Analyte sensors featuring one or more detection-facilitating enhancements

Abstract

To address such a problem that analyte sensors are being increasingly employed for monitoring various analytes in vivo, analyte sensors configured to monitor a plurality of analytes are also in development, however, sufficient sensitivity for low-abundance analytes and multiple analytes having differing membrane permeability values may complicate analyte detection in some cases.SOLUTION: Analyte sensors may feature enhancements to address one or both of these issues. Some analyte sensors may comprise a carbon working electrode comprising a dielectric substrate, one or more apertures extending through the dielectric substrate and filled with a carbon conductor pillar, a carbon conductor coating on a first face of the dielectric substrate in direct contact with each carbon conductor pillar, and one or more active areas on a second face of the dielectric substrate in electrical communication with the carbon conductor pillars. Photopolymerized mass transport limiting membranes may be used in combination with such carbon working electrodes or with other working electrode types.SELECTED DRAWING: None

Description

[Technical field]

[0001] The present invention relates to an analyte sensor. [Background technology]

[0002] Detection of various analytes in an individual may be important for health monitoring. Deviations from normal analyte levels may indicate many physiological conditions. Glucose levels may be particularly important for detection and monitoring in diabetic individuals, for example. By monitoring glucose levels with sufficient regularity, diabetic individuals may be able to take corrective action (e.g., by injecting insulin to lower glucose levels or by eating to raise glucose levels) before significant physiological problems occur. Monitoring of other analytes may be desirable for various other physiological conditions. In some cases, monitoring of multiple analytes may be desirable, especially for co-occurring conditions that, in combination with each other, result in dysregulation of two or more analytes simultaneously.

[0003] Many analytes are interesting targets for physiological analysis if the appropriate detection chemistry can be identified. To this end, in vivo analyte sensors configured to assay a variety of physiological analytes have been developed and improved in recent years, many of which utilize enzyme-based detection strategies to improve detection specificity. Indeed, in vivo analyte sensors that utilize glucose-responsive enzymes to monitor blood glucose levels are now in common use among diabetic individuals. In vivo analyte sensors for other analytes are in various stages of development, including in vivo analyte sensors that can monitor multiple analytes. Low sensitivity to small amounts of analyte can be particularly problematic for some analyte sensors, especially due to excess background signal resulting from the interaction of interferents with the carbon working electrode.

[0004] To improve biocompatibility, the in vivo analyte sensor may include a membrane disposed over the implantable portion of the sensor, particularly a membrane covering at least the active area(s) of the analyte sensor. In addition to promoting biocompatibility, the membrane may be permeable or semi-permeable to the analyte of interest and limit the total analyte flux to the active area(s) of the analyte sensor. Such mass transport limiting membranes can help avoid overloading (saturation) of the sensing components in the active area(s), thereby improving sensor performance and accuracy. By limiting mass transport of the analyte, the chemical kinetics of the sensing process can be analyte limited rather than enzyme limited, thereby allowing the sensor output to be easily correlated to the amount of analyte present.

[0005] Another problem associated with analyte monitoring is that various analytes may exhibit different permeabilities through a given mass transport limiting membrane. The most common mass transport limiting membranes used in in vivo analyte sensors are polyvinylpyridine or polyvinylimidazole polymers and copolymers, which can be easily applied to the working electrode by dip coating techniques. Polyurethanes are also commonly used to form mass transport limiting membranes. Among this limited set of polymers, it can sometimes be difficult to identify the appropriate membrane chemistry to promote sufficient permeability of a particular analyte. The problem of different analyte permeability can be further complicated in analyte sensors configured to assay multiple analytes, where compositionally different mass transport limiting membranes may be required on different portions of the sensor tail to provide sufficient permeability and / or stable response for each analyte. Different membrane permeability values ​​can result in very different response sensitivities between two analytes, which can complicate detection. A dip coating process to apply a mass transport limiting membrane with compositionally different portions on the analyte sensor tail, while feasible, can significantly increase the complexity of manufacturing. Furthermore, membrane chemistries other than those based on polyvinylpyridine or polyvinylimidazole may not be easily scalable to dip-coating processes. Differential sensitivity to multiple analytes can sometimes be partially compensated for by using active areas of different sizes (e.g., smaller active areas for analytes with high sensitivity / permeability and larger active areas for analytes with lower sensitivity / permeability), but this approach can present significant manufacturing challenges and may not be applicable in all cases. Thus, the scarcity of available compositions for forming mass transport limiting membranes can complicate the detection of certain analytes. [Brief description of the drawings]

[0006] The following figures 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 numerous modifications, variations, combinations, and equivalents in form and function without departing from the scope of the present disclosure.

[0007] [Figure 1] 1 shows a schematic diagram of an exemplary sensing system that may incorporate an analyte sensor of the present disclosure. [Figure 2A] FIG. 2 shows a cross-sectional view of an analyte sensor with a single active area. [Figure 2B] FIG. 2 shows a cross-sectional view of an analyte sensor with a single active area. [Figure 2C] FIG. 2 shows a cross-sectional view of an analyte sensor with a single active area. [Figure 3A] 1 shows a cross-sectional view of an analyte sensor with two active areas. [Figure 3B] 1 shows a cross-sectional view of an analyte sensor with two active areas. [Figure 3C] 1 shows a cross-sectional view of an analyte sensor with two active areas. [Figure 4] 1 shows a cross-sectional view of an analyte sensor with two working electrodes, each having an active area thereon. [Diagram 5] FIG. 1 is a schematic diagram showing a top view of a conventional carbon working electrode having an active area thereon. [Figure 6A] FIG. 1 shows a cross-sectional view of a first configuration of a carbon working electrode suitable for use in an analyte sensor of the present disclosure. [Figure 6B] The corresponding top view is shown. [Figure 7] 1 shows a schematic diagram of an exemplary process by which a carbon working electrode may be fabricated in a dielectric substrate. [Figure 8A] FIG. 2 shows a cross-sectional view of a second configuration of a carbon working electrode suitable for use in the analyte sensor of the present disclosure. [Figure 8B] The corresponding top view is shown. [Figure 9A] FIG. 2 shows a cross-sectional view of a third configuration of a carbon working electrode suitable for use in the analyte sensor of the present disclosure. [Figure 9B]The corresponding top view is shown. [Figure 10A] 1 shows an enzyme system configured to detect glucose. [Figure 10B] 1 shows an enzyme system configured to detect glucose. [Figure 10C] 1 shows an enzyme system configured to detect glucose. [Figure 11A] 1 shows an enzyme system configured to detect ketones. [Figure 11B] 1 shows an enzyme system configured to detect ketones. [Figure 11C] 1 shows an enzyme system configured to detect ketones. [Figure 12] 1 shows an enzyme system configured to detect creatinine. [Figure 13] 1 shows plots of the sensor response of several glucose sensors coated with mass transport limiting membranes formed from various ratios of HEMA:POMA. [Figure 14] A corresponding plot of the sensor response as a function of glucose concentration is shown. [Figure 15A] 1 shows plots of the sensor response of several ketone sensors coated with mass transport limiting membranes formed from various ratios of HEMA:POMA. [Figure 15B] 1 shows plots of the sensor response of several ketone sensors coated with mass transport limiting membranes formed from various ratios of HEMA:POMA. [Figure 16A] A corresponding plot of sensor response as a function of ketone concentration is shown. [Figure 16B] A corresponding plot of sensor response as a function of ketone concentration is shown. [Figure 17] 1 shows plots of the sensor response of several ketone sensors coated with mass transport limiting membranes formed from various ratios of thiol-ene polymers. [Figure 18] A corresponding plot of sensor response as a function of ketone concentration is shown. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0008] The present disclosure generally describes analyte sensors suitable for in vivo use, and more specifically, describes analyte sensors that feature one or more enhancements to facilitate improved detection sensitivity, as well as methods of making and using the same. Such enhancements may include reducing the amount of extraneous carbon on the surface of the carbon working electrode and / or broadening the range of film chemistries available for deposition of the mass transport limiting film. In particular, the range of chemistries available for the mass transport limiting film may be broadened through an in situ polymerization reaction, such as photopolymerization, to provide selective film deposition onto the active area(s) of the working electrode. The selectivity provided by in situ photopolymerization may allow mass transport limiting films having different compositions to be deposited onto selected areas of the working electrode, which may be particularly beneficial when assaying multiple analytes using a single analyte sensor capable of multiple analyte detection. The specific details and further advantages of each type of enhancement are described in more detail herein. Depending on the particular needs, the analyte sensors of the present disclosure may be configured to detect one or more analytes simultaneously or nearly simultaneously.

[0009] Analyte sensors using enzyme-based detection are commonly used to assay a single analyte, such as glucose, due to the frequent specificity of enzymes for a particular substrate or class of substrates. For this purpose, analyte sensors employing both single enzymes and enzyme systems with multiple enzymes acting in concert can be used. As used herein, the term "in concert" refers to coupled enzyme reactions in which the product of a first enzyme reaction becomes the substrate for a second enzyme reaction, and the second or subsequent enzyme reaction serves as the basis for measuring the concentration of the analyte. The use of in vivo analyte sensors featuring enzymes or enzyme systems to facilitate detection can be particularly advantageous in avoiding frequent withdrawal of bodily fluids that may otherwise be required to perform analyte monitoring.

[0010] Although suitable active regions for assaying various analytes are currently known, there are sometimes difficulties associated with the detection of certain analytes or combinations of analytes. For example, sensor sensitivity may be insufficient for low amounts of analytes. Carbon working electrodes may provide relatively high background signals that may complicate accurate detection of some low amounts of analytes. Significantly different membrane permeability values ​​may also be problematic when assaying multiple analytes. The present disclosure provides analyte sensor enhancements that may improve detection sensitivity for both single analytes and multiple analytes in combination with each other, either alone or in combination, as described in more detail below. That is, the present disclosure provides analyte sensors having carbon working electrodes that may reduce background signals and expand the range of suitable membrane chemistries that may be selectively deposited on the analyte sensor. Although certain aspects of the present disclosure are directed to the enhancement of carbon working electrodes, it should be understood that other types of electrodes may be similarly enhanced in accordance with the disclosure herein. Types of electrodes that may be enhanced through the use of the disclosure herein also include gold, platinum, PEDOT, and the like.

[0011] Before describing the analyte sensors of the present disclosure and their enhancements in further detail, a brief overview of suitable in vivo analyte sensor configurations and sensor systems using analyte sensors will first be provided so that embodiments of the present disclosure may be better understood. FIG. 1 shows a schematic diagram of an exemplary sensing system that may incorporate the analyte sensors of the present disclosure. As shown, the sensing system 100 includes a sensor control device 102 and a reading device 120 that are configured to communicate with each other via a local communication path or link 140, which may be wired or wireless, unidirectional or bidirectional, and encrypted or unencrypted. According to some embodiments, the reading device 120 may constitute an output medium for viewing the analyte concentration and alerts or notifications determined by the sensor 104 or its associated processor, as well as for enabling one or more user inputs. The reading device 120 may be a general-purpose smartphone or a dedicated electronic reading device. Although only one reading device 120 is shown, multiple reading devices 120 may be present in certain examples. The reading device 120 may also communicate with the remote terminal 170 and / or the trusted computer system 180 via communication path(s) / link(s) 141 and / or 142, respectively, which may also be wired or wireless, unidirectional or bidirectional, and encrypted or unencrypted. The reading device 120 may also or instead 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 further be 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 reading device 120. For example, the sensor 104 may communicate with the remote terminal 170 and / or the trusted computer system 180 via a direct communications link to the network 150, according to some embodiments, as described in U.S. Patent Application Publication No. 2011 / 0213225, the entire contents of which are incorporated herein by reference.Any suitable electronic communication protocol may be used for each of the communication paths or links, such as Near Field Communication (NFC), Radio Frequency Identification (RFID), BLUETOOTH or BLUETOOTH low energy protocols, WiFi, etc. The remote terminal 170 and / or the trusted computer system 180 may be accessible by individuals other than the primary user who have an interest in the user's analyte levels, according to some embodiments. The reading 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.

[0012] The sensor control device 102 includes a sensor housing 103 that may 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 reading device 120. The sensor 104 protrudes from an underside of the sensor housing 103 and penetrates an adhesive layer 105, which according to some embodiments is adapted to adhere the sensor housing 103 to a tissue surface such as skin.

[0013] The sensor 104 is adapted to be at least partially inserted into a tissue of interest, such as in the dermis or subcutaneous layers of the skin. Alternatively, the sensor 104 may be adapted to penetrate the epidermis. Still alternatively, the sensor 104 may be placed superficially and not penetrate the tissue, such as when assaying one or more analytes in sweat on the skin. The sensor 104 may comprise a sensor tail of sufficient length to be inserted to a desired depth in a given tissue. The sensor tail may comprise at least one working electrode and an active region comprising an enzyme or enzyme system configured to assay one or more analytes of interest. Suitable enzymes and enzyme systems are discussed in further detail herein. A counter electrode may be present in combination with the at least one working electrode, and optionally further in combination with a reference electrode. Particular electrode configurations on the sensor tail are described in more detail below with reference to Figures 2A-4. According to various embodiments, one or more enzymes in the active region(s) may be covalently attached to a polymer comprising the active region(s). Alternatively, the enzyme may be non-covalently associated within the active region(s), such as by encapsulation or physical entrainment. One or more analytes may be monitored in any bodily fluid of a subject, such as dermal fluid, interstitial fluid, plasma, blood, lymphatic fluid, synovial fluid, cerebrospinal fluid, saliva, bronchoalveolar lavage, or amniotic fluid, etc. In certain embodiments, the analyte sensor of the present disclosure may be adapted to assay dermal fluid or interstitial fluid to determine the analyte concentration in vivo.

[0014] One or more mass transport limiting membranes may cover the active area(s). When different types of active areas are present, the mass transport limiting membranes may be compositionally the same or compositionally different in each type of active area. Sensor architectures are available to incorporate different mass transport limiting membranes on each type of active area, optionally via dip coating techniques, to facilitate detection of multiple analytes. Different membrane thicknesses or membrane architectures may also be used to facilitate detection of multiple analytes. As described further herein, mass transport limiting membranes with compositional variations in one or more active areas may also be prepared by in situ polymerization, such as in situ photopolymerization. Living polymerization techniques may also be used to form mass transport limiting membranes on active areas. If a single mass transport limiting membrane provides sufficient permeability to both analytes detectable by a multiple analyte detector, a simpler sensor architecture may be used. In situ photopolymerization may also expand the range of suitable membrane chemistries beyond those that are only suitable for deposition by dip coating techniques. In some cases, better quality membranes may also be formed compared to dip coating techniques.

[0015] Referring again to FIG. 1 , the sensor 104 may automatically transfer data to the reading device 120. For example, analyte concentration data may be communicated automatically and periodically, such as at a particular frequency when data is acquired or after a particular period of time has passed, and stored in memory until transmitted (e.g., every minute, every five minutes, or other predetermined period of time). Data associated with different analytes may be transferred at the same or different frequencies and / or using the same or different communication protocols. In other embodiments, the sensor 104 may communicate with the reading device 120 non-automatically and not according to a set schedule. For example, data may be communicated from the sensor 104 using RFID technology when the sensor electronics are brought within communication range of the reading device 120. The data may remain stored in the memory of the sensor 104 until communicated to the reading device 120. Thus, the user does not need to maintain constant proximity to the reading device 120, but can 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 reading device 120 is no longer within communication range of the sensor 104 .

[0016] An introducer may be temporarily present to facilitate the introduction of the sensor 104 into the tissue. In an exemplary embodiment, the introducer may comprise a needle or similar sharp, or a combination thereof. It should be appreciated that other types of introducers, such as a sheath or blade, may be present in alternative embodiments. More specifically, the needle or other introducer may be temporarily present near the sensor 104 prior to tissue insertion and then withdrawn. While present, the needle or other introducer may facilitate the insertion of the sensor 104 into the tissue by opening an access path for the sensor 104 to follow. For example, the needle may facilitate the penetration of the epidermis as an access path to the dermis to allow the implantation of the sensor 104 to occur, according to one or more embodiments. After opening the access path, the needle or other introducer may be withdrawn such that it does not 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 specific embodiments, suitable needles may be comparable in cross-sectional diameter and / or tip design to acupuncture needles and may have a cross-sectional diameter of about two hundred fifty microns (250 μm). However, it should be appreciated that suitable needles may have larger or smaller cross-sectional diameters as required for a particular application. For example, needles having cross-sectional diameters ranging from about three hundred microns (300 μm) to about four hundred microns (400 μm) may be used.

[0017] In some embodiments, the tip of the needle (while present) may be angled over 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 may be subsequently withdrawn after facilitating sensor insertion.

[0018] Sensor configurations featuring a single active area configured for the detection of a corresponding single analyte may use a two-electrode or three-electrode detection motif, as further described herein with reference to Figures 2A-2C. Sensor configurations featuring two different active areas for the detection of different analytes, either on separate working electrodes or on the same working electrode, are described separately below with reference to Figures 3A-4. Sensor configurations with multiple working electrodes may be particularly advantageous for incorporating two different active areas within the same sensor tail, since the signal contribution from each active area may be more easily determined through the separate response of each working electrode. Each active area may be covered with a mass transport limiting membrane, which may be introduced by dip coating or produced by in situ photopolymerization, according to further disclosure below.

[0019] When a single working electrode is present in the analyte sensor, a three-electrode sensor configuration may comprise a working electrode, a counter electrode, and a reference electrode. A related two-electrode sensor configuration may comprise a working electrode and a second electrode, which may function as both a counter electrode and a reference electrode (i.e., a counter / reference electrode). The various electrodes may be at least partially stacked (layered) on one another and / or may be laterally spaced apart from one another on the sensor tail. In any of the sensor configurations disclosed herein, the various electrodes may be electrically insulated from one another by a dielectric material or similar insulator.

[0020] Analyte sensors featuring multiple working electrodes may also include at least one additional electrode. When one additional electrode is present, the one additional electrode may function as a counter / reference electrode for each of the multiple working electrodes. When 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.

[0021] 2A shows a schematic diagram of an exemplary two-electrode analyte sensor configuration suitable for use in the present disclosure. As shown, the analyte sensor 200 comprises 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 between them (configuration not shown). An active area 218 is disposed as at least one layer over at least a portion of the working electrode 214. The active area 218 may comprise multiple spots or a single spot configured for detection of the analyte, as discussed further herein.

[0022] 2A, according to some embodiments, membrane 220 covers at least active area 218 and may optionally cover some or all of working electrode 214 and / or counter / reference electrode 216, or the entire analyte sensor 200. One or both sides of analyte sensor 200 may be covered by membrane 220. Membrane 220 may comprise one or more polymeric membrane materials capable of limiting analyte flux to active area 218 (i.e., membrane 220 is a mass transport limiting membrane having some permeability to the analyte of interest). The composition and thickness of membrane 220 may be varied to facilitate a desired analyte flux to active area 218, thereby providing a desired signal strength and stability. Analyte sensor 200 may be operable to assay an analyte by any of the following electrochemical detection techniques: coulometric, amperometric, voltammetric, or potentiometric.

[0023] 2B and 2C show schematic diagrams of exemplary three-electrode analyte sensor configurations, which are also suitable for use in the present disclosure. The three-electrode analyte sensor configuration may be similar to that shown as analyte sensor 200 in FIG. 2A, except for the inclusion of an additional electrode 217 in analyte sensors 201 and 202 (FIGS. 2B and 2C). With the additional electrode 217, counter / reference electrode 216 may then function as either a counter electrode or a reference electrode, and additional electrode 217 performs other electrode functions not otherwise described. Working electrode 214 continues to perform its original function. Additional electrode 217 may be disposed on either working electrode 214 or electrode 216, with a separating layer of dielectric material therebetween. For example, as shown in FIG. 2B, dielectric layers 219a, 219b, and 219c separate electrodes 214, 216, and 217 from one another and provide electrical insulation. Alternatively, at least one of the electrodes 214, 216, and 217 may be disposed on the opposite side of the substrate 212, as shown in FIG. 2C. Thus, in some embodiments, the electrode 214 (working electrode) and the electrode 216 (counter electrode) may be disposed on the opposite side of the substrate 212, and the electrode 217 (reference electrode) is 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 the location shown in FIG. 2B and FIG. 2C. Similar to the sensor 200 shown in FIG. 2A, the active area 218 in the analyte sensors 201 and 202 may comprise multiple spots or a single spot. In addition, analyte sensors 201 and 202 may be similarly operable to assay the analyte by any of the following electrochemical detection techniques: coulometry, amperometry, voltammetry, or potentiometry.

[0024] Similar to analyte sensor 200, membrane 220 may also cover active area 218 and other sensor components in analyte sensors 201 and 202, thereby acting as a mass transport limiting membrane. Additional electrode 217 may be covered by membrane 220 in some embodiments. Membrane 220 may further be fabricated by dip coating or in situ photopolymerization and may vary in composition at different locations. Although FIGS. 2B and 2C show electrodes 214, 216, and 217 all covered by membrane 220, it should be appreciated that in some embodiments, only working electrode 214 or active area 218 may be covered. Additionally, the thickness of membrane 220 in each of electrodes 214, 216, and 217 may be the same or different. As in the two-electrode analyte sensor configuration (FIG. 2A), one or both faces of analyte sensors 201 and 202 may be covered by membrane 220 in the sensor configurations of FIGURES 2B and 2C, or the entirety of analyte sensors 201 and 202 may be covered. Thus, the three-electrode sensor configuration shown in FIGURES 2B and 2C should be understood as not limiting the embodiments disclosed herein, and alternative electrode and / or layer configurations remain within the scope of the present disclosure.

[0025] FIG. 3A shows an exemplary configuration of a sensor 203 having a single working electrode with two different active areas disposed thereon. FIG. 3A is similar to FIG. 2A, except that there are two active areas on the working electrode 214, a first active area 218a and a second active area 218b, which are responsive to different analytes and are laterally spaced apart from each other on the surface of the working electrode 214. The active areas 218a and 218b may comprise multiple spots or a single spot configured for detection of each analyte. The composition of the membrane 220 may vary in the active areas 218a and 218b or may be compositionally the same. The first active area 218a and the second active area 218b may be configured to detect their corresponding analytes at different working electrode potentials, as discussed further below.

[0026] Figures 3B and 3C show cross-sectional views of exemplary three-electrode sensor configurations for sensors 204 and 205, respectively, each featuring a single working electrode having a first active area 218a and a second active area 218b disposed thereon. Figures 3B and 3C are otherwise similar to Figures 2B and 2C and may be better understood by reference thereto. As with Figure 3A, the composition of membrane 220 may vary in active areas 218a and 218b or may be compositionally the same.

[0027] An exemplary sensor configuration having multiple working electrodes, specifically two working electrodes, is described in further detail with reference to FIG. 4. The following description is primarily directed to a sensor configuration having two working electrodes, but it should be understood that more than two working electrodes may be incorporated by extension of the disclosure herein. The additional working electrodes may be used to provide the analyte sensor with additional sensing capabilities beyond just the first analyte and the second analyte. That is, an analyte sensor containing more than two working electrodes may be suitable for detecting a corresponding number of additional analytes.

[0028] 4 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 in the present disclosure. As shown, the analyte sensor 300 includes working electrodes 304 and 306 disposed on opposite sides of a substrate 302. A first active area 310a is disposed on the surface of the working electrode 304, and a second active area 310b is disposed on the surface of the working electrode 306. The counter electrode 320 is electrically insulated from the working electrode 304 by a dielectric layer 322, and the reference electrode 321 is electrically insulated from the working electrode 306 by a dielectric layer 323. Outer dielectric layers 330 and 332 are disposed on the reference electrode 321 and the counter electrode 320, respectively. A membrane 340 may cover at least the active areas 310a and 310b according to various embodiments, and optionally other components of the analyte sensor 300 or the entire analyte sensor 300 are also covered by the membrane 340. Additionally, membrane 340 may be of varying composition in active regions 310a and 310b, if desired, to provide appropriate permeability values ​​to separately adjust the analyte flux at each location.

[0029] Alternative sensor configurations having multiple working electrodes and different from the configuration shown in Figure 4 may feature counter / reference electrodes in place of separate counter and reference electrodes 320, 321, and / or different layer and / or film arrangements than those explicitly shown. For example, the locations of counter electrode 320 and reference electrode 321 may be opposite those shown in Figure 4. Furthermore, working electrodes 304 and 306 need not necessarily be on opposite sides of substrate 302 as in the location shown in Figure 4.

[0030] A carbon working electrode may suitably comprise the working electrode(s) in any of the analyte sensors disclosed herein. Although carbon working electrodes are very commonly used in electrochemical detection, their use in electrochemical sensing is not without difficulties. In particular, a current for an analyte of interest occurs only when the active area interacts with the analyte and transfers electrons to a portion of the carbon working electrode adjacent to the active area. Fluids containing the analyte of interest also interact with the carbon surface of the carbon working electrode that is not covered by the active area and do not contribute to the analyte signal because there is no enzyme or enzyme system at these locations that facilitates electron transfer from the analyte to the working electrode. However, interferents may be oxidized at the portion of the working electrode that lacks the active area and contribute background to the overall signal. Ascorbic acid is one example of an interferent commonly present in bodily fluids that may generate a background signal at a carbon working electrode. Thus, a carbon working electrode with extraneous carbon areas on the electrode surface may not contribute significantly to the analyte signal and may result in excessive background in some cases. Other electrodes with excessive surface area that do not directly detect analytes of interest may experience similar problems and may be enhanced through the improvements disclosed herein.

[0031] 5 is a schematic diagram showing a top view of a conventional carbon working electrode 412 having an active area 418 arranged as multiple spots thereon. When an analyte interacts with the active area 418, only the portion of the carbon working electrode 412 below the active area 418 contributes to a signal associated with the analyte of interest. The extraneous carbon area 410 is not directly covered by the active area 418 and does not contribute to the signal associated with the analyte, but may generate a background signal associated with one or more interfering substances.

[0032] The present disclosure shows how extraneous carbon area can be reduced in a carbon working electrode while still remaining functional for generating a signal associated with an analyte of interest. In particular, the present disclosure provides an analyte sensor comprising an improved carbon working electrode at least partially formed in a dielectric substrate, such as a polymer block, where the dielectric substrate replaces most or all of the extraneous carbon area on the electrode surface not covered by the active area. More specifically, the carbon working electrodes described herein can be obtained by filling one or more openings with a carbon conductor, as described in more detail below. Alternative electrodes comprising metal or PEDOT can similarly be formed in a dielectric substrate according to the disclosure herein.

[0033] FIG. 6A illustrates a cross-sectional view of a first configuration of a carbon working electrode suitable for use in an analyte sensor of the present disclosure. As shown in FIG. 6A, the carbon working electrode 500 includes a dielectric substrate 510 having carbon conductor pillars 512 that penetrate the dielectric substrate 510 and extend between a first surface 514 and a second surface 516. The carbon conductor pillars 512 may be formed by filling vias or similar openings with a carbon conductor ink, followed by curing, as described in more detail below with reference to FIG. 7. A carbon conductor coating 520 is disposed on the first surface 514 and in direct contact with each of the carbon conductor pillars 512, thereby establishing electrical continuity between each of the carbon conductor pillars 512. A dielectric coating 522 is disposed on the carbon conductor coating 520. Thus, the only carbon surface available for electron transfer is located on the second surface 516 where the carbon conductor pillars 512 penetrate the dielectric substrate 510. An active region 530 is disposed on the second surface 516 in direct contact with the carbon conductor pillars 512 .

[0034] Alternatives to carbon working electrodes may be formed by depositing similar conductive inks into openings through the dielectric substrate 510. For example, metal-containing inks may be similarly deposited and cured to provide metal conductor pillars. Metal conductor coatings may interconnect the metal conductor pillars and may similarly be formed from metal-containing inks. Thus, any of the electrode structures described herein with respect to carbon working electrodes may similarly be formed using alternative conductive materials.

[0035] FIG. 6B shows a corresponding top view of the carbon working electrode of FIG. 6A. As shown, the active areas 530 cover the exposed surfaces (not visible in the depicted view) of the carbon conductor pillars 512, thereby leaving little extraneous carbon area available to generate an electrochemical signal upon interacting with interferents. Although FIGS. 6A and 6B show a complete overlay of the active areas 530 on the carbon conductor pillars 512, it should be understood that the active areas 530 may also be slightly offset from the carbon conductor pillars 512 and / or may not completely cover the carbon conductor pillars 512, thereby leaving a small amount of extraneous carbon area that may be exposed to interferents. Nevertheless, it can be understood that the amount of extraneous carbon present in the carbon working electrode 500 is much less than the amount in a conventional carbon working electrode having a surface substantially formed of a carbon conductor. It should also be understood that the number and spacing of the carbon conductor pillars 512 and the active areas 530 are exemplary and non-limiting. In exemplary embodiments, the number of openings (vias) may range from about 1 to about 20, or from about 3 to about 15, or from about 2 to about 10, and the diameter of the openings may range from about 25 μm to about 200 μm. Non-circular openings may also be present. A corresponding number of active areas may be present on the carbon conductor pillars, or the number of active areas may be less than the number of carbon conductor pillars. If less than all of the carbon conductor pillars are covered by active areas, some extraneous carbon remains present for potential exposure to interferents.

[0036] FIG. 7 shows a schematic of an exemplary process by which a carbon working electrode may be fabricated in a dielectric substrate. First, a dielectric substrate 510 is provided with a number of vias 511 therethrough. There are numerous methods to introduce the vias 511 in the dielectric substrate 510, such as drilling, laser drilling, or similar techniques well known to those skilled in the art. A carbon conductor ink is then deposited by screen printing or a similar deposition technique to form a carbon conductor coating 520 on the first side 514. The vias 511 may be at least partially filled during this process. If necessary, completion of the filling of the vias 511 with the carbon conductor ink to provide carbon conductor pillars 512 after the ink dries may be performed from the second side 516. Suitable carbon conductor inks are well known to those skilled in the art.

[0037] A dielectric coating 522 is then deposited on the carbon conductor coating 520, leaving exposed carbon conductor pillar surfaces 528 on the second side 516 of the dielectric substrate 510. Finally, an active area 530 is deposited on the exposed carbon conductor pillar surfaces 528 to provide a carbon working electrode 500 having sensing capabilities for an analyte of interest. Although Figure 7 is described with respect to via filling, it should be understood that other types of openings may be filled with the carbon conductor ink to form similar types of carbon conductor pillars therein.

[0038] Accordingly, a method for forming an analyte sensor of the present disclosure may include providing a dielectric substrate having one or more openings extending therethrough between a first side and a second side; filling the one or more openings with a carbon conductor to form carbon conductor pillars therein; depositing a carbon conductor coating on the first side of the dielectric substrate such that the carbon conductor coating directly contacts each carbon conductor pillar; depositing a dielectric coating on the carbon conductor coating; forming one or more active areas on the second side of the dielectric substrate in electrical communication with the carbon conductor pillars in the one or more openings and responsive to the analyte; and depositing a mass transport limiting membrane on at least the one or more active areas.

[0039] 8A shows a cross-sectional view of a second configuration of a carbon working electrode suitable for use in an analyte sensor of the present disclosure. The carbon working electrode 501 differs from the carbon working electrode 500 shown in FIGS. 6A and 6B in that a monolithic carbon conductor pillar 513 penetrates the dielectric substrate 510 between a first side 514 and a second side 516, thereby replacing a plurality of smaller carbon conductor pillars 512. The monolithic carbon conductor pillars 513 may be formed by filling a slot or similar opening with a carbon conductor ink in a manner similar to that described above with reference to FIG. 7, followed by drying the ink. Each of the active areas 530 is disposed on the second side 516 in direct contact with a monolithic carbon conductor pillar 513.

[0040] 8B shows a corresponding top view of the carbon working electrode of FIG. 8A. As shown, the active areas 530 cover the exposed surfaces 540 of the monolithic carbon conductor pillars 513. Although the exposed surfaces 540 are not completely covered by the active areas 530 in the carbon working electrode 501, the amount of extraneous carbon is much less than that present in a conventional carbon working electrode having a surface substantially formed of a carbon conductor. Furthermore, it should be understood that the number and spacing of the active areas 530 are exemplary and non-limiting. In an exemplary embodiment, the slots can range from about 25 μm to about 200 μm in width and about 100 μm to about 2000 μm in length.

[0041] 9A shows a cross-sectional view of a third configuration of a carbon working electrode suitable for use in the analyte sensor of the present disclosure. The carbon working electrode 502 differs from the carbon working electrode 500 shown in FIGS. 6A and 6B in that the carbon conductor pillars 512 are interconnected by a carbon conductor strip 550 disposed on the second side 516 of the dielectric substrate 510. The active areas 530 are disposed directly on the carbon strip 550, rather than on the individual carbon conductor pillars 512 in the carbon working electrode 501. The use of the carbon conductor strip 550 ensures that the active areas 530 are all electrically connected to the carbon conductor coating 520. If there is an incomplete via fill when forming one or more of the carbon conductor pillars 512, for example due to manufacturing issues, the electrical conductivity of a given active area 530 relative to the carbon conductor coating 520 can still be maintained by the carbon conductor strip 550. Furthermore, in an electrode configuration using the carbon conductor strip 550, the active area 530 does not need to directly cover each carbon conductor pillar 512.

[0042] 9B shows the corresponding top view of the carbon working electrode of FIG. 9A. The top view of the carbon working electrode 502 is similar to the top view of the carbon working electrode 501, as shown in FIG. 8B, except that the carbon conductor strip 550 covers the individual carbon conductor pillars 512, rather than the monolithic carbon conductor pillar 513 providing the entirety of exogenous carbon on the second surface 516 and providing the deposition surface for the active area 530. As with the carbon working electrode 501, the carbon conductor strip 550 is not completely covered by the active area 530 in the carbon working electrode 502, but the amount of exogenous carbon is much less than that present in a conventional carbon working electrode having a surface formed substantially of a carbon conductor. Furthermore, it should be understood that the number and spacing of the carbon conductor pillars 512 and active areas 530 are exemplary and non-limiting. In exemplary embodiments, the number of openings (vias) may range from about 1 to about 20, or from about 3 to about 15, or from about 2 to about 10, and the diameter of the openings may range from about 25 μm to about 200 μm. The carbon conductor strips interconnecting the carbon conductor pillars may range from about 25 μm to about 200 μm in width and about 100 μm to about 2000 μm in length.

[0043] Accordingly, the present disclosure provides an analyte sensor comprising a carbon working electrode having a dielectric substrate, one or more openings extending through the dielectric substrate and filled with carbon conductor pillars extending between a first side and a second side of the dielectric substrate, and a carbon conductor coating disposed on the first side of the dielectric substrate in direct contact with each of the carbon conductor pillars. One or more active areas are disposed on the second side of the dielectric substrate and in electrical communication with each of the carbon conductor pillars, the one or more active areas being responsive to an analyte. A mass transport limiting membrane may cover at least the one or more active areas.

[0044] The one or more openings through the dielectric substrate can be in the form of a plurality of vias through the dielectric substrate or a slot through the dielectric substrate. The carbon conductor pillars can be disposed within the vias or slots and completely fill the vias or slots. The active area can be disposed directly on the carbon conductor pillars disposed within any type of opening on the second side of the dielectric substrate.

[0045] Optionally, the plurality of vias through the dielectric substrate may be disposed on the second side of the dielectric substrate and electrically interconnected via a carbon conductor strip covering the plurality of vias. The active area may be disposed directly on the carbon conductor strip and does not necessarily cover the corresponding via. Although the carbon conductor strip introduces some extraneous carbon to the electrode surface, the improvement in manufacturing reliability may outweigh the enhancement in sensor performance in some cases. The layer thickness of the carbon conductor strip may range, for example, from about one micron (1 μm) to about twenty microns (20 μm).

[0046] The active region in any of the analyte sensors disclosed herein may comprise one or more analyte-responsive enzymes acting alone or in concert within an enzyme system. The one or more enzymes may be covalently attached to a polymer that comprises the active region, as well as one or more electron transfer agents located within the active region.

[0047] Examples of suitable polymers within each active region may include poly(4-vinylpyridine) and poly(N-vinylimidazole) or copolymers thereof, e.g., quaternized pyridine and imidazole groups serve as attachment sites for the electron transfer agent or enzyme(s). Other suitable polymers that may be present in the active region(s) include, but are not limited to, those described in U.S. Pat. No. 6,605,200 (hereby incorporated by reference in its entirety), such as poly(acrylic acid), styrene / maleic anhydride copolymer, methyl vinyl ether / maleic anhydride copolymer (GANTREZ polymer), poly(vinylbenzyl chloride), poly(allylamine), polylysine, poly(4-vinylpyridine) quaternized with carboxypentyl groups, and poly(sodium 4-styrenesulfonate).

[0048] The enzymes covalently attached to the polymer in the active region that can facilitate analyte detection are not believed to be particularly limited. Suitable enzymes may include enzymes capable of detecting glucose, lactate, ketones, or creatinine, etc. Any of these analytes may be detected in combination with one another in an analyte sensor capable of detecting multiple analytes. Suitable enzymes and enzyme systems for detecting these analytes are described below.

[0049] In some embodiments, the analyte sensor may comprise a glucose-responsive active region comprising a glucose-responsive enzyme disposed on the sensor tail. Suitable glucose-responsive enzymes may include, for example, glucose oxidase or glucose dehydrogenase (e.g., pyrroloquinoline quinone (PQQ) or cofactor-dependent glucose dehydrogenase, e.g., flavin adenine dinucleotide (FAD)-dependent glucose dehydrogenase or nicotinamide adenine dinucleotide (NAD)-dependent glucose dehydrogenase). Glucose oxidase and glucose dehydrogenase are distinguished by their ability to utilize oxygen as an electron acceptor when oxidizing glucose, where glucose oxidase may utilize oxygen as an electron acceptor, while glucose dehydrogenase transfers electrons to a natural or artificial electron acceptor, such as an enzyme cofactor. Exemplary enzyme-based detection schemes for analyzing glucose are further illustrated in Figures 10A to 10C, which utilize glucose oxidase or glucose dehydrogenase to facilitate detection. Both glucose oxidase and glucose dehydrogenase may be covalently attached to a polymer comprising a glucose-responsive active region and may exchange electrons with an electron transfer agent (e.g., an osmium (Os) complex or similar transition metal complex), which may also be covalently attached to the polymer. Suitable electron transfer agents are described in further detail below. Glucose oxidase may directly exchange electrons with the electron transfer agent (FIG. 10A), while glucose dehydrogenase may utilize a cofactor to improve electron exchange with the electron transfer agent (FIGS. 10B and 10C). The FAD cofactor may directly exchange electrons with the electron transfer agent, as shown in FIG. 10B. In contrast, the NAD cofactor may utilize diaphorase to facilitate electron transfer from the cofactor to the electron transfer agent, as shown in FIG. 10C. Further details regarding glucose-responsive active regions incorporating glucose oxidase or glucose dehydrogenase, and glucose detection therewith, may be found, for example, in co-owned U.S. Pat. No. 8,268,143.

[0050] 11A-11C show enzyme systems configured to detect ketones. Further details regarding enzyme systems responsive to ketones can be found in co-owned U.S. Patent Application No. 16 / 774,835, entitled "Analyte Sensors and Sensing Methods Featuring Dual Detection of Glucose and Ketones," filed January 28, 2020, and published as U.S. Patent Application Publication No. . In the enzyme system shown in FIG. 11A, β-hydroxybutyrate serves as a surrogate for ketones formed in vivo, which upon reaction with an enzyme system including β-hydroxybutyrate dehydrogenase (HBDH) and diaphorase facilitates ketone detection within a ketone-responsive active area disposed on the surface of at least one working electrode, as further described herein. Within the ketone-responsive active area, β-hydroxybutyrate dehydrogenase converts β-hydroxybutyrate and oxidized nicotinamide adenine dinucleotide (NAD) to ketones. + ) into acetoacetate and reduced nicotinamide adenine dinucleotide (NADH), respectively. The term "nicotinamide adenine dinucleotide (NAD)" should be understood to include the phosphate-bound forms of the aforementioned enzyme cofactors. That is, the use of the term "NAD" herein refers to NAD + It refers to both phosphate and NADH phosphate, specifically the diphosphate that combines two nucleotides, one of which contains an adenine nucleobase and the other of which contains a nicotinamide nucleobase. +The / NADH enzyme cofactor helps facilitate the concerted enzymatic reaction disclosed herein. Once formed, NADH can undergo diaphorase-mediated oxidation, and the electrons transferred during this process provide the basis for ketone detection at the working electrode. Thus, there is a 1:1 molar correspondence between the amount of electrons transferred to the working electrode and the amount of β-hydroxybutyrate converted. The transfer of electrons to the working electrode can occur with the additional mediation of an electron transfer agent, such as an osmium (Os) compound or a similar transition metal complex, as described in more detail below. Albumin can further be present as a stabilizer within the active region. β-hydroxybutyrate dehydrogenase and diaphorase can be covalently attached to a polymer with a ketone-responsive active region. NAD + may or may not be covalently attached to a polymer, + If NAD is not covalently linked, it is difficult to separate NAD from the ketone-responsive active region by, for example, a mass-transport limiting membrane that is permeable to ketones. + may be physically held within the ketone-responsive active region.

[0051] Other suitable chemistries for enzymatically detecting ketones are shown in Figures 11B and 11C. In both cases, there is again a 1:1 molar correspondence between the amount of electrons transferred to the working electrode and the amount of β-hydroxybutyrate converted, thereby providing the basis for ketone detection.

[0052] As shown in FIG. 11B, β-hydroxybutyrate dehydrogenase (HBDH) again reacts with β-hydroxybutyrate and NAD +NADH oxidase may convert β-hydroxybutyrate dehydrogenase to acetoacetate and NADH, respectively. Instead of electron transfer to the working electrode being completed by diaphorase (see FIG. 11A) and a suitable redox mediator, the reduced form of NADH oxidase (NADHOx(Red)) undergoes a reaction to form the corresponding oxidized form (NADHOx(Ox)). NADHOx(Red) may then be reformed through reaction with molecular oxygen to produce superoxide, which may then undergo subsequent conversion to hydrogen peroxide under superoxide dismutase (SOD) mediation. Hydrogen peroxide may then undergo oxidation at the working electrode to provide a signal that can be correlated to the amount of ketone originally present. SOD may be covalently attached to a polymer in a ketone-responsive active region according to various embodiments. Similar to the enzyme system shown in FIG. 11A, β-hydroxybutyrate dehydrogenase and NADH oxidase may be covalently attached to a polymer in a ketone-responsive active region, and NAD + The NAD+ may or may not be covalently bound to a polymer in the ketone responsive active region. If the NAD+ is not covalently bound, it may be physically held within the ketone responsive active region, and a membrane polymer may be used to hold the NAD+ within the ketone responsive active region. + Promote retention of

[0053] As shown in FIG. 11C, another enzymatic detection chemistry for ketones utilizes β-hydroxybutyrate dehydrogenase (HBDH) to produce β-hydroxybutyrate and NAD. + can be converted to acetoacetate and NADH, respectively. The electron transfer cycle in this case is + The oxidation of NADH by 1,10-phenanthroline-5,6-dione to reform β-hydroxybutyrate dehydrogenase is completed by the oxidation of NADH by 1,10-phenanthroline-5,6-dione to reform β-hydroxybutyrate dehydrogenase, which then transfers electrons to the working electrode. 1,10-phenanthroline-5,6-dione may or may not be covalently attached to a polymer in the ketone-responsive active region. Similar to the enzyme system shown in FIG. 11A, β-hydroxybutyrate dehydrogenase may be covalently attached to a polymer in the ketone-responsive active region, and .... +may or may not be covalently attached to the polymer in the ketone-responsive active region. The inclusion of albumin in the active region can provide a surprising improvement in response stability. A suitable membrane polymer can be used to inhibit the binding of NAD to the ketone-responsive active region. + This may promote retention of

[0054] In some embodiments, the analyte sensor may further comprise a creatinine-responsive active region comprising an enzyme system that operates in concert to facilitate detection of creatinine. A suitable enzyme system that may be used to detect creatinine in the analyte sensors disclosed herein is shown in FIG. 12 and described in further detail below. Further details regarding enzyme systems responsive to creatinine can be found in U.S. Patent Application Publication No. 2010 / 0139994, filed September 25, 2019, and incorporated herein by reference. No. 16 / 774,835, entitled "Analyte Sensors and Sensing Methods for Detecting Creatine," published as US Pat. No. 6,313,315.

[0055] As shown in Figure 12, 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 amidohydrolase (CRH). Neither of these reactions produces an electron flow (e.g., oxidation or reduction) that provides the basis for electrochemical detection of creatinine.

[0056] With further reference to FIG. 12, sarcosine generated via the hydrolysis of creatine may 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 may also be generated in the presence of oxygen. The reduced form of sarcosine oxidase may then undergo reoxidation in the presence of an oxidized form of an electron transfer agent (e.g., an Os(III) complex), thereby generating the corresponding reduced form of the electron transfer agent (e.g., an Os(II) complex) and delivering electron flow to the working electrode.

[0057] Oxygen may interfere with the concerted series of reactions used to detect creatinine according to the disclosure above. Specifically, the reduced form of sarcosine oxidase may undergo reaction 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 electrons do not 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, it is believed that the oxidation of the reduced form of sarcosine oxidase by oxygen occurs faster than the oxidation promoted by the electron transfer agent. Hydrogen peroxide is also formed in the presence of oxygen.

[0058] The desired reaction pathway for facilitating the detection of creatinine shown in FIG. 12 can be promoted by including an oxygen scavenger in close proximity to the enzyme system. A variety of oxygen scavengers and their placement can be suitable, including oxidase enzymes such as glucose oxidase. Small molecule oxygen scavengers can also be suitable, but they can be completely consumed before the sensor life is completely exhausted. In contrast, the enzyme can undergo reversible oxidation and reduction, thereby resulting in a longer sensor life. By preventing the oxidation of the reduced sarcosine oxidase by oxygen, a slower electron exchange reaction with the electron transfer agent can occur, thereby allowing the generation of a current at the working electrode. The magnitude of the current generated is proportional to the amount of creatinine initially reacted.

[0059] The oxygen scavenger used to promote the desired reaction pathway in Figure 12 may be an oxidase enzyme in any embodiment of the present disclosure. Any oxidase enzyme may be used to promote oxygen scavenging in proximity to the enzyme system, provided that a suitable substrate for the enzyme is also present, thereby providing a reagent for reacting with oxygen in the presence of the oxidase enzyme. Oxidase enzymes that may be suitable for oxygen scavenging 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 desirable oxidase enzyme to promote oxygen scavenging due to the ready availability of glucose in various body fluids. Reaction 1 below illustrates the enzymatic reaction promoted by glucose oxidase resulting in oxygen scavenging. [ka] Although the concentration of bioavailable lactate is lower than that of glucose, it is still sufficient to facilitate oxygen capture.

[0060] An oxidase enzyme, such as glucose oxidase, may be located in any location suitable for facilitating oxygen capture in an analyte sensor disclosed herein. For example, glucose oxidase may be located on the sensor tail such that the glucose oxidase is functional and / or non-functional to facilitate glucose detection. When non-functional to facilitate glucose detection, the glucose oxidase may be located on the sensor tail such that electrons generated during glucose oxidation are prevented from reaching the working electrode, such as by electrically isolating the glucose oxidase from the working electrode.

[0061] In some embodiments, the analyte sensor may comprise a lactate-responsive active region comprising a lactate-responsive enzyme disposed on the sensor tail. Suitable lactate-responsive enzymes may include, for example, lactate oxidase. Lactate oxidase or other lactate-responsive enzymes may be covalently attached to a polymer comprising the lactate-responsive active region and may exchange electrons with an electron transfer agent (e.g., an osmium (Os) complex or similar transition metal complex), which may also be covalently attached to the polymer. Suitable electron transfer agents are described in more detail below. As described in more detail in co-owned US Patent Publication No. 20190320947, which is incorporated herein by reference in its entirety, albumin, such as human serum albumin, may be present in the lactate-responsive active region to stabilize the sensor response. Lactate levels may change in response to a number of environmental or physiological factors, including, for example, feeding, stress, exercise, sepsis or septic shock, infection, hypoxia, or the presence of cancerous tissue.

[0062] In some embodiments, the analyte sensor may comprise an active area responsive to pH. Suitable analyte sensors configured to determine pH are described in commonly owned U.S. Patent Application Publication No. 20200060592, incorporated herein by reference. Such an analyte sensor may comprise a sensor tail comprising a first working electrode and a second working electrode, the first active area located on the first working electrode comprising a material having a pH-dependent redox chemistry, and the second active area located on the second working electrode comprising a material having a redox chemistry that is substantially invariant to pH. By obtaining a difference between the first signal and the second signal, the difference may be correlated to the pH of the fluid to which the analyte sensor is exposed.

[0063] Two different types of active regions may be disposed on a single working electrode, such as the carbon working electrode described above, and spaced apart from each other. Each active region may have a redox potential, and the redox potential of the first active region is sufficiently separated from the redox potential of the second active region to allow independent generation of a signal from one of the active regions. In non-limiting examples, the redox potentials may differ 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 by the working electrochemical window in vivo. By sufficiently separating the redox potentials of the two active regions from each other in magnitude, electrochemical reactions can occur in one of the two active regions (i.e., the first active region or the second active region) without substantially including electrochemical reactions in the other active region. Thus, a signal from either the first active region or the second active region can be independently generated at or above its corresponding redox potential (the lower redox potential) but below the redox potential of the other active region. The differential signal can allow the signal contribution from each analyte to be separated.

[0064] Some or other embodiments of the analyte sensor disclosed herein may feature two different active areas disposed on the surface of separate working electrodes. Such an analyte sensor may comprise at least a first working electrode and a second working electrode, a sensor tail comprising a first active area disposed on the surface of the first working electrode, and a second active area disposed on the surface of the second working electrode and responsive to a different analyte. A membrane may cover at least one of the first active area and the second active area. The membrane may be a mass transport limiting membrane and may comprise a multi-component membrane, where the membrane covers at least one of the active areas. The multi-component membrane may comprise a bilayer of two different membrane polymers, or a mixture of two different membrane polymers, where one of the membrane polymers covers the other active area. Such a multi-component membrane may be deposited by a dip coating technique, in a non-limiting example.

[0065] Other suitable mass transport limiting membranes may be deposited by in situ polymerization, such as in situ photopolymerization, as discussed in more detail below.

[0066] Electron transfer agents may be present in any of the active areas disclosed herein. A suitable electron transfer agent may facilitate the transfer of electrons to an adjacent working electrode after one or more analytes undergo an enzymatic redox reaction in the corresponding active area, thereby generating an electron flow indicative of the presence of a particular analyte. The amount of current generated is proportional to the amount of analyte present. Depending on the sensor configuration used, the electron transfer agents in active areas responsive to different analytes may be the same or different. For example, when two different active areas are placed on the same working electrode, the electron transfer agents in each active area 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 area may be the same or different, since each working electrode may be detected separately.

[0067] Suitable electron transfer agents may include electroreducible and electrooxidizable ions, complexes, or molecules (e.g., quinones) that have redox potentials several hundred millivolts higher or lower than 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. Further 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 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.

[0068] An active region suitable for detecting any of the analytes disclosed herein may comprise a polymer to which an electron transfer agent is covalently attached. Any of the electron transfer agents disclosed herein may comprise a suitable functional group to facilitate covalent attachment to the polymer in the active region. Examples of suitable 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. Suitable polymers 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 containing monomer units such as, for example, styrene, acrylamide, methacrylamide, or acrylonitrile. When two or more different active regions are present, the polymers in each active region may be the same or different.

[0069] The electron transfer agent may be covalently attached to the polymer in the active region by polymerizing a monomer unit having a covalently attached electron transfer agent, or the electron transfer agent may be reacted separately with the polymer after the polymer has already been synthesized. A bifunctional spacer can covalently attach the electron transfer agent to the polymer in the active region, with a first functional group reactive to the polymer (e.g., a functional group capable of quaternizing a pyridine nitrogen atom or an imidazole nitrogen atom) and a second functional group reactive to the electron transfer agent (e.g., a functional group reactive to a ligand that coordinates to a metal ion).

[0070] Similarly, one or more enzymes in an active region may be covalently bound to the polymer that comprises the active region. 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, or at least one enzyme may be non-covalently bound to the polymer, such that the non-covalently bound enzyme is physically entrapped within the polymer. Covalent binding of the enzyme(s) to the polymer in a given active region may be via a crosslinker introduced with a suitable crosslinker. Crosslinkers suitable for reaction with free amino groups in the enzyme (e.g., free side chain amines in lysine) may include, for example, crosslinkers such as polyethylene glycol diglycidyl ether (PEGDGE) or other polyepoxides, cyanuric chloride, N-hydroxysuccinimide, imidoesters, epichlorohydrin, or derivatized variants thereof. Crosslinkers suitable for reaction with free carboxylic acid groups in the enzyme may include, for example, carbodiimides. Cross-linking of the enzyme to the polymer is generally intermolecular, but in some embodiments can be intramolecular, hi certain embodiments, all of the enzymes within a given active region can be covalently bound to the polymer.

[0071] The electron transfer agent and / or enzyme(s) may be bound to the polymer in the active area through means other than covalent bonds. In some embodiments, the electron transfer agent and / or enzyme(s) may be ionically or coordinatively bound to the polymer. For example, a charged polymer may be ionically bound to an oppositely charged electron transfer agent or enzyme(s). In yet other embodiments, the electron transfer agent and / or enzyme(s) may be physically entrapped within the polymer without being bound to the polymer. The physically entrapped electron transfer agent and / or enzyme(s) may still interact appropriately with the fluid and facilitate detection of the analyte without substantially leaching from the active area.

[0072] The polymer in the active region(s) contains NAD that is not covalently attached to the polymer. +or another cofactor may be selected to have limited outward diffusion, which may facilitate reasonable sensor lifetimes (days to weeks) while still allowing sufficient inward analyte diffusion to facilitate detection.

[0073] The active areas in the analyte sensors disclosed herein are approximately 0.01 mm in size. 2 From about 1 mm 2 Or about 0.05 mm 2 from about 0.3 mm 2 Each active region may comprise one or more individual spots (e.g., from 1 to about 20 spots, or even more individual spots), which may range from 1 to 20 individual spots, although larger or smaller individual spots within the active region are also contemplated herein. When two different active regions are present, the number and / or size of the individual spots may be the same or different for each type of active region.

[0074] It should also be understood that the sensitivity (output current) of an analyte sensor to a given analyte or combination of analytes may be varied by varying the coverage (area or size) of the active regions, the area ratio of the active regions to each other, the identity, thickness and / or composition of the mass transport limiting membrane covering the active regions. Variations of these parameters may be readily made by one of ordinary skill in the art given the benefit of the disclosure herein.

[0075] In more specific embodiments, the analyte sensor of the present disclosure may include a sensor tail configured to be inserted into tissue. Suitable tissues are not believed to be particularly limited and are described in more detail above. Similarly, considerations for deploying the sensor tail at a particular location within a given tissue, such as the dermis layer of the skin, are described above.

[0076] In certain embodiments of the present disclosure, the mass transport limiting membrane covering one or more active regions may comprise a crosslinked polyvinylpyridine homopolymer or copolymer. The composition of the mass transport limiting membrane may be the same as or different from the mass transport limiting membrane covering the different types of active regions. When the membrane composition is different at two different locations, the membrane may comprise a bilayer membrane or a homogeneous mixture of two different membrane polymers, one of which may be a crosslinked polyvinylpyridine or polyvinylimidazole homopolymer or copolymer. Suitable techniques for depositing the mass transport limiting membrane on the active region(s) may include, for example, spray coating, painting, inkjet printing, screen printing, stenciling, roller coating, dip coating, and the like, and any combination thereof. Dip coating techniques may be particularly desirable for polyvinylpyridine and polyvinylimidazole polymers and copolymers.

[0077] Other suitable mass transport limiting membranes may be in situ polymerized on the surface of one or more working electrodes. A particular example of a mass transport limiting membrane that can be formed in situ may comprise a photopolymerized (photocured) mass transport limiting membrane. When multiple types of active areas are present, a photopolymerized mass transport limiting membrane may be selectively formed on each type of active area. That is, a mass transport limiting membrane having a first portion may cover the first type of active area, and a second portion, different in composition from the first portion, may cover the second type of active area. The mass transport limiting membrane may or may not be continuous between two or more active areas. More specifically, such a photopolymerized mass transport limiting membrane may be formed by depositing one or more monomers on a second surface in contact with one or more active areas and photopolymerizing the one or more monomers. Suitable deposition techniques for depositing the monomers include, for example, spraying, screen printing, or any combination thereof. Film chemistries that may be obtained through photopolymerization include, for example, acrylate polymers and copolymers, thiol-ene copolymers, or any combination thereof. Polymerization to form both of these types of membranes can occur under conditions that do not interfere with the sensing chemistry in the active area. Additional in situ crosslinking can also occur on the surface of the working electrode(s) in the process forming a mass transport limiting membrane in situ.

[0078] In a non-limiting embodiment, a mass transport limiting membrane suitable for incorporation in an analyte sensor of the present disclosure can include a polymer or copolymer that includes one or more acrylate monomers. The term "acrylate monomer" refers to acrylic acid, methacrylic acid, or derivatives thereof. A monomer that can be either an acrylate or a methacrylate is referred to herein as a "(meth)acrylate monomer." That is, the designation of a particular monomer as a "(meth)acrylate" refers to both the particular acrylate monomer and the corresponding methacrylate monomer form. Suitable acrylate monomers that may be present in the mass transport limiting membrane of the present disclosure include, for example, 2-hydroxyethyl (meth)acrylate, poly(ethylene glycol) methyl ether (meth)acrylate, alkyl ether poly(ethylene glycol) (meth)acrylate, poly(ethylene glycol) (meth)acrylate, poly(propylene glycol) (meth)acrylate, alkyl ether poly(propylene glycol) (meth)acrylate, isobutyl (meth)acrylate, alkyl (meth)acrylate, 2-(trimethylsilyloxy)ethyl (meth)acrylate, 3-[tris(trimethylsiloxy)silyl]propyl (meth)acrylate, N,N-dimethylacrylamide, glycidyl (meth)acrylate, or any combination thereof. Glycidyl (meth)acrylate may be further functionalized in some cases. Crosslinkable acrylates such as di(ethylene glycol) di(meth)acrylate, poly(ethylene glycol) di(meth)acrylate, trimethylolpropane triacrylate, or any combination thereof, may be present in combination with any of the aforementioned (meth)acrylate monomers. Any molecule containing two or more alkene groups of sufficient reactivity may also function as a crosslinker when forming the mass transport limiting membrane. The amount of crosslinkable (meth)acrylate may be selected to provide the desired degree of crosslinking, for example, a weight percentage of crosslinkable (meth)acrylate up to about 1% by weight based on the total weight of monomers.The selection of a particular (meth)acrylate monomer, crosslinkable (meth)acrylate or similar polyene crosslinker, or any combination thereof, and the ratio between them, can be selected to provide sufficient permeability for a given analyte of interest. For example, two or more (meth)acrylate monomers with different levels of hydrophilicity and hydrophobicity can be selected, and their ratios can be altered to provide specific membrane properties depending on the water content and hydrophilicity or hydrophobicity of the analyte. Membranes containing glycidyl (meth)acrylate can also be crosslinked with a diol or triol crosslinker, such as ethylene glycol, propylene glycol, butanediol, hexanediol, glycerol, poly(ethylene glycol), poly(propylene glycol), or any combination thereof.

[0079] In addition, (meth)acrylamides, alkyl or dialkyl (meth)acrylamides, (meth)acrylic acids, or alkyl (meth)acrylate esters can be copolymerized with any of the aforementioned (meth)acrylate monomers or crosslinkable acrylates. Other olefinically unsaturated monomers can also be copolymerized with any of the aforementioned (meth)acrylate monomers. Other monomers that can be copolymerized include, for example, alpha-olefins such as ethylene, propylene, butene, pentene, hexene, heptene, octene, nonene, decene, undecene, dodecene, or mixtures thereof. Alpha-olefins that are liquid at room temperature may be particularly desirable. Such comonomers can be included to facilitate further adjustment of the physical properties of the resulting membrane. For example, one or more alpha-olefin monomers can be added to increase the hydrophobicity of the membrane.

[0080] Some acrylate monomers may undergo photopolymerization or thermal polymerization in the absence of an initiator. Other acrylate monomers may undergo photopolymerization in the presence of a suitable initiator that generates radical species when exposed to electromagnetic radiation such as ultraviolet light (e.g., from a mercury lamp). In non-limiting embodiments, suitable photoinitiators may include, for example, 2,2-dimethoxy-2-phenylacetophenone, camphorquinone, azo compounds, and peroxides (e.g., benzoyl peroxide with N,N-dimethyltoluidine accelerator). Other suitable photoinitiators may include, but are not limited to, Norrish Type I initiators (e.g., 2,2-dimethoxy-2-phenylacetophenone, hydroxyacetophenone, aminoacetophenone, and acetophenone phosphine oxide, etc.), Norrish Type II initiators (e.g., benzophenone, benzyl formate, and thioxanthone, etc., optionally with amine synergistic accelerators), phenol glyoxalic acid methyl ester, alpha amino ketones, benzoyl diphenyl phosphine oxide, or any combination thereof. CAROCUR, IRGACUR, and LUCIRIN photoinitiators from BASF are representative examples. Suitable photoinitiators may be present in an amount of up to about 1% by weight, based on the total weight of monomers.

[0081] Thiol-ene copolymers may also be suitably incorporated as mass transport limiting membranes in the analyte sensors disclosed herein. Advantageously, thiol-ene polymers may be formed in air, as opposed to (meth)acrylate polymers, which may require the use of inert air for sufficient polymerization to occur. Thiol-ene polymers may be obtained by reacting a monomer containing two or more thiol groups with a monomer containing two or more non-conjugated alkene groups. Any of the above photoinitiators may be used as needed. Monomers with two thiol groups or two non-conjugated alkene groups may provide linear polymers. Monomers with three or more thiol groups or three or more non-conjugated alkene groups may provide various degrees of crosslinking. Any type of non-crosslinkable monomer may be used, for example, to reduce crosslink density. Crosslinkable monomers, which may be tripodal or tetrapodal in nature, may have variable length spacers between the central atom and the terminal thiol or terminal alkene groups. The length of the spacer and the amount of crosslinkable monomer may also affect the crosslink density.

[0082] Particularly suitable monomers containing thiol groups may be tetrapodal, with each arm of the tetrapodal structure terminating in a thiol group.The following compounds 1 and 2 are illustrative examples of monomers containing thiol groups arranged in a tetrapodal configuration that may be suitable for use in forming a mass transport limiting membrane by photopolymerization. [ka] Compound 3 below (dithiol) can be used to reduce crosslink density by introducing linear moieties into the thiol-ene polymer. Smaller dithiols such as ethanedithiol and propanedithiol can be used to reduce crosslink density as well as the larger polyether dithiols such as compound 3. Similarly, trithiols can be used to reduce crosslink density. [ka]

[0083] Particularly suitable ene monomers can be dipodal, tripodal, or tetrapodal, depending on the desired crosslink density. Compounds 4 to 6 are illustrative examples of dipodal, tripodal, and tetrapodal ene monomers, respectively, where A is a spacer group that is not particularly limited in structure and can optionally contain one or more heteroatoms. Compound 4 Compound 5 Compound 6 Compounds 7 through 10 below are illustrative examples of particular ene monomers that may be suitable for forming mass transport limiting membranes by in situ photopolymerization. [ka]

[0084] The photopolymerized mass transport limiting membrane may be present in an analyte sensor with a carbon working electrode as described above, or the photopolymerized mass transport limiting membrane may be present in an analyte sensor with a conventional carbon working electrode or any other type of working electrode. In either case, the photopolymerized mass transport limiting membrane may be advantageous since it can be easily tailored to meet the specific needs of a particular application. Furthermore, the photopolymerized mass transport limiting membrane may be obtained by deposition of an easily dispensed monomer, which may be deposited at one or more specific locations by spraying or screen printing techniques. As a result of the deposition specificity, photopolymerized mass transport limiting membranes with different compositions may cover different types of active areas. Alternatively, the photopolymerized mass transport limiting membrane may cover a first type of active area, while a second type of active area may be covered with a polyvinylpyridine or polyvinylimidazole polymer or copolymer deposited by dip coating.

[0085] Thus, some analyte sensors of the present disclosure may include a first working electrode, one or more first active areas disposed on the first working electrode and responsive to a first analyte, and a first photopolymerized mass transport limiting membrane formed directly on the first working electrode and covering at least one of the one or more first active areas. The first working electrode may be a first carbon electrode, such as the carbon electrodes described in more detail above. Conventional carbon working electrodes may also be suitable. In a non-limiting embodiment, the first active area may include an analyte-responsive enzyme or enzyme system. Any of the analytes discussed in more detail above may be assayed by the first active area.

[0086] The analyte sensor may also include a second working electrode and one or more second active areas disposed on the second working electrode that are responsive to a second analyte different from the first analyte. The second working electrode may be a second carbon electrode, such as the carbon electrode described in more detail above, or a conventional carbon working electrode may also be suitable. A second mass transport limiting membrane may cover at least one or more second active areas and may be compositionally different from the first photopolymerized mass transport limiting membrane. The second mass transport limiting membrane may comprise a dip-coated polyvinylpyridine or polyvinylimidazole polymer or copolymer, and more desirably, the second photopolymerized mass transport limiting membrane may be compositionally different from the first mass transport limiting membrane. The first photopolymerized mass transport limiting membrane and / or the second photopolymerized mass transport limiting membrane may be discontinuous such that the membrane does not extend between adjacent spots of a given active area or between two different active areas configured to detect different analytes.

[0087] Thus, a method for forming an analyte sensor with a photopolymerized mass transport limiting membrane can include providing an analyte sensor with at least one first working electrode having one or more first active areas disposed thereon responsive to a first analyte, applying one or more first monomers onto the first working electrode in contact with the one or more first active areas, and polymerizing in situ, such as by photopolymerization, the one or more first monomers on the first working electrode to form a first mass transport limiting membrane covering at least the one or more first active areas. In a non-limiting embodiment, the photopolymerization can include exposing the one or more first monomers (e.g., a mixture of a first monomer and a second monomer) to ultraviolet light and optionally a photoinitiator. When the analyte sensor further comprises a second working electrode, the method may further comprise applying one or more second monomers onto the second working electrode in contact with the one or more second active areas, and polymerizing, such as by photopolymerization, the one or more second monomers onto the second working electrode to form a second mass transport limiting membrane covering at least the one or more second active areas. The second mass transport limiting membrane may have the same composition as the first mass transport limiting membrane, or may be different in composition. In various embodiments, the first mass transport limiting membrane and the second mass transport limiting membrane may both be photopolymerized.

[0088] The analyte sensor can be prepared as an assembly using an electrode material (e.g., carbon) having multiple active areas disposed thereon. One or more first monomers can be applied to the active areas, such as by syringe deposition of a solution containing one or more first monomers, and polymerization can occur as described above. The solution containing one or more first monomers can be deposited at about 100 to 200 nL, in a non-limiting example. 365 nm and 1 to 30 mW / cm 2 After polymerization, such as with UV irradiation at 1000 nm of radiation power for up to 5 minutes, individual analyte sensors can be isolated by laser cutting the electrode material and, optionally, the mass transport limiting membrane.

[0089] Embodiments disclosed herein include the following.

[0090] A. Analyte Sensor Having a Carbon Working Electrode The analyte sensor includes a carbon working electrode comprising a dielectric substrate, one or more openings extending through the dielectric substrate and each filled with a carbon conductor pillar extending between a first side and a second side of the dielectric substrate, a carbon conductor coating disposed on the first side of the dielectric substrate in direct contact with each of the carbon conductor pillars, and a dielectric coating disposed on the carbon conductor coating, one or more active areas located on the second side of the dielectric substrate in electrical communication with each of the carbon conductor pillars and responsive to an analyte, and a mass transport limiting membrane covering at least the one or more active areas.

[0091] B. A method for fabricating an analyte sensor having a carbon working electrode, the method comprising providing a dielectric substrate having one or more openings extending through the dielectric substrate between a first side and a second side, filling the one or more openings with a carbon conductor to form carbon conductor pillars therein, depositing a carbon conductor coating on the first side of the dielectric substrate such that the carbon conductor coating directly contacts each carbon conductor pillar, depositing a dielectric coating on the carbon conductor coating, forming one or more active areas on the second side of the dielectric substrate in electrical communication with the carbon conductor pillars in the one or more openings and responsive to an analyte, and depositing a mass transport limiting membrane on at least the one or more active areas.

[0092] C. Analyte Sensor with Mass Transport Limiting Membrane The analyte sensor includes a first working electrode, one or more first active areas responsive to a first analyte disposed on the first working electrode, and a first photopolymerized mass transport limiting membrane formed directly on the first working electrode and covering at least the one or more first active areas.

[0093] D. Method for manufacturing an analyte sensor having a mass transport limiting membrane The method includes providing an analyte sensor comprising at least one first working electrode having one or more first active areas disposed thereon responsive to a first analyte, applying one or more first monomers onto the first working electrode in contact with the one or more first active areas, and in situ polymerizing the one or more first monomers on the first working electrode to form a first mass transport limiting membrane covering at least the one or more first active areas.

[0094] Each of embodiments A through D may have one or more of the following additional elements in any combination.

[0095] Element 1: The one or more openings comprise a plurality of vias extending through the dielectric substrate.

[0096] Element 2: Each via has an active area disposed directly on a carbon conductor pillar disposed therein.

[0097] Element 3: The analyte sensor further comprises a carbon conductor strip disposed on the second surface of the dielectric substrate and covering the plurality of vias, with the one or more active areas disposed directly on the carbon conductor strip.

[0098] Element 4: The one or more openings comprise a slot extending through the dielectric substrate.

[0099] Element 5: Multiple active regions are disposed directly on the carbon conductor pillars that are placed within the slots.

[0100] Element 6: The one or more active regions comprise one or more analyte-responsive enzymes.

[0101] Element 7: The mass transport limiting membrane is a photopolymerized mass transport limiting membrane.

[0102] Element 8: A photopolymerized mass transport limiting membrane is selectively formed over one or more active regions.

[0103] Element 9: The mass transport limiting membrane comprises an acrylate polymer or copolymer, a thiol-ene copolymer, or any combination thereof.

[0104] Element 10: A carbon working electrode is disposed on the sensor tail configured to be inserted into tissue.

[0105] Element 11: The method further comprises depositing a carbon conductor strip covering the plurality of vias on the second side of the dielectric substrate, with the one or more active areas disposed directly on the carbon conductor strip.

[0106] Element 12: The mass transport limiting membrane is deposited by dip coating.

[0107] Element 13: A mass transport limiting membrane is polymerized in situ onto one or more active areas.

[0108] Element 14: Mass transport limiting membrane is a photopolymerized mass transport limiting membrane formed by depositing one or more monomers on a second surface of the dielectric substrate in contact with the one or more active regions and photopolymerizing the one or more monomers.

[0109] Element 15: The photopolymerized mass transport limiting membrane comprises an acrylate polymer or copolymer, a thiol-ene copolymer, or any combination thereof.

[0110] Element 16: The first photopolymerized mass transport limiting membrane comprises an acrylate polymer or copolymer, a thiol-ene copolymer, or any combination thereof.

[0111] Element 17: The analyte sensor further comprises a second working electrode, one or more second active areas disposed on the second working electrode and responsive to a second analyte different from the first analyte, and a second mass transport limiting membrane covering at least the one or more second active areas and having a different composition than the first photopolymerized mass transport limiting membrane.

[0112] Element 18: The second mass transport limiting membrane is a second photopolymerized mass transport limiting membrane that is compositionally different from the first photopolymerized mass transport limiting membrane.

[0113] Element 19: The first photopolymerized mass transport limiting membrane is crosslinked.

[0114] Element 20: The first photopolymerized mass transport limiting membrane is discontinuous.

[0115] Element 21: A first photopolymerized mass transport limiting membrane is disposed substantially over the one or more active areas.

[0116] Element 22: The one or more first active regions comprise one or more analyte-responsive enzymes.

[0117] Element 23: A first working electrode disposed on the sensor tail configured to be inserted into tissue.

[0118] Element 24: The first mass transport limiting membrane is a photopolymerized mass transport limiting membrane formed by photopolymerizing one or more first monomers.

[0119] Item 25: Applying the one or more first monomers comprises screen printing the one or more first monomers, spraying the one or more first monomers, or any combination thereof.

[0120] Element 26: The analyte sensor further comprises a second working electrode having one or more second active areas disposed thereon, the one or more second active areas responsive to a second analyte different from the first analyte, and the method further comprises applying one or more second monomers onto the second working electrode in contact with the one or more second active areas, and in situ polymerizing the one or more second monomers on the second working electrode to form a second mass transport limiting membrane different in composition from the first mass transport limiting membrane and covering at least the one or more second active areas.

[0121] Element 27: The second mass transport limiting membrane is a photopolymerized mass transport limiting membrane formed by photopolymerizing one or more second monomers.

[0122] Element 28: The first mass transport limiting membrane is discontinuous.

[0123] Element 29: A first mass transport limiting membrane is selectively formed on the one or more first active regions.

[0124] As non-limiting examples, exemplary combinations applicable to A include, but are not limited to, 1 and 2, 1 and 3, 1 through 3, 1 and 6, 1 and 7, 1 and 8, 1 and 9, 1 and 10, 4 and 5, 4 and 6, 4 through 6, 4 and 7, 4 and 5 and 7, 4 and 8, 4 and 5 and 8, 4 and 9, 4 and 5 and 9, 4 and 10, and 4 and 5 and 10. Exemplary combinations applicable to B include, but are not limited to, 1 and 2, 1 and 11, 1 and 2 and 11, 1 and 6, 1 and 7, 1 and 8, 1 and 9, 1 and 10, 4 and 5, 4 and 6, 4 to 6, 4 and 7, 4 and 5 and 7, 4 and 8, 4 and 5 and 8, 4 and 9, 4 and 5 and 9, 4 and 10, 4 and 5 and 10, 1 and 12, 1 and 2 and 12, 1 and 13, 1 and 2 and 13, 1 and 2 and 11 and 13, 4 and 12, 4 and 5 and 12, 4 and 13, 4 and 5 and 13, 1 and 13 and 14, 4 and 13 and 14, 1 and 13 to 15, and 4 and 13 to 15. Exemplary combinations applicable to C include, but are not limited to, 16 and 17, 16 to 18, 16 and 19, 16 and 20, 16 and 21, 16 and 22, 16 and 23, 17 and 18, 17 and 19, 17 and 20, 17 and 21, 17 and 22, 17 and 23, 20 and 21, 20 and 22, 20 and 23, 21 and 22, 21 and 23, and 22 and 23. Exemplary combinations applicable to D include, but are not limited to, 16 and 24, 16 and 24 and 25, 24 and 25, 16 and 24 and 26, 24 and 26, 24 and 26 and 27, 16 and 24 and 28, 24 and 28, 16 and 24 and 26 and 27, 24 and 29, 16 and 24 and 29, 26 and 27, 26 and 28, 26 to 28, 26 and 29, 26 and 27 and 29, and 28 and 29.

[0125] To facilitate a better understanding of the embodiments described herein, the following examples of various representative embodiments are given. The following examples should not be read to limit or define the scope of the invention.

[0126] Working Example General procedure for sensor fabrication. The appropriate sensing layer chemistry is first applied to a 0.05 to 0.3 mm thick film. 2 The sensing layer chemicals were deposited on the working electrode (e.g., a carbon working electrode) as a group of separate dots or slots with an area of ​​1.5 mm × 2.5 mm. Deposition of the sensing layer chemicals was typically performed with a piezoelectric deposition device. A microsyringe was then used to manually deposit about 100 to 200 nL of monomer solution containing monomer(s), crosslinker, and initiator over a working electrode area of ​​about 1.5 mm × 2.5 mm. The resulting construct was then transferred into an argon-filled chamber containing a UV lamp emitting at 365 nm. A mass transport limiting membrane was then placed over the working electrode at 1 to 30 mW / cm. 2 The plates were then photopolymerized for up to 5 minutes at 1000 W of UV power. Individual sensors were then isolated by laser cutting.

[0127] The active regions for the various test substances utilized a poly(vinylpyridine)-bound transition metal complex as the electron transfer agent having the structure shown in Formula 11 below. Further details regarding this transition metal complex and electron transfer therewith are provided in co-owned U.S. Patent No. 6,605,200, which is incorporated by reference above. The subscripts for each monomer indicate exemplary atomic ratios and do not indicate any particular monomer order. [ka]

[0128] Example 1: Glucose sensor coated with a photopolymerized film Glucose-responsive active regions were deposited using the formulations shown in Table 1 below, formulated in 10 mM HEPES buffer (pH=8.05). [Table 1] A total of 12 nL of the formulations in Table 1 were deposited onto the carbon working electrode using a piezoelectric dispensing system, with a depth of approximately 0.1 mm 2 A glucose-responsive active region with an area of ​​100 nm was then formed. 200 nL volumes of 2-hydroxyethyl methacrylate (HEMA) and poly(propylene glycol) methacrylate (POMA) were then deposited on the active region and polymerized with various molar ratios of monomers in the presence of 1 wt% 2,2-dimethoxy-2-phenylacetophenone photoinitiator and 1 wt% di(ethylene glycol) dimethacrylate crosslinker. Polymerization and crosslinking were performed under argon for 5 min with UV irradiation wavelength of 365 nm and 6 mW / cm. 2 The experiment was performed at an output of 100 nm. The sensors were then isolated by laser cutting the photopolymerized membrane to form a 0.7 mm wide tail. FIG. 13 shows plots of the sensor response of several glucose sensors covered with mass transport limiting membranes formed from various ratios of HEMA:POMA after the addition of various amounts of 1 M glucose stock solution to achieve a range of glucose concentrations in PBS at 33° C. FIG. 14 shows corresponding plots of sensor response as a function of glucose concentration. Test substance sensors with HEMA:POMA membranes showed an average drift of less than 10% over 14 days, while membranes with only HEMA drifted nearly 100% (data not shown). HEMA:POMA ratios of 2:1 and 4:1 provided a good balance of signal, response linearity, and extended response stability.

[0129] Example 2: Ketone sensor coated with HEMA-POMA film Ketone-responsive active regions were deposited using the formulations shown in Table 2 below, formulated in 10 mM MES buffer (pH=5.5). [Table 2-1] [Table 2-2] A total of 12 nL of the formulations in Table 2 was deposited onto the carbon working electrode using a piezoelectric dispensing system, with a depth of approximately 0.1 mm2 A ketone-responsive active region with an area of ​​100 nm was then formed. 200 nL volumes of 2-hydroxyethyl methacrylate (HEMA) and poly(propylene glycol) methacrylate (POMA) were then deposited onto the active region and polymerized with various molar ratios of monomers in the presence of 1 wt% 2,2-dimethoxy-2-phenylacetophenone photoinitiator and 1 wt% di(ethylene glycol) dimethacrylate crosslinker. Polymerization and crosslinking were performed under argon for 5 min with UV irradiation wavelength of 365 nm and 6 mW / cm. 2 The experiment was carried out at an output of 100 nm. The sensors were then isolated by laser cutting the photopolymerized membrane to form a 0.7 mm wide tail. A PVP-co-styrene layer was then formed on the HEMA-POMA copolymer by dip coating the sensor tail. Figures 15A and 15B show plots of sensor response for several ketone sensors covered with mass transport limiting membranes formed from various ratios of HEMA:POMA after addition of various amounts of 1 M ketone stock solution to achieve a range of ketone concentrations in PBS at 33°C. Figures 16A and 16B show corresponding plots of sensor response as a function of ketone concentration. A HEMA:POMA ratio of 4:6 provided a good balance of signal and response linearity. Comparable sensor performance to a dip coated PVP / PVP-co-styrene mass transport limiting membrane control was achieved, which provides good performance when assaying ketones (U.S. Patent Application Serial No. 16 / 774,835 referenced above). The sensor response changed approximately 2.4% over the two week measurement at this HEMA:POMA ratio (data not shown).

[0130] Example 3: Crosslink density variation within a thiol-ene polymer system. 2,2'-(ethane-1,2-diylbis(oxy))bis(ethane-1-thiol) (EDDEE) and 2-(5-mercapto-3-oxopentyl)-2-(((3-mercaptopropanoyl)oxy)methyl)propane-1,3-diylbis(3-mercaptopropanoate) (PETMP) were combined in various molar ratios and photopolymerized with tri(ethylene glycol) divinyl ether (TEGDVE) as shown in Table 3 below. The molar ratio of the two thiols to TEGDVE was maintained at 1:1 in all cases. Polymerizations were performed by exposing the monomer mixture to 365 nm UV light at 6 mW / cm. 2 The results were analyzed by exposing the sample to air for 5 minutes at a power density of 1000 Hz. Table 3 also summarizes the polymer properties obtained. [Table 3] Entries 1 through 12 in Table 1 are ranked in approximate order of lowest to highest crosslink density. Crosslink density was assessed qualitatively by the appearance of the polymer as well as semiquantitatively by the amount of water absorbed by the polymer. Water content was measured by the ratio of the difference between the dry polymer mass and the wet polymer mass to the wet polymer mass after immersion of a polymer in water for 8 hours. As shown in Table 3, more tetrafunctional thiol PETMP resulted in higher crosslink density values. This example demonstrates that it is possible to tailor the permeability of thiol-ene polymer systems to account for different test material sizes. For water-containing systems, higher water content polymers typically exhibit higher permeability values.

[0131] Example 4: Ketone sensors covered with thiol-ene films. Ketone sensors were fabricated as in Example 2 and covered with thiol-ene copolymers from Table 3, entries 6, 8, 11, and 12. Photopolymerization was performed as in Example 3. The sensors were then isolated by laser cutting the photopolymerized film to form 0.7 mm wide tails. A PVP-co-styrene layer was then formed on the thiol-ene copolymer by dip coating the sensor tails. Figure 17 shows plots of sensor response for several ketone sensors covered with mass transport limiting membranes formed from various ratios of thiol-ene polymers after addition of various amounts of 1 M ketone stock solution to achieve a range of ketone concentrations in PBS at 33°C. Figure 18 shows corresponding plots of sensor response as a function of ketone concentration. In general, the sensor response increased as the crosslink density decreased, except for the film formed from entry 6, which was a sticky film.

[0132] Unless otherwise indicated, all numbers expressing quantities and the like in the specification and the related claims should be understood to be modified in all instances by the term "about." Accordingly, unless indicated to the contrary, the numerical parameters set forth in the specification and appended 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 at least be construed in light of the number of reported significant digits and by applying ordinary rounding techniques.

[0133] One or more exemplary embodiments incorporating various features are presented herein. Not all features of a physical implementation are described or shown in this application for clarity. In developing a physical implementation incorporating an embodiment of the present invention, it is understood that numerous implementation-specific decisions must be made, which will vary from implementation to implementation and from case to case, to achieve the developer's goals, such as compliance with system, business, governmental, and other constraints. Although the developer's efforts may be time consuming, such efforts are nonetheless routine undertakings for those of ordinary skill in the art who would have the benefit of this disclosure.

[0134] While various systems, tools, and methods are described herein in terms of "comprising" various components or steps, the systems, tools, and methods may also be referred to as "consisting essentially of" or "consisting of" various components and steps.

[0135] As used herein, the phrase "at least one of," along with the terms "and" or "or" preceding a series of items and separating some of the items, modifies the entire list rather than each member (i.e., each item) of the list. The phrase "at least one of" allows for the inclusion of 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" respectively refers 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.

[0136] Thus, the disclosed systems, tools and methods are fully adapted to achieve the objects and advantages mentioned as well as those inherent therein. The teachings of the present disclosure may be modified and implemented in different but equivalent manners as will be apparent to those skilled in the art having the benefit of the teachings herein, and the specific embodiments disclosed above are illustrative only. Moreover, no limitations are intended to the details of construction or design shown herein, other than as described in the following claims. It is therefore apparent that the specific exemplary embodiments disclosed above may be altered, combined or modified, and all such variations are considered to be within the scope of the present disclosure. The systems, tools and methods illustratively disclosed herein may be suitably practiced in the absence of any element not specifically disclosed herein and / or any optional element disclosed herein. Although the systems, tools and methods are described in terms of "comprising," "containing," or "including" various components or steps, the systems, tools and methods may also "consist essentially of" or "consist of" the various components and steps. All of the numbers and ranges disclosed above may be varied by some amount. Whenever a numerical range with a lower limit and an upper limit is disclosed, any number falling within that range and any included range is specifically disclosed. In particular, all ranges of values ​​disclosed herein (in the form of "about a to about b", or equivalently "approximately a to b", or equivalently "approximately a to b") should be understood to describe all numbers and ranges falling within the broader range of values. Also, in the claims, terms have their plain and ordinary meaning unless expressly and unambiguously defined by the patent owner. Moreover, the indefinite article "a" or "an" used in the claims is defined herein to mean one or more of the element it introduces. In the event of any discrepancy in the usage of a word or term in this specification and in one or more patent documents or other documents that may be incorporated by reference herein, the definition that is consistent with this specification should be adopted.

Claims

1. A dielectric substrate; one or more openings through the dielectric substrate, each opening being filled with a carbon conductor pillar extending between a first side and a second side of the dielectric substrate; a carbon conductor coating disposed on the first surface of the dielectric substrate in direct contact with each carbon conductor pillar; a dielectric coating disposed on the carbon conductor coating; A carbon working electrode comprising: one or more active regions located on the second surface of the dielectric substrate, in electrical communication with each of the carbon conductor pillars, and responsive to a test substance; a mass transport limiting membrane covering at least the one or more active areas.

2. The analyte sensor of claim 1 , wherein the one or more openings comprise a plurality of vias extending through the dielectric substrate.

3. 3. The analyte sensor of claim 2, wherein each via has an active area disposed directly on the carbon conductor pillar disposed therein.

4. 3. The analyte sensor of claim 2, further comprising a carbon conductor strip disposed on the second surface of the dielectric substrate and covering the plurality of vias, the one or more active areas being disposed directly on the carbon conductor strip.

5. The analyte sensor of claim 1 , wherein the one or more openings comprise slots extending through the dielectric substrate.

6. The analyte sensor of claim 5 , wherein a plurality of active areas are disposed directly on the carbon conductor pillars disposed within the slots.

7. 10. The analyte sensor of claim 1, wherein the one or more active regions comprise one or more analyte responsive enzymes.

8. 2. The analyte sensor according to claim 1, wherein the mass transport limiting membrane is a photopolymerized mass transport limiting membrane.

9. 9. The analyte sensor of claim 8, wherein the photopolymerized mass transport limiting membrane is selectively formed on the one or more active regions.

10. 10. The analyte sensor of claim 9, wherein the mass transport limiting membrane comprises an acrylate polymer or copolymer, a thiol-ene copolymer, or any combination thereof.

11. The analyte sensor of claim 1 , wherein the carbon working electrode is disposed on a sensor tail configured for insertion into tissue.

12. 1. A method for forming an analyte sensor, comprising: providing a dielectric substrate having one or more openings extending therethrough and between a first surface and a second surface; filling the one or more openings with a carbon conductor to form carbon conductor pillars therein and depositing a carbon conductor coating on the first surface of the dielectric substrate, the carbon conductor coating directly contacting each carbon conductor pillar; depositing a dielectric coating over the carbon conductor coating; forming one or more active areas on the second surface of the dielectric substrate in electrical communication with the carbon conductor pillars in the one or more openings and responsive to a test substance; and depositing a mass transport limiting membrane over at least the one or more active regions.

13. The method of claim 12 , wherein the one or more openings comprise a plurality of vias through the dielectric substrate.

14. The method of claim 13 , wherein each via has an active area disposed directly on the carbon conductor pillar disposed therein.

15. 14. The method of claim 13, further comprising depositing a carbon conductor strip on the second surface of the dielectric substrate covering the plurality of vias, the one or more active areas being disposed directly on the carbon conductor strip.

16. The method of claim 12 , wherein the one or more openings comprise slots through the dielectric substrate.

17. The method of claim 16 , wherein a plurality of active areas are disposed directly on the carbon conductor pillars disposed in the slots.

18. The method of claim 12 , wherein the mass transport limiting membrane is deposited by dip coating.

19. The method of claim 12 , wherein the mass transport limiting membrane is polymerized in situ onto the one or more active areas.

20. 20. The method of claim 19, wherein the mass transport limiting membrane is a photopolymerized mass transport limiting membrane formed by depositing one or more monomers on the second surface of the dielectric substrate in contact with the one or more active regions and photopolymerizing the one or more monomers.

21. 21. The method of claim 20, wherein the photopolymerized mass transport limiting membrane comprises an acrylate polymer or copolymer, a thiol-ene copolymer, or any combination thereof.

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