH). Creatine can then undergo catalytic hydrolysis to form sarcosine in the presence of creatine amidinohydrolase (CRH). Neither of these reactions generates an electron flow (e.g., oxidation or reduction) to provide a basis for electrochemical detection of creatinine.

[0025] As further shown in Figures 2A and 2B, sarcosine produced by the hydrolysis of creatine can undergo oxidation in the presence of oxidized sarcosine oxidase (SOX-ox) to form glycine and formaldehyde, thereby generating reduced sarcosine oxidase (SOX-red) in the process. Hydrogen peroxide can also be generated in the presence of oxygen (Figure 2B). The reduced sarcosine oxidase can then undergo reoxidation in the presence of an oxidized electron transfer agent (e.g., Os(III)), thereby generating the corresponding reduced electron transfer agent (e.g., Os(II)) and delivering electron flow to the working electrode.

[0026] Oxygen may interfere with the concerted series of reactions used to detect creatinine according to the present disclosure. Specifically, as shown in FIG. 2B, reduced sarcosine oxidase can react with oxygen to reform the corresponding oxidized form of the enzyme, but without exchanging electrons with the electron transfer agent. When the reaction with oxygen occurs, all of the enzymes remain active, but no electrons flow to the working electrode. Without being bound by theory or mechanism, it is believed that the competitive reaction with oxygen is due to kinetic effects; that is, the oxidation of reduced sarcosine oxidase by oxygen is believed to occur faster than the oxidation promoted by the electron transfer agent. Hydrogen peroxide is also formed in the presence of oxygen.

[0027] A preferred reaction pathway for facilitating the detection of creatinine is shown in FIG. 2A. The oxidation of reduced sarcosine oxidase may be promoted by including an oxygen scavenger near the enzyme system. As noted above, a variety of oxygen scavengers and their placement may be suitable, including oxidase enzymes such as glucose oxidase. Small molecule oxygen scavengers may also be suitable, but may be completely consumed before the sensor's lifetime is fully exhausted. In contrast, the enzyme can undergo reversible oxidation and reduction, thereby increasing the sensor's lifetime. By preventing the oxidation of reduced sarcosine oxidase by oxygen, the electron exchange reaction with the electron transfer agent occurs more slowly, thereby allowing a current to be generated at the working electrode. The magnitude of the current generated is proportional to the amount of creatinine initially reacted.

[0028] The oxygen scavenger used to facilitate the desired reaction pathway in FIG. 2A may be an oxidase enzyme in any embodiment of the present disclosure. Any oxidase enzyme may be used to facilitate oxygen removal near the enzyme system, so long as the appropriate substrate for the enzyme is also present in the creatinine-containing fluid, thereby providing a reagent for reaction with oxygen in the presence of the oxidase enzyme. Oxidase enzymes that may be suitable for oxygen removal in the present disclosure include, but are not limited to, glucose oxidase, lactate oxidase, xanthine oxidase, and the like. Glucose oxidase may be a particularly suitable oxidase enzyme for use in the present disclosure, due to the ready availability of glucose in various bodily fluids. Reaction 1 below illustrates the enzymatic reaction facilitated by glucose oxidase to remove oxygen.

[0029] β-D-glucose + O2 -- → D-glucono-1,5-lactone + H2O2 Reaction 1 The concentration of bioavailable lactate is lower than that of glucose, but is still sufficient to facilitate oxygen removal.

[0030] An oxidase enzyme, such as glucose oxidase, can be located anywhere suitable for facilitating oxygen removal in the analyte sensors disclosed herein. For example, glucose oxidase can be located on the sensor tail such that it is functional and / or non-functional for facilitating glucose detection. If non-functional for facilitating glucose detection, glucose oxidase can be located on the sensor tail to prevent electrons generated during glucose oxidation from reaching the working electrode that receives electrons generated upon oxidation of sarcosine. Approaches for electrically isolating glucose oxidase from the working electrode are addressed in more detail below. If functional for facilitating glucose detection, glucose oxidase can be located in a glucose-responsive active area on the working electrode such that, in addition to scavenging oxygen near the creatinine-responsive active area, electrons generated during glucose oxidation are received by the working electrode. The working electrode having a glucose-responsive active area on its surface can be the same working electrode or a different working electrode as the one having the creatinine-responsive active area. Suitable approaches for locating glucose oxidase within the glucose-responsive active area on a particular working electrode are also discussed below herein. Any combination of the aforementioned approaches for disposing glucose oxidase on the sensor tail can be used in the analyte sensors disclosed herein.

[0031] An alternative detection strategy to that shown in Figure 2A may omit the glucose oxidase, the membrane separating it from the working electrode, and the electron transfer agent. In such a detection approach, creatinine amidohydrolase, creatine amidinohydrolase, and sarcosine oxidase act in concert as shown, with oxygen promoting the formation of hydrogen peroxide and interconverting the oxidized and reduced forms of sarcosine oxidase. Hydrogen peroxide is detected at the working electrode and may serve as the basis for assaying creatinine with this type of sensor configuration.

[0032] The analyte sensors disclosed herein feature at least a creatinine-responsive active area on a working electrode in combination with at least one additional electrode, which may be a counter electrode, a reference electrode, and / or a counter / reference electrode. Analyte sensors featuring both a creatinine-responsive active area and a glucose-responsive active area can incorporate the creatinine-responsive active area and the glucose-responsive active area on separate working electrodes or on the same working electrode. Exemplary configurations of each are discussed below.

[0033] Sensor configurations featuring a creatinine-responsive active region, but not a glucose-responsive active region, may use a two-electrode or three-electrode detection motif, as further described herein with reference to Figures 3A-3C. Sensor configurations featuring both creatinine-responsive and glucose-responsive active regions on separate working electrodes or on the same working electrode are subsequently described separately with reference to Figures 4A-6D. Sensor configurations having multiple working electrodes may be particularly advantageous for incorporating both creatinine-responsive and glucose-responsive active regions within the same sensor tail, since the signal contribution from each active region can be more easily determined.

[0034] When a single working electrode is present in the analyte sensor, a three-electrode sensor configuration may include a working electrode, a counter electrode, and a reference electrode. A related two-electrode sensor configuration may include a working electrode and a second electrode, which may function as both the counter electrode and the reference electrode (i.e., a counter / reference electrode). The various electrodes may be at least partially stacked (layered) on one another and / or laterally spaced apart from one another on the sensor tail. A suitable sensor configuration may be substantially flat or substantially cylindrical in shape, with the creatinine-responsive active area and the optional glucose-responsive active area being laterally spaced apart on the working electrode. In any sensor configuration disclosed herein, the various electrodes may be electrically insulated from one another by a dielectric material or similar insulator.

[0035] Analyte sensors featuring multiple working electrodes may similarly include at least one additional electrode. If one additional electrode is present, the one additional electrode may function as a counter / reference electrode for each of the multiple working electrodes. If two additional electrodes are present, one of the additional electrodes may function as a counter electrode for each of the multiple working electrodes, and the other of the additional electrodes may function as a reference electrode for each of the multiple working electrodes.

[0036] 3A shows a diagram of an exemplary two-electrode analyte sensor configuration suitable for use in the present disclosure. As shown, the analyte sensor 200 includes a substrate 212 disposed between a working electrode 214 and a counter / reference electrode 216. Alternatively, the working electrode 214 and the counter / reference electrode 216 may be disposed on the same side of the substrate 212 with a dielectric material interposed therebetween (configuration not shown). A creatinine-responsive active region 218 is disposed as at least one layer on at least a portion of the working electrode 214. The creatinine-responsive active region 218 may include multiple spots or a single spot configured for detection of creatinine, as described further herein.

[0037] 3A, the membrane 220, according to some embodiments, covers at least the creatinine-responsive active area 218 and can optionally cover some or all of the working electrode 214 and / or counter / reference electrode 216, or the entire analyte sensor 200. One or both sides of the analyte sensor 200 may be covered with the membrane 220. The membrane 220 may include one or more polymeric membrane materials capable of restricting analyte flux to the active area 218 (i.e., the membrane 220 is a mass transport limiting membrane having some permeability to creatinine). The composition and thickness of the membrane 220 may be varied to facilitate a desired creatinine flux to the creatinine-responsive active area 218, thereby providing a desired signal strength and stability. The analyte sensor 200 may be operable to assay creatinine by any of the following electrochemical detection techniques: coulometric, amperometric, voltammetric, or potentiometric.

[0038] 3B and 3C show diagrams of an exemplary three-electrode analyte sensor configuration that is also suitable for use as disclosed herein. The three-electrode analyte sensor configuration can be similar to that shown for the analyte sensor 200 of FIG. 3A, except for the inclusion of an additional electrode 217 in the analyte sensors 201 and 202 (FIGS. 3B and 3C). With the additional electrode 217, the counter / reference electrode 216 can function as either a counter electrode or a reference electrode, and the additional electrode 217 performs the other electrode function. The working electrode 214 continues to perform its original function. The additional electrode 217 can be disposed on either the working electrode 210 or the electrode 216, with a dielectric separating layer therebetween. For example, as shown in FIG. 2B, the dielectric layers 219a, 219b, and 219c separate the electrodes 214, 216, and 217 from each other and provide electrical insulation. Alternatively, at least one of the electrodes 214, 216, and 217 may be disposed on opposite sides of the substrate 212, as shown in FIG. 3C. Thus, in some embodiments, the electrode 214 (working electrode) and the electrode 216 (counter electrode) may be disposed on opposite sides of the substrate 212, and the electrode 217 (reference electrode) may be disposed on one of the electrodes 214 or 216 and separated therefrom by a dielectric material. A reference material layer 230 (e.g., Ag / AgCl) may be present on the electrode 217, and the location of the reference material layer 230 is not limited to that shown in FIGS. 2B and 2C. Similar to the sensor 200 shown in FIG. 3A, the creatinine-responsive active area 218 of the analyte sensors 201 and 202 may include multiple spots or a single spot. Additionally, analyte sensors 201 and 202 may be operable to assay creatinine by any of the following electrochemical detection techniques: coulometric, amperometric, voltammetric, or potentiometric.

[0039] Similar to analyte sensor 200, membrane 220 may also cover creatinine-responsive active area 218, as well as other sensor components, in analyte sensors 201 and 202, thereby functioning as a mass transport limiting membrane. In some embodiments, additional electrode 217 may be covered with membrane 220. Although in FIGS. 3B and 2C, all of electrodes 214, 216, and 217 are depicted as being covered with membrane 220, it should be appreciated that in some embodiments, only working electrode 214 may be covered. Furthermore, the thickness of membrane 220 on each of electrodes 214, 216, and 217 may be the same or different. As in the two-electrode analyte sensor configuration (FIG. 3A), one or both sides of analyte sensors 201 and 202 may be covered with membrane 220 in the sensor configuration of FIGS. 3B and 2C, or the entire analyte sensors 201 and 202 may be covered. Therefore, the three-electrode sensor configurations shown in Figures 3B and 3C should be understood as non-limiting examples of embodiments disclosed herein, with alternative electrode and / or layer configurations falling within the scope of the present disclosure.

[0040] Analyte sensors having both creatinine- and glucose-responsive active areas on a single working electrode or on multiple working electrodes are described in further detail with reference to Figures 4A-6D.

[0041] FIG 4A shows an exemplary configuration of a sensor 203 having a single working electrode with both creatinine-responsive active regions and glucose-responsive active regions disposed thereon. FIG 4A is similar to FIG 3A except for the presence of two active regions on the working electrode 214: creatinine-responsive active region 218a and glucose-responsive active region 218b. These active regions are laterally spaced apart from one another on the surface of the working electrode 214. Active regions 218a and 218b may include multiple spots or single spots configured for detection of each analyte. The composition of membrane 220 may vary in active regions 218a and 218b or may be compositionally the same.

[0042] Figures 4B and 4C show cross-sectional views of exemplary three-electrode sensor configurations for sensors 204 and 205, respectively, each featuring a single working electrode with both creatinine-responsive active area 218a and glucose-responsive active area 218b disposed thereon. Figures 4B and 4C are otherwise similar to Figures 3B and 3C and may be better understood with reference thereto. As with Figure 4A, the composition of membrane 220 may vary in active areas 218a and 218b or may be compositionally the same.

[0043] Exemplary sensor configurations having multiple working electrodes, specifically two working electrodes, are described in further detail with reference to Figures 5-6D. While the following description is primarily directed to sensor configurations having two working electrodes, it should be understood that the disclosure herein may be extended to incorporate three or more working electrodes. Additional working electrodes may be used to provide the analyte sensor with additional sensing capabilities beyond just creatinine and glucose sensing.

[0044] 5 illustrates a cross-sectional view of an exemplary analyte sensor configuration having two working electrodes, a reference electrode, and a counter electrode suitable for use as disclosed herein. As shown, analyte sensor 300 includes working electrodes 304 and 306, respectively, disposed on opposing sides of substrate 302. Creatinine-responsive active area 310a is disposed on the surface of working electrode 304, and glucose-responsive active area 310b is disposed on the surface of working electrode 306. Counter electrode 320 is electrically insulated from working electrode 304 by dielectric layer 322, and reference electrode 321 is electrically insulated from working electrode 306 by dielectric layer 323. Outer dielectric layers 330 and 332 are disposed on reference electrode 321 and counter electrode 320, respectively. A membrane 340 can cover at least active areas 310a and 310b according to various embodiments, and other components of analyte sensor 300, or the entire analyte sensor 300, may also be optionally covered with membrane 340. Again, membrane 340 may be compositionally varied in active regions 310a and 310b as desired to provide appropriate permeability values ​​for separately regulating analyte flux at each location.

[0045] Alternative sensor configurations having multiple working electrodes and different from the configuration shown in Figure 5 may feature counter / reference electrodes instead of separate counter and reference electrodes 320, 321, and / or different layer and / or film arrangements than those explicitly shown. For example, the arrangement of counter electrode 320 and reference electrode 321 can be reversed from that shown in Figure 5. Furthermore, working electrodes 304 and 306 do not necessarily have to be on opposing sides of substrate 302 in the manner shown in Figure 4.

[0046] It should be understood that suitable sensor configurations may feature electrodes that are substantially planar in nature, but sensor configurations featuring non-planar electrodes may also be advantageous and particularly suitable for use in the present disclosure. In particular, substantially cylindrical electrodes arranged concentrically with respect to one another may facilitate deposition of a mass transport limiting membrane, as described herein below. Figures 6A-6D show perspective views of an analyte sensor featuring two working electrodes arranged concentrically with respect to one another. It should be understood that sensor configurations having a concentric electrode arrangement, but lacking a second working electrode, are also possible in the present disclosure.

[0047] 6A shows a perspective view of an exemplary sensor configuration in which multiple electrodes are substantially cylindrical and concentrically arranged around one another around a central substrate. As shown, the analyte sensor 400 includes a central substrate 402 around which all of the electrodes and dielectric layers are concentrically arranged around one another. In particular, a working electrode 410 is disposed on a surface of the central substrate 402, and a dielectric layer 412 is disposed on a portion of the working electrode 410 distal to the sensor tip 404. A working electrode 420 is disposed on the dielectric layer 412, and a dielectric layer 422 is disposed on a portion of the working electrode 420 distal to the sensor tip 404. A counter electrode 430 is disposed on the dielectric layer 422, and a dielectric layer 432 is disposed on a portion of the counter electrode 430 distal to the sensor tip 404. A reference electrode 440 is disposed on the dielectric layer 432, and a dielectric layer 442 is disposed on a portion of the reference electrode 440 distal to the sensor tip 404. As such, the exposed surfaces of working electrode 410 , working electrode 420 , counter electrode 430 , and reference electrode 440 are spaced apart from one another along the longitudinal axis B of analyte sensor 400 .

[0048] Continuing to refer to FIGURE 6A, creatinine-responsive active area 414a and glucose-responsive active area 414b are disposed on the exposed surfaces of working electrodes 410 and 420, respectively, thereby allowing contact with a fluid for sensing creatinine and / or glucose. Although active areas 414a and 414b are depicted as three separate spots in FIGURE 6A, it should be understood that there may be fewer or more than three spots in alternative sensor configurations. Additionally, the arrangement of creatinine-responsive active area 414a and glucose-responsive active area 414b may be reversed from that shown in FIGURE 6A.

[0049] In Figure 6A, the sensor 400 is partially covered with a membrane 450 on the working electrodes 410 and 420 and on the active areas 414a and 414b disposed thereon. Figure 6B shows an alternative sensor configuration in which substantially the entire sensor 401 is covered with a membrane 450. The membrane 450 may be the same on the active areas 414a and 414b or may be compositionally different.

[0050] It should be further understood that the arrangement of the various electrodes in Figures 6A and 6B may differ from that explicitly shown. For example, the positions of the counter electrode 430 and the reference electrode 440 may be reversed from the configuration shown in Figures 6A and 6B. Similarly, the positions of the working electrodes 410 and 420 are not limited to those explicitly shown in Figures 6A and 6B. Figure 6C illustrates an alternative sensor configuration to that shown in Figure 6B, where the sensor 405 includes the counter electrode 430 and the reference electrode 440 located more proximally to the sensor tip 404 and the working electrodes 410 and 420 located more distally to the sensor tip 404. A sensor configuration in which the working electrodes 410 and 420 are located more distally to the sensor tip 404 may be advantageous by providing a larger surface area for deposition of the active regions 414a and 414b (five separate sensing spots exemplarily shown in Figure 6C), which may facilitate increased signal strength in some cases.

[0051] While Figures 6A-6C each show a sensor configuration supported on a central substrate 402, it should be understood that alternative sensor configurations may be supported on electrodes instead and lack a central substrate 402. In particular, the innermost concentric electrode may be utilized to support the other electrodes and dielectric layers. Figure 6D shows an alternative sensor configuration to that shown in Figure 6C, where sensor 406 does not include a central substrate 402, and counter electrode 430 is the innermost concentric electrode, used to sequentially position reference electrode 440, working electrodes 410 and 420, and dielectric layers 432, 442, 412, and 422 thereon. It should again be understood that other electrode and dielectric layer configurations may be used in sensor configurations lacking a central substrate 402, and in different position configurations, in light of the disclosure herein. As such, the sensor configuration shown in Figure 6D should be considered exemplary and non-limiting in nature.

[0052] As described above, an oxygen scavenger can be placed near the creatinine-responsive active region to promote oxidation of the reduced sarcosine oxidase using an electron transfer agent instead of oxygen. Oxidase enzymes, particularly glucose oxidase, can be used for this purpose in various sensor configurations disclosed herein. When only the creatinine-responsive active region is present, the glucose oxidase that is not functional for glucose detection can be located near the creatinine-responsive active region. When both the creatinine-responsive active region and the glucose-responsive active region are present, the glucose oxidase in the glucose-responsive active region can be effectively promoted to remove oxygen, optionally in combination with the glucose oxidase that is not functional for glucose detection.

[0053] An exemplary placement of glucose oxidase that is not functional for glucose detection relative to a creatinine-responsive active area is shown in Figures 7A and 7B. In particular, Figures 7A and 7B show a diagram illustrating the placement of glucose oxidase 407 on a membrane 409 that covers a creatinine-responsive active area 403 disposed on a working electrode 500. The membrane 409 electrically isolates the glucose oxidase 407 from the working electrode 500, so that electrons generated upon oxidizing glucose are not transferred to the working electrode 500 to limit oxygen exposure. The membrane 408 then covers the glucose oxidase 407 and provides it with a mass transport limiting function. The membranes 408 and 409 can be compositionally the same in various embodiments of the present disclosure. 7A shows glucose oxidase 407 disposed directly on the creatinine-responsive active region 403, it should be understood that the creatinine-responsive active region 403 and glucose oxidase 407 can be laterally spaced apart from one another so long as the glucose oxidase 407 is inhibited from transferring electrons to the working electrode 500 when oxidizing glucose. Further alternatively, glucose oxidase 407 can also be disposed on the opposite side of the sensor in yet other sensor configurations. As shown in FIG. 7B, membrane 409 does not necessarily extend the same lateral distance over working electrode 500 as membrane 408 does.

[0054] In the sensor configurations disclosed herein, the creatinine-responsive active region and, if present, the glucose-responsive active region may comprise one or more discrete spots (e.g., from 1 to about 10 spots, or even more discrete spots) that are approximately 0.01 mm in size. 2 ~about 1mm 2 The total active area can range from 0.01 to 0.01 mm, although larger or smaller individual active area spots are contemplated herein. The total active area can be selected to provide the desired sensitivity for each analyte.

[0055] In some or other embodiments, an analyte sensor of the present disclosure may include a sensor tail configured for insertion into a tissue. Suitable tissues are not considered to be particularly limiting and are addressed in more detail above. Considerations in placing the sensor tail at a particular location within a given tissue are addressed above.

[0056] Thus, the analyte sensor disclosed herein may include at least a first working electrode, a sensor tail including a creatinine-responsive active region disposed on the surface of the first working electrode and including a first electron transfer agent, a first polymer, and an enzyme system including a plurality of enzymes that can act in concert to facilitate detection of creatinine, a first membrane that is permeable to creatinine and covers the creatinine-responsive active region, and an oxygen scavenger disposed near the creatinine-responsive active region on the sensor tail. The enzyme system includes creatinine amidohydrolase, creatine amidinohydrolase, and sarcosine oxidase. The oxygen scavenger may be separated from the creatinine-responsive active region by the first membrane, according to certain embodiments of the present disclosure. An oxidase enzyme, such as glucose oxidase, may comprise at least a portion of the oxygen scavenger in some embodiments.

[0057] An oxidase enzyme, such as glucose oxidase, may be covalently attached to a second polymer when placed near the creatinine-responsive active region. A suitable polymer for covalently attaching glucose oxidase is not particularly limited and may be polyvinylpyridine in certain embodiments of the present disclosure. The covalently attached polymer may help immobilize glucose oxidase in a desired location relative to the creatinine-responsive active region.

[0058] Creatinine amide hydrolase, creatine amidinohydrolase, and sarcosine oxidase may be covalently attached to the first polymer of the creatinine-responsive active region in any embodiment of the present disclosure. The polymer suitable for covalently attaching these enzymes is not believed to be particularly limited, and in certain embodiments of the present disclosure, may be polyvinylpyridine. The first polymer of the creatinine-responsive active region and the second polymer covalently attached to glucose oxidase may be the same polymer.

[0059] In any of the exemplary sensor configurations disclosed herein, the creatinine-responsive active region and, if present, the glucose-responsive active region may each include an electron transfer agent. When both the creatinine-responsive active region and the glucose-responsive active region are present, the electron transfer agents may be the same or different depending on the particular sensor configuration used. A suitable electron transfer agent may facilitate the transfer of electrons to the working electrode after an enzymatic oxidation or reduction reaction has occurred, thereby indicating the presence of a particular analyte and generating a current proportional to the amount of analyte present. For example, when the creatinine-responsive active region and the glucose-responsive active region are disposed on the same working electrode, the electron transfer agents in each active region may be different (e.g., chemically different such that the electron transfer agents exhibit different redox potentials). When multiple working electrodes are present, the electron transfer agents in each active region may be the same or different, since each working electrode may be individually responded to when acquiring a signal. The electron transfer agent may be covalently attached to the polymer in any active region disclosed herein.

[0060] According to various embodiments of the present disclosure, suitable electron transfer agents may include electroreducible and electrooxidizable ions, complexes, or molecules (e.g., quinones) that have redox potentials several hundred millivolts above or below the redox potential of a standard calomel electrode (SCE). According to some embodiments, suitable electron transfer agents may include low potential osmium complexes such as those described in U.S. Pat. Nos. 6,134,461 and 6,605,200, which are incorporated herein by reference in their entireties. Additional examples of suitable electron transfer agents include those described in U.S. Pat. Nos. 6,736,957, 7,501,053, and 7,754,093, the disclosures of each of which are incorporated herein by reference in their entireties. Other suitable electron transfer agents may include metal compounds or complexes of ruthenium, osmium, iron (e.g., polyvinylferrocene or hexacyanoferrate), or cobalt (including, for example, metallocene compounds thereof). Suitable ligands for metal complexes may also include bidentate or higher dentate ligands, such as, for example, bipyridine, biimidazole, phenanthroline, or pyridyl (imidazole). Other suitable bidentate ligands may include, for example, amino acids, oxalic acid, acetylacetone, diaminoalkanes, or o-diaminoarenes. Any combination of monodentate, bidentate, tridentate, tetradentate, or higher dentate ligands may be present in the metal complex to achieve a complete coordination sphere.

[0061] Active regions suitable for detecting creatinine and / or glucose may also include a polymer to which an electron transfer agent is covalently attached. Any of the electron transfer agents disclosed herein may include appropriate functionality to facilitate covalent attachment to the polymer in the active region. Suitable examples of polymer-bound electron transfer agents may include those described in U.S. Pat. Nos. 8,444,834, 8,268,143, and 6,605,201, the disclosures of which are incorporated herein by reference in their entirety. Polymers suitable for inclusion in the active region may include, but are not limited to, polyvinylpyridine (e.g., poly(4-vinylpyridine)), polyvinylimidazole (e.g., poly(1-vinylimidazole)), or any copolymers thereof. Exemplary copolymers that may be suitable for inclusion in the active region include those that include monomer units such as, for example, styrene, acrylamide, methacrylamide, or acrylonitrile. The polymers in each active region may be the same or different.

[0062] In certain embodiments of the present disclosure, the mass transport limiting membrane covering the creatinine-responsive active area may comprise at least a cross-linked polyvinylpyridine homopolymer or copolymer, including polyvinylpyridine-co-styrene polymer. A mass transport limiting membrane with a similar composition may also cover an oxygen scavenger, such as glucose oxidase. The composition of the mass transport limiting membrane may be the same or different where it covers each active area. Suitable techniques for depositing the mass transport limiting membrane on the active area include, for example, spray coating, painting, inkjet printing, stenciling, roller coating, dip coating, and the like, and any combination thereof.

[0063] The method of covalent bonding between the electron transfer agent and the polymer in each active region is not considered to be particularly limited. The covalent bonding of the electron transfer agent to the polymer can occur by polymerizing a monomer unit having a covalently bonded electron transfer agent, or the electron transfer agent can be reacted separately with the polymer after the polymer has already been synthesized. According to some embodiments, a bifunctional spacer can covalently bond the electron transfer agent to the polymer in the active region, where a first functional group is reactive with the polymer (e.g., a functional group that can quaternize the pyridine nitrogen atom or the imidazole nitrogen atom) and a second functional group is reactive with the electron transfer agent (e.g., a functional group that reacts with the ligand that coordinates the metal ion).

[0064] Similarly, one or more enzymes in an active region may be covalently bound to a polymer. When an enzyme system comprising multiple enzymes is present in a given active region, in some embodiments, all of the multiple enzymes may be covalently bound to the polymer, while in other embodiments, only a portion of the multiple enzymes may be covalently bound to the polymer. For example, one or more enzymes comprising the enzyme system may be covalently bound to the polymer, and at least one enzyme may be non-covalently bound to the polymer, such that the non-covalently bound enzyme is physically entrained within the polymer. According to more specific embodiments, the covalent binding of the enzyme to the polymer of a given active region may occur via a crosslinker introduced with a suitable crosslinker. Suitable crosslinkers for reaction with free amino groups in the enzyme (e.g., with free side chain amines in lysine) may include, for example, polyethylene glycol diglycidyl ether (PEGDGE) or other polyepoxides, cyanogen chloride, N-hydroxysuccinimide, imidoesters, epichlorohydrin, or derivatized variants thereof. Suitable crosslinkers for reaction with free carboxylic acid groups in the enzyme may include, for example, carbodiimides. Crosslinking of the enzyme to the polymer is generally intermolecular, but in some embodiments may be intramolecular. In certain embodiments, all enzymes herein may be covalently bound to the polymer.

[0065] The electron transfer agent and / or enzyme can be associated with the polymer in the active area by means other than covalent bonding. In some embodiments, the electron transfer agent and / or enzyme can be ionically or coordinatively associated with the polymer. For example, a charged polymer can be ionically bonded with an oppositely charged electron transfer agent or enzyme. In yet other embodiments, the electron transfer agent and / or enzyme can be physically entrained within the polymer without being bound to the polymer. A physically entrained electron transfer agent and / or enzyme can still adequately interact with the fluid to facilitate detection of the analyte without substantially leaching out of the active area.

[0066] The creatinine-responsive analyte sensor may further incorporate a glucose-responsive active region for sensing both creatinine and glucose in some embodiments of the present disclosure. When both a creatinine-responsive active region and a glucose-responsive active region are present, the creatinine-responsive active region and the glucose-responsive active region may be present on the same working electrode or on different working electrodes, as described above with reference to Figures 4A-6D. Considerations for incorporating a glucose-responsive active region in either location are described in more detail below. In any sensor configuration herein that includes both a creatinine-responsive active region and a glucose-responsive active region, the glucose oxidase, which is not functional for glucose detection, may be located on a membrane covering the creatinine-responsive active region or in another location where it cannot transfer electrons to the working electrode associated with the creatinine-responsive active region.

[0067] When the creatinine-responsive active area and the glucose-responsive active area are disposed on a single working electrode, one of the active areas can be configured to be separately responsive to facilitate detection of each analyte, as described below. In particular, the creatinine-responsive active area and the glucose-responsive active area can include different electron transfer agents to allow one of the active areas to generate a signal independent of the other. Either the creatinine-responsive active area or the glucose-responsive active area can be configured to generate a signal independent of the other active area.

[0068] In embodiments in which the creatinine-responsive active area and the glucose-responsive active area are disposed on a single working electrode, the redox potential associated with the glucose-responsive active area may be separated from the redox potential of the creatinine-responsive active area by at least about 100 mV, or at least about 150 mV, or at least about 200 mV. The upper limit of the separation between the redox potentials is determined in vivo by the working electrochemical window. By separating the magnitude of the redox potentials of the two active areas sufficiently from each other, an electrochemical reaction may occur within one of the two active areas (i.e., the glucose-responsive active area or the creatinine-responsive active area) without substantially inducing an electrochemical reaction within the other active area. Thus, a signal from one of the glucose-responsive active area or the creatinine-responsive active area may be independently generated at or above its corresponding redox potential (lower redox potential) but below the redox potential (higher redox potential) of the other of the glucose-responsive active area and the creatinine-responsive active area. In contrast, above the redox potential (higher redox potential) of the other active region not previously interrogated, electrochemical reactions can occur in both the glucose-responsive active region and the creatinine-responsive active region. Thus, the signal obtained above the higher redox potential can include signal contributions from both the glucose-responsive active region and the creatinine-responsive active region, and the observed signal is a composite signal. The signal contribution above its redox potential from one active region (either the glucose-responsive active region or the creatinine-responsive active region) can then be determined by subtracting the signal above its redox potential obtained from only the glucose-responsive active region or the creatinine-responsive active region from the composite signal.

[0069] In more specific embodiments, the glucose-responsive active region and the creatinine-responsive active region may contain different electron transfer agents to provide sufficient separation in the magnitude of redox potentials between each other when the active regions are located on the same working electrode. More specifically, the glucose-responsive active region may contain a first electron transfer agent and the creatinine-responsive active region may contain a second electron transfer agent, the first electron transfer agent being different from the second electron transfer agent. According to various embodiments of the present disclosure, the metal center and / or ligands present in a given electron transfer agent may be varied to provide sufficient separation in the redox potentials of the two active regions.

[0070] Ideally, the glucose-responsive active region and the creatinine-responsive active region disposed on a single working electrode can be configured to rapidly achieve a steady-state current upon operation of the analyte sensor at a given potential. Rapid achievement of a steady-state current can be promoted by selecting an electron transfer agent for each active region that rapidly changes its oxidation state upon exposure to a potential equal to or greater than its redox potential. Making the active regions as thin as possible can also facilitate rapid achievement of a steady-state current. For example, suitable thicknesses for the glucose-responsive active region and the creatinine-responsive active region can range from about 0.1 microns to about 10 microns. In some or other embodiments, combining conductive materials, such as, for example, carbon nanotubes, graphene, or metal nanoparticles, within one or more active regions can promote rapid achievement of a steady-state current. A suitable amount of conductive particles can range from about 0.1% to about 50% by weight, or from about 1% to about 50% by weight, or from about 0.1% to about 10% by weight, or from about 1% to about 10% by weight of the active region. Stabilizers can also be used to promote stability of the response.

[0071] It should also be understood that the sensitivity (output current) of the analyte sensor to each analyte can be altered by varying the coverage (area or size) of the active regions, the area ratio of the active regions to each other, the nature, thickness, and / or composition of the mass transport limiting membrane covering the active regions. Alterations in these parameters can be readily implemented by one of ordinary skill in the art given the benefit of the disclosure herein.

[0072] Other embodiments of the analyte sensor disclosed herein may feature a creatinine-responsive active region and a glucose-responsive active region on the surface of different working electrodes. Such an analyte sensor may further include a second working electrode, a glucose-responsive active region disposed on the surface of the second working electrode, and a second membrane that is permeable to glucose covering the glucose-responsive active region. The glucose-responsive active region may include a second electron transfer agent, a third polymer, and glucose oxidase covalently bound to the third polymer. The third polymer may be the same or different from the first and / or second polymers associated with the creatinine-responsive active region or the glucose oxidase that is not functional for glucose detection, respectively. When the creatinine-responsive active region and the glucose-responsive active region are disposed on separate working electrodes, the electron transfer agents associated with each active region may be the same or different.

[0073] Thus, a particular analyte sensor of the present disclosure capable of detecting both creatinine and glucose includes: a sensor tail including a first working electrode and a second working electrode; a creatinine-responsive active region disposed on the surface of the first working electrode, the creatinine-responsive active region including a first electron transfer agent, a first polymer, and an enzyme system including a plurality of enzymes that can act in concert to facilitate detection of creatinine, the enzyme system including creatinine amidohydrolase, creatine amidinohydrolase, and sarcosine oxidase; a first membrane that is permeable to creatinine and covers the creatinine-responsive active region; glucose oxidase covalently bonded to a second polymer and disposed on the first membrane; a glucose-responsive active region disposed on the surface of the second working electrode, the glucose-responsive active region including a second electron transfer agent, a third polymer, and glucose oxidase covalently bonded to the third polymer; and a second membrane that is permeable to glucose and covers the glucose-responsive active region. Such an analyte sensor may further include a third membrane that covers the glucose oxidase disposed on the first membrane. The first film, the second film, and, if present, the third film, can be compositionally the same in certain embodiments.

[0074] A detection method for assaying creatinine includes: exposing an analyte sensor to a fluid containing at least creatinine, the analyte sensor including at least a first working electrode, a sensor tail including a creatinine-responsive active region disposed on a surface of the first working electrode, a first membrane permeable to creatinine and covering the creatinine-responsive active region, and an oxygen scavenger disposed on the sensor tail and near the creatinine-responsive active region. The creatinine-responsive active region includes a first electron transfer agent, a first polymer, an enzyme system including a plurality of enzymes that can act in concert to facilitate detection of creatinine. The enzyme system includes creatinine amidohydrolase, creatine amidinohydrolase, and sarcosine oxidase, all of which may be covalently attached to the first polymer in certain embodiments. The method may further include applying a potential to the first working electrode, obtaining a first signal at or above the redox potential of the creatinine-responsive active region, the first signal being proportional to the concentration of creatinine in the fluid, and correlating the first signal to the concentration of creatinine in the fluid. In certain embodiments of the present disclosure, the fluid may be a biological fluid. In more particular embodiments, glucose may be present in the fluid along with creatinine.

[0075] In some embodiments, the first signal can be correlated to a corresponding creatinine concentration by referencing a lookup table or calibration curve. A creatinine lookup table can be created by analyzing multiple samples with known creatinine concentrations and recording the sensor response at each concentration. Similarly, a creatinine calibration curve can be determined by plotting the analyte sensor response as a function of creatinine concentration, and a suitable calibration function can be determined (e.g., by regression, particularly linear regression) over the calibration range.

[0076] The processor can determine which sensor response value in the lookup table is closest to that measured for the sample with unknown analyte concentration and report the analyte concentration accordingly. In some or other embodiments, if the sensor response value of the sample with unknown analyte concentration is between the values ​​recorded in the lookup table, the processor can interpolate between the two lookup table values ​​to estimate the analyte concentration. The interpolation can assume a linear concentration variation between the two values ​​reported in the lookup table. Interpolation can be used when the sensor response is sufficiently different from a given value in the lookup table (e.g., a variation of about 10% or more).

[0077] Similarly, according to some or various other embodiments, the processor can input the sensor response values ​​of samples having unknown analyte concentrations into a corresponding calibration function, and the processor can then report the analyte concentrations accordingly.

[0078] The sensor tail may further include a second working electrode having a glucose-responsive active region disposed thereon, the glucose-responsive active region may include a second electron transfer agent, a third polymer, and glucose oxidase covalently bound to the third polymer. Thus, the method may further include: applying a potential to the second working electrode, obtaining a second signal at or above the redox potential of the glucose-responsive active region that is proportional to the concentration of glucose in the fluid, and correlating the second signal to the concentration of glucose in the fluid.

[0079] A detection method for assaying creatinine and / or glucose using an analyte sensor featuring a creatinine-responsive active region and a glucose-responsive active region on a single working electrode may include: exposing the analyte sensor to a fluid containing at least one of creatinine and glucose. The analyte sensor may include at least a working electrode, particularly a single working electrode, and a sensor tail disposed on the surface of the working electrode and including at least a creatinine-responsive active region and a glucose-responsive active region spaced apart from one another. A membrane may cover the creatinine-responsive active region, and glucose oxidase covalently bound to a polymer may be disposed on the membrane in addition to the glucose oxidase in the glucose-responsive active region. The creatinine-responsive active region includes an enzyme system including two or more enzymes capable of acting in concert to facilitate detection of creatinine, a first polymer covalently bound to the enzyme, and a first electron transfer agent covalently bound to the first polymer. The glucose-responsive active region includes glucose oxidase, a third polymer covalently bound to the glucose oxidase, and a second electron transfer agent covalently bound to the third polymer. When the glucose-responsive active area and the creatinine-responsive active area are located on a single working electrode, the first and second electron transfer agents are compositionally distinct from one another, as described in more detail herein. Each active area has an oxidation-reduction potential, and the oxidation-reduction potential of the creatinine-responsive active area is sufficiently distant from the oxidation-reduction potential of the glucose-responsive active area to allow for the generation of a signal from one of the active areas. The method further includes acquiring a first signal at or above the lower oxidation-reduction potential but below the higher oxidation-reduction potential, such that the first signal is proportional to the concentration of one of glucose or creatinine in the fluid; acquiring a second signal at or above the higher oxidation-reduction potential, such that the second signal is a composite signal that includes a signal contribution from the glucose-responsive active area and a signal contribution from the creatinine-responsive active area; and subtracting the first signal from the second signal to acquire a difference signal proportional to the concentration of one of glucose and creatinine.

[0080] In more specific embodiments, the redox potential associated with the creatinine-responsive active region may be at least about 100 mV, or at least about 150 mV, or at least about 200 mV away from the redox potential of the glucose-responsive active region to provide sufficient separation for independent generation of a signal from the first active region. Different redox potentials can be generated by incorporating different electron transfer agents into the active regions.

[0081] A detection method for assaying creatinine and / or glucose using an analyte sensor featuring a creatinine-responsive active area and a glucose-responsive active area on separate working electrodes may include: exposing the analyte sensor to a fluid containing at least one of glucose and creatinine. The analyte sensor includes at least a first working electrode and a second working electrode, a creatinine-responsive active area disposed on the surface of the first working electrode, a sensor tail including a glucose-responsive active area disposed on the surface of the second working electrode, and a first membrane covering the creatinine-responsive active area and a second membrane covering the glucose-responsive active area. The glucose-responsive active area includes a glucose-responsive enzyme, such as glucose oxidase, and the creatinine-responsive active area includes an enzyme system including at least two enzymes that can act in concert to facilitate detection of creatinine.

[0082] The method may further include applying a potential to the first working electrode and applying a potential to the second working electrode, obtaining a first signal at or above the redox potential of the creatinine-responsive active region that is proportional to the concentration of creatinine in the fluid, obtaining a second signal at or above the redox potential of the glucose-responsive active region that is proportional to the concentration of glucose in the fluid, and correlating the first signal to the concentration of creatinine in the fluid and the second signal to the concentration of glucose in the fluid.

[0083] According to more specific embodiments, the first signal and the second signal can be measured at different times. Thus, in such embodiments, the potential can be applied alternately to the first and second working electrodes. In other specific embodiments, the first and second signals can be measured simultaneously through the first and second channels, in which case the potential can be applied simultaneously to both electrodes. In either case, the signals associated with each active area can be correlated to the concentrations of creatinine and glucose in a similar manner as described above using lookup tables or calibration functions.

[0084] Embodiments disclosed herein include the following: A. Creatinine-Responsive Analyte Sensor. The analyte sensor includes: a sensor tail including at least a first working electrode; a creatinine-responsive active region disposed on a surface of the first working electrode, the creatinine-responsive active region including a first electron transfer agent, a first polymer, and an enzyme system including a plurality of enzymes capable of acting in concert to facilitate detection of creatinine, the enzyme system including creatinine amidohydrolase, creatine amidinohydrolase, and sarcosine oxidase; a first membrane permeable to creatinine and covering the creatinine-responsive active region; and an oxygen scavenger disposed on the sensor tail and proximate the creatinine-responsive active region.

[0085] B. Creatinine and Glucose Responsive Analyte Sensor. The analyte sensor includes: a sensor tail including a first working electrode and a second working electrode; a creatinine-responsive active region disposed on the first working electrode, the creatinine-responsive active region including a first electron transfer agent, a first polymer, and an enzyme system including a plurality of enzymes that can act in concert to facilitate detection of creatinine, the enzyme system including creatinine amidohydrolase, creatine amidinohydrolase, and sarcosine oxidase; a first membrane permeable to creatinine and covering the creatinine-responsive active region; glucose oxidase covalently bonded to a second polymer and disposed on the first membrane; a glucose-responsive active region disposed on the second working electrode, the glucose-responsive active region including a second electron transfer agent, a third polymer, and glucose oxidase covalently bonded to the third polymer; and a second membrane permeable to glucose and covering the glucose-responsive active region.

[0086] C. A method of assaying creatinine using an analyte sensor, the method including: exposing the analyte sensor to a fluid including at least creatinine; the analyte sensor includes a sensor tail including at least a first working electrode, a creatinine-responsive active region disposed on a surface of the first working electrode, a first membrane permeable to creatinine and covering the creatinine-responsive active region, and an oxygen scavenger disposed on the sensor tail and near the creatinine-responsive active region; the creatinine-responsive active region includes a first electron transfer agent, a first polymer, and an enzyme system including a plurality of enzymes capable of acting in concert to facilitate detection of creatinine, the enzyme system including creatinine amidohydrolase, creatine amidinohydrolase, and sarcosine oxidase; applying an electrical potential to the first working electrode; obtaining a first signal at or above the redox potential of the creatinine-responsive active region, the first signal being proportional to the concentration of creatinine in the fluid; and correlating the first signal to the concentration of creatinine in the fluid. Each of embodiments A through D may have one or more of the following additional elements in any combination: Element 1: The oxygen scavenger is separated from the creatinine responsive active area by a first membrane.

[0087] Element 2: The oxygen scavenger comprises an oxidase enzyme. Element 3: Oxygen scavengers include glucose oxidase. Element 4: Glucose oxidase is covalently attached to a second polymer.

[0088] Element 5: An oxygen scavenger is disposed on the first membrane, optionally the oxygen scavenger comprises an oxidase enzyme, optionally the oxygen scavenger comprises glucose oxidase, optionally the glucose oxidase is covalently bound to a second polymer.

[0089] Element 6: The creatinine amidohydrolase, the creatine amidinohydrolase, and the sarcosine oxidase are each covalently attached to a first polymer. Element 7: The analyte sensor further includes a second working electrode; a glucose-responsive active area disposed on a surface of the second working electrode, the glucose-responsive active area including a second electron transfer agent, a third polymer, and glucose oxidase covalently bonded to the third polymer; and a second membrane that is permeable to glucose and covers the glucose-responsive active area.

[0090] Element 8: The analyte sensor further includes glucose oxidase covalently bonded to a second polymer and disposed on the first membrane. Element 9: The first film and the second film are compositionally identical.

[0091] Element 10: Glucose oxidase disposed on a first membrane is covered by a third membrane that is permeable to creatinine. Element 11: The first film, the second film, and the third film are compositionally identical.

[0092] Element 12: An oxygen scavenger is disposed on the first membrane. Element 13: The oxygen scavenger comprises glucose oxidase covalently attached to a second polymer.

[0093] Element 14: The sensor tail further includes a second working electrode having a glucose-responsive active region disposed on a surface of the second working electrode, the glucose-responsive active region including a second electron transfer agent, a third polymer, and glucose oxidase covalently bound to the third polymer, and the method further includes: applying a potential to the second working electrode; obtaining a second signal at or above the redox potential of the glucose-responsive active region, the second signal being proportional to the concentration of glucose in the fluid; and correlating the second signal to the concentration of glucose in the fluid.

[0094] Element 15: The first signal and the second signal are acquired at different times. Element 16: A first signal and a second signal are simultaneously acquired via a first channel and a second channel.

[0095] As non-limiting examples, exemplary combinations applicable to A include: 1 and 2; 1 and 3; 1, 3 and 4; 1 and 5; 1, 5 and 6; 1 and 7; 1, 3 and 7; 1, 3, 4 and 7; 1, 5 and 7; 1 and 5-7; 1 and 8; 1, 7 and 8; 1, 3, 4 and 7; 1, 5 and 7; 1 and 5-7; 1, 6 and 7; 1, 3, 4, 6 and 7; 1, 3, 4 and 6-8; 1, 3, 4, 6, 7 and 9; 1 and 5-10; 1 and 5-11; 1 and 5- 12;2 and 3;2-4;2 and 6;2 and 7;3 and 6;3, 6 and 7;3 and 7;3 and 8;3, 7 and 8;3, 8 and 9;3, 7 and 8;3 and 7-9;3 and 8-10;3 and 8-11;3 and 8-12;3, 4 and 7;3, 4, 8 and 9;3, 4 and 7-10;3, 4 and 7-11;4 and 5;5 and 6;5-7;5 and 7;7 and 9;7, 9 and 10;7 and 9-11;7 and 8; and 8 and 9. Exemplary combinations applicable to B include 10 and 11;9 and 10;6 and 10; and 6 and 11. Exemplary combinations applicable to C include: 1 and 3; 1 and 6; 1, 3 and 6; 1 and 9; 1, 3 and 9; 1, 3 and 10; 1, 3, 10 and 11; 6 and 12; 6 and 13; 6 and 14; 6 and 15; 6 and 16; 12 and 13; 12 and 14; 12 and 15; 12 and 16; 13 and 14; 13 and 15; 13 and 16; 14 and 15; and 14 and 16.

[0096] To facilitate a better understanding of the present disclosure, the following examples of various representative embodiments are given and should not be construed as limiting or defining the scope of the present invention.

[0097] Working Example A poly(vinylpyridine)-bound transition metal complex has been prepared having the structure shown in Formula 1. Further details regarding this transition metal complex and electron transfer therewith are provided in commonly owned U.S. Patent No. 6,605,200, incorporated by reference above. The subscripts for each monomer represent exemplary atomic ratios and do not indicate a particular monomer order.

[0098] [ka]

[0099] The buffered spotting formulation (10 mM MES buffer) identified in Table 1 below was deposited onto the carbon working electrode to form a creatinine-responsive active area. The deposition was performed to deposit the creatinine-responsive active area on a 0.12 mm 2 The spotting formulation was used to form a single spot with an area of ​​15 nL. After deposition, the creatinine-responsive active area was cured overnight at 25 °C. The membrane was then dip-coated on top of the creatinine-responsive active area using a coating solution formulated as 4 mL of 35 mg / mL polyvinylpyridine-co-styrene, 0.1 mL of 100 mg / mL PEGDGE400, and 3.3 μL of PDMS in 80:20 ethanol / 10 mM HEPES buffer (pH = 8). No curing was performed at this stage.

[0100] [Table 1]

[0101] After coating the membrane on the creatinine-responsive active area, a buffered spotting formulation containing glucose oxidase as specified in Table 2 was deposited on the membrane. Specifically, 15 nL of spotting formulation was applied to 0.05 mm 2 was deposited on the membrane with an area of ​​100 μg / ml and then cured overnight at 25° C. After that, the same coating solution as above was used for dip coating to form a membrane on the deposited glucose oxidase.

[0102] [Table 2]

[0103] A control electrode was prepared as above, except that glucose oxidase deposition onto the creatinine-responsive active area was omitted. Creatinine analysis was performed by immersing the electrodes in 5 mM glucose solutions containing various amounts of creatinine (20 μM, 40 μM, 60 μM, 80 μM, 100 μM, 130 μM, and 200 μM) and measuring the current response. A control electrode without glucose oxidase in the creatinine-responsive active area was also tested under the same conditions. FIG. 8 shows an exemplary plot of the current response of three replicates of an analyte sensor containing a creatinine-responsive active area covered with glucose oxidase upon exposure to various creatinine concentrations at 33° C. As shown, the current response increased for a few minutes after exposure to the new creatinine concentration and then stabilized. In contrast, the two control sensors, whose creatinine-responsive active areas were not covered with glucose oxidase, did not respond to creatinine at any concentration. 9 shows an exemplary plot of the current response of a single analyte sensor containing a creatinine-responsive active region coated with glucose oxidase upon exposure to various creatinine concentrations (20 μM, 40 μM, 60 μM, 80 μM, 100 μM, 130 μM, and 200 μM). As shown, the sensor response was essentially linear over the concentration range tested. Again, a control sensor not coated with glucose oxidase showed essentially no response to creatinine, likely due to oxygen interference with the enzyme system.

[0104] Unless otherwise noted, all numbers expressing quantities and the like in the specification and the associated claims should be understood in all instances to be modified by the term "about." Accordingly, unless indicated to the contrary, the numerical parameters set forth in the following specification and attached claims are approximations that may vary depending upon the desired properties sought to be obtained by embodiments of the invention. At the very least, and not as an attempt to limit the application of the doctrine of equivalents to the scope of the claims, each numerical parameter should be construed at least in light of the number of reported significant digits and by applying ordinary rounding techniques.

[0105] One or more exemplary embodiments incorporating various features are presented herein. For clarity, not all features of a physical implementation are described or shown in this application. In developing a physical embodiment incorporating an embodiment of the present invention, it is understood that numerous implementation-specific decisions must be made to achieve the developer's goals, such as compliance with system-related, business-related, government-related and other constraints. These will vary from implementation to implementation and from case to case. While the developer's efforts may be time consuming, such efforts are nevertheless routine for those of ordinary skill in the art who would have the benefit of this disclosure.

[0106] Although various systems, tools, and methods are described herein in terms of "including" various components or steps, the systems, tools, and methods may also "consist essentially of" or "consist of" various components and steps.

[0107] As used herein, the phrase "at least one of" with the term "and" or "or" preceding a list of items and separating any of the items modifies the entire list, not each member (i.e., each item) of the list. The phrase "at least one of" allows for the meaning of including at least one of any one of the items, and / or at least one of any combination of the items, and / or at least one of each of the items. By way of example, the phrase "at least one of A, B, and C" or "at least one of A, B, or C" refers, respectively, to A only, B only, or C only; any combination of A, B, and C; and / or at least one of each of A, B, and C.

[0108] Thus, the disclosed systems, tools, and methods are well adapted to achieve the objects and advantages mentioned, as well as those inherent therein. The specific embodiments disclosed above are illustrative only, as the teachings of the disclosure may be modified and implemented in different and equivalent manners apparent to those skilled in the art having the benefit of the teachings herein. Moreover, no limitations are intended to the details of construction or design shown herein, except as set forth in the appended claims. Thus, it will be apparent that the specific exemplary embodiments disclosed above may be altered, combined, or modified, and all such variations are deemed to be within the scope of the present disclosure. The systems, tools, and methods illustratively disclosed herein may suitably be practiced in the absence of elements not specifically disclosed herein and / or optional elements disclosed herein. Although the systems, tools, and methods are described in terms of "including" various components or steps, the systems, tools, and methods may also "consist essentially of" or "consist of" various components and steps. All of the numbers and ranges disclosed above may vary somewhat. Whenever a numerical range with a lower limit and an upper limit is disclosed, any number within that range and any included range is specifically disclosed. In particular, all range values ​​disclosed herein (in the form of "about a to about b", or equivalently "about a to b", or equivalently "about a to b") should be understood to describe all numbers and ranges within the broader range of values. In addition, unless expressly and unambiguously defined by the patent owner, the claim terms have their ordinary meaning. In the event of a discrepancy in the usage of a word or term between this specification and one or more patent documents or other documents that may be incorporated by reference herein, the definition in accordance with this specification shall prevail.

Claims

1. An analyte sensor for detecting creatinine in vivo, comprising: A first working electrode; a creatinine-responsive active area for detecting creatinine disposed on a surface of the first working electrode, creatinine amidohydrolase, creatine amidinohydrolase, and Sarcosine oxidase the creatinine responsive active region comprising an enzyme system comprising: an oxygen scavenger disposed adjacent the creatinine responsive active region; The analyte sensor is configured to be at least partially inserted into a user's skin such that a distal portion of the analyte sensor contacts interstitial fluid, thereby detecting creatinine in vivo.

2. The analyte sensor of claim 1, wherein the oxygen scavenger comprises an oxidase enzyme.

3. An analyte sensor as described in claim 1 or 2, wherein the oxygen scavenger includes glucose oxidase.

4. An analyte sensor described in any one of claims 1 to 3, wherein the creatinine responsive active region comprises a first polymer, and creatinine amide hydrolase, creatine amidinohydrolase, and sarcosine oxidase are each covalently bonded to the first polymer.

5. An analyte sensor as described in any one of claims 1 to 4, further comprising a first mass transport limiting membrane disposed on the creatinine-responsive active region, the first mass transport limiting membrane limiting creatinine flux to the creatinine-responsive active region and electrically isolating the oxygen scavenger from the creatinine-responsive active region.

6. The analyte sensor of claim 5, wherein the oxygen scavenger is separated from the creatinine-responsive active region by the first mass transport limiting membrane.

7. The analyte sensor of claim 5, wherein the oxygen scavenger is disposed on the first mass transport limiting membrane.

8. The analyte sensor of claim 5, further comprising a second mass transport limiting membrane disposed on the oxygen scavenger and the first mass transport limiting membrane.

9. A second working electrode, and a glucose-responsive active area for detecting glucose disposed on the surface of the second working electrode; 8. The analyte sensor of claim 5, further comprising: wherein the glucose-responsive active region comprises glucose oxidase.

10. The analyte sensor of claim 9, further comprising a second mass transport limiting membrane disposed on the glucose-responsive active region, the second mass transport limiting membrane for limiting glucose flux to the glucose-responsive active region.

11. The analyte sensor of claim 10, wherein the first mass transport limiting membrane and the second mass transport limiting membrane are of the same composition.

12. The analyte sensor of claim 10 or 11, wherein the oxygen scavenger is covered by a third mass transport limiting membrane for limiting creatinine flux to the creatinine-responsive active region.

13. The analyte sensor of claim 12, wherein the first membrane, the second membrane, and the third membrane are compositionally identical.

14. A method for assaying creatinine in vivo, comprising the steps of: Exposing the analyte sensor of any one of claims 1 to 13 to a fluid containing at least creatinine; applying a potential to the first working electrode; obtaining a first signal at or above the redox potential of the creatinine responsive active region, the first signal being proportional to the concentration of creatinine in the fluid; and determining a concentration of creatinine in the fluid based on the first signal. The method includes:

15. A method for assaying glucose and creatinine in vivo, comprising the steps of: Exposing the analyte sensor of any one of claims 9 to 13 to a fluid containing glucose and creatinine; applying a potential to the first working electrode and the second working electrode; obtaining a first signal at or above the redox potential of the creatinine responsive active region, the first signal being proportional to the concentration of creatinine in the fluid; obtaining a second signal at or above the redox potential of the glucose-responsive active region, the second signal being proportional to the concentration of glucose in the fluid; determining a concentration of creatinine in the fluid based on the first signal; and determining a concentration of glucose in the fluid based on the second signal. The method includes:

16. The method of claim 15, wherein the first signal and the second signal are acquired at different times.

17. The method of claim 15, wherein the first signal and the second signal are acquired simultaneously via a first channel and a second channel.

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