System, method, and device for non-invasive body fluid sampling and analysis

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SYSTEM, METHOD, AND DEVICE FOR NON-INVASIVE BODY FLUID

SAMPLING AND ANALYSIS

CROSS-REFERENCE TO RELATED APPLICATIONS

The present invention relates to PCT International Patent

Publication No. WO 00/35351, entitled “Method and Apparatus for Producing Homogenous Cavitation to Enhance Transdermal Transport”.

BACKGROUND OF THE INVENTION

1. Field ofthe Invention

The present invention relates to non-invasive sampling of body fluids, and, more particularly, to a system, method, and device for non-invasive body fluid sampling and analysis.

2. Description ofthe Related Art

Diabetics frequently prick their fingers and forearms to obtain blood in order to monitor their blood glucose concentration. This practice of using blood to perform frequent monitoring can be painful and inconvenient. New, less painful methods of sampling body fluids have been contemplated and disclosed. For example, these painless methods include the use of tiny needles, the use of iontophoresis, and the use of ultrasound to sample body fluid, such as blood and interstitial fluid.

It has been shown that the application of ultrasound can enhance skin permeability. Examples of such are disclosed in U.S. Patent No. 4,767,402, U.S. Patent No. 5,947,921, and U.S. Patent No. 6,002,961.

Ultrasound may be applied to the stratum comeum via a coupling medium in order to disrupt the lipid bilayers

CA 02374751 2007-08-27 through the action of cavitation and its bioacoustic effects. The disruption of stratum comeum, a barrier to transport, allows the enhanced diffusion of analyte, such as glucose or drugs, through, into, and out of the skin.

Transport of analytes and body fluids can be enhanced further by the action of a motive force. These motive forces include, inter alia, sonophoretic, iontophoretic, electromotive, pressure force, vacuum, electromagnetic motive, thermal force, magnetic force, chemomotive, capillary action, and osmotic. The use of active forces provide a means for obtaining fluid for subsequent analysis.

The application of a motive force before, during, and after making the skin permeable has been disclosed in U.S. Patent No. 5,279,543 , U.S. Patent No. 5,722,397, U.S. Patent No. 5,947,921, U.S. Patent No. 6,002,961, and U.S. Patent No. 6,009,343.

The purpose of using a motive force is to actively extract body fluid and its content out of the skin for the purpose of analysis. As mentioned, active forces, such as vacuum, sonophoresis, and electrosmotic forces, can create convective flow through the stratum comeum. Although these forces can be used for extraction of body fluids, there are certain limitations that may apply when the forces are applied to human skin. For example, a major limitation is the flow and volume of body fluid that can be transported across the stratum comeum. In general, high-pressure force is necessary in order to transport fluid across an enhanced permeable area of stratum comeum. The application of vacuum on skin for an extended period may cause physical separation of the epidermis from the dermis, resulting in bruises and blisters.

Another example of a limitation is the amount of energy that can be applied to the skin in order to create convective flow. Extraction of usable volume of body fluid has the potential to cause pain and skin damage with prolonged exposure to ultrasound. In a similar manner, electro-osmotic extraction of body fluid through stratum comeum has the potential to cause skin damage due the need to use high current density. It is evident that there are limitations to the use of the mentioned extraction methods when applied to human skin.

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SUMMARY OF THE INVENTION

Therefore, a need has arisen for a system, method, and device for non-invasive body fluid sampling and analysis that overcomes these and other drawbacks of the related art.

Therefore, a need has arisen for a method of enhancing the permeability of a biological membrane, such as skin, buccal, and nails, for an extended period of time, and a method for extracting body fluid to perform blood, interstitial fluid, lymph, or other body fluid analyte monitoring in a discrete or continuous manner that is non-invasive and practical.

A method for non-invasive body fluid sampling and analysis is disclosed. According to one embodiment of the present invention, the method includes the steps of (1) identifying an area of biological membrane having a permeability level; (2) increasing the permeability level of the area of biological membrane; (3) contacting the area of biological membrane with a receiver; (4) extracting body fluid through and out of the area of biological membrane; (5) providing an external force to enhance the body fluid extraction; (6) collecting the body fluid in the receiver; (7) analyzing the collected body fluid for the presence of at least one analyte; and (8) providing the results of the step of analyzing the body fluid.

The area of biological membrane may be made permeable using ultrasound with controlled dosimetry. Extraction of body fluid may be performed on the area exposed to ultrasound using osmotic transport. The body fluid may be collected using a receiver. The receiver may be attached to the biological membrane in a form of a patch, a wearable reservoir, a membrane, an absorbent strip, a hydrogel, or an equivalent. The receiver may be analyzed for the presence of various analytes indicative of blood analytes. The analysis may comprise the use of electrochemical, biochemical, optical, fluorescence, absorbance, reflectance, Raman, magnetic, mass spectrometry, infra-red (IR) spectroscopy measurement methods and combinations thereof. The receiver may also be attached to a secondary receiver where the concentration of analyte in the secondary receiver is

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PCT/US01/08489 continuously maintained substantially lower than that in the body fluid so the chemical concentration driving force between body fluid and secondary receiver is maximized. This may be achieved by chemical reaction or volume for dilution or similar means. In one embodiment, the receiver and the secondary receiver may operate on different principles (e.g., osmosis, dilution, etc.). In another embodiment, the receivers may operate on the same principle.

A system for non-invasive body fluid sampling and analysis is disclosed. According to one embodiment of the present invention, the system includes a controller that controls the generation of ultrasound; an ultrasonic applicator that applies the ultrasound to an area of biological membrane; a receiver that contacts the area of biological membrane and receives body fluid through and out of the area of biological membrane; and a meter that interacts with the receiver and detects the presence of at least one analyte in the body fluid in the receiver. The receiver may include a membrane and a medium, such as a hydrogel, a fluid, or a liquid, that is contained within the membrane.

A method for noninvasive body fluid sampling and analysis is disclosed. According to one embodiment of the present invention, the method includes the steps of (1) enhancing a permeability level of an area of biological membrane; (2) attaching a receiver to the area of biological membrane; (3) extracting an analyte through and out of the area of biological membrane; (4) collecting the body fluid in the receiver; and (5) determining a concentration of at least one analyte in the body fluid.

A device for noninvasive body fluid sampling and analysis is disclosed. According to one embodiment of the present invention, the device includes a receiver that is attached to an area of biological membrane with an enhanced permeability and receives body fluid through and out of the area of biological membrane, and a wearable meter that detects the presence of at least one analyte in the received body fluid and indicates a concentration of that analyte. The receiver may include a membrane and a medium, such as a hydrogel, a fluid, or a liquid, that is contained in the membrane. The meter may include a processor and a

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PCT/US01/08489 device that detects the presence of the analyte. The detecting device may include an electrochemical detector; a biochemical detector; a fluorescence detector; an absorbance detector; a reflectance detector; a Raman detector; a magnetic detector; a mass spectrometry detector; an IR spectroscopy detector; and combinations thereof.

According to one embodiment of the present invention, osmotic forces may be used to sample body fluid from and through a biological membrane in an on-demand manner. The osmotic agent in solution, gel, hydrogel, or other form may be applied to the ultrasound-treated biological membrane using a receiver, such as a thin liquid reservoir, whenever the concentration of an analyte needs to be determined for diagnosis and monitoring. The receiver may be attached to the biological membrane using an adhesive. The receiver may be attached to the biological membrane for a brief duration. The solution in the receiver may be subsequently removed and analyzed for the presence of analytes. In one embodiment, the receiver may be constructed in the form of a patch. The receiver may contain a hydrogel and osmotic agent. The receiver may combine the osmotic agent and the chemical reagents to detect the presence of the analyte. The reagents may allow the use of electrochemical, biochemical, optical, fluorescence, absorbance, reflectance, Raman, magnetic, mass spectrometry, infrared (IR) spectroscopy measurement methods and combinations thereof to be performed on the receiver.

In another embodiment, osmotic forces may be used to sample body fluid from or through a biological membrane in a periodic or a continuous manner. The osmotic agent in solution form may be applied to the ultrasound-treated biological membrane using a thin receiver, such as a thin liquid reservoir, whenever the concentration of analyte needs to be determined for diagnosis and monitoring. The receiver may be attached to biological membrane using an adhesive. In one embodiment, the receiver may be constructed in the form of a patch. The receiver may contain a hydrogel that contains the osmotic agent. The receiver may contain means for manipulating the intensity and duration of the osmotic force. The

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PCT/US01/08489 intensity of the osmotic force may be manipulated using electric field forces, magnetic field forces, electromagnetic field forces, biochemical reactions, chemicals, molarity adjustment, adjusting solvents, adjusting pH, ultrasonic field forces, electro-omostic field forces, iontophoretic field forces, electroporatic field forces and combinations thereof. The duration of the osmotic force may be manipulated using electric field forces, magnetic field forces, electromagnetic field forces, biochemical reactions, chemicals, molarity adjustment, adjusting solvents, adjusting pH, ultrasonic field forces, electroomostic field forces, iontophoretic field forces, electroporatic field forces and combinations thereof. The receiver may combine the osmotic agent and the biochemical reagents to detect the presence of the analyte. The reagents may allow the use of electrochemical, biochemical, optical, fluorescence, absorbance, reflectance, Raman, magnetic, mass spectrometry, IR spectroscopy measurement methods and combinations thereof to be performed on the receiver. The receiver may also be removed periodically for detection.

In one embodiment, the intensity, duration, and frequency of exposure of biological membrane to osmotic forces may be manipulated by using an electric current to cause a change in the concentration of the osmotic agent that is in contact with the ultrasound-exposed biological membrane. The osmotic agent may be a multi-charged agent that can dissociate into several charged species. These charged species may be transported using electric field forces. A membrane may be used to isolate the charged species. The charged species freely diffuse and combine upon removal of the electric field force.

In one embodiment, the intensity, duration, and frequency of exposure of biological membrane to osmotic forces may be manipulated by using active forces to cause a change in the concentration of the osmotic agent that is in contact with the ultrasound-exposed biological membrane. The osmotic agent may be a neutral charge agent. The agent may be transported using a variety of field forces. The field force depends on the constitutive and colligative properties of the chosen agent. The field force generates a force necessary to move the osmotic

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PCT/US01/08489 agent toward and away from the biological membrane surface. The movement of the osmotic agent modulates the periodic and continuous extraction of body fluid through the stratum comeum.

In one embodiment, the intensity, duration, and frequency of exposure of biological membrane to osmotic forces may be manipulated by changing the concentration of the osmotic agent that is in contact with the ultrasound-exposed biological membrane. Manipulating the volume of the solvent and the volume of the hydrogel containing the osmotic agent may cause a change in the concentration of the osmotic agent. The volume of the hydrogel can be changed by constructing a hydrogel wherein its volume is sensitive to the concentrations of molecules that can diffuse into the gel. One example is a hydrogel constructed to be sensitive to the molecule glucose. The hydrogel volume can also be changed by manipulating its temperature and by changing the pH of the gel.

A receiver that is attached to an area of biological membrane with an enhanced permeability and receives body fluid through and out of the area of biological membrane is disclosed. According to one embodiment of the present invention, the receiver includes a first grid; a medium layer comprising at least one agent; a membrane that induces a concentration gradient barrier for the at least one agent; a counter grid; an oxidase layer; a detection layer; and a voltage source that provides a potential difference between the first grid and the counter grid. The body fluid, which may include blood, interstitial fluid, analyte, and lymph, may flow out of, or through, the biological membrane, to the detector layer via the first grid, the counter grid, and the oxidase layer.

It is a technical advantage of the present invention that a system, method, and device for non-invasive sampling and analysis of body fluids is disclosed. It is another technical advantage of the present invention that a concentration of an analyte may be measured continuously or periodically.

BRIEF DESCRIPTION OF THE DRAWINGS

For a more complete understanding of the present invention, the objects and advantages thereof, reference is now made to the following descriptions

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PCT/US01/08489 taken in connection with the accompanying drawings in which:

Fig. 1 is a flowchart depicting a method for non-invasive body fluid sampling according to one embodiment of the present invention;

Fig. 2 depicts a device for controlled application of ultrasound to a biological membrane to enhance the permeability of the biological membrane according to one embodiment of the present invention;

Fig. 3 depicts the components to perform discrete extraction and measurement of body fluid to infer analyte concentrations according to one embodiment of the present invention;

Fig. 4 depicts the components to perform continuous extraction and measurement of body fluid to infer analyte concentrations according to one embodiment of the present invention;

Fig. 5 depicts an approach to periodic monitoring of an analyte by performing periodic osmotic extractions of body fluid according to one embodiment of the present invention;

Fig. 6 depicts the components of a wearable extraction chamber according to one embodiment of the present invention; and

Fig. 7 depicts a graph of glucose flux versus blood glucose concentration according to one embodiment of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

The preferred embodiment of the present invention and its advantages are best understood by referring to Figs. 1 through 7 of the drawings, like numerals being used for like and corresponding parts of the various drawings.

As used herein, the term “body fluid” may include blood, interstitial fluid, lymph, and/or analyte. In addition, as used herein, the term “biological membrane” may include tissue, mucous membranes and comified tissues, including skin, buccal, and nails. Further, as used herein, the term “force” may also include force gradients.

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Although the present invention may be described in conjunction with human applications, veterinary applications are within the contemplation and the scope of the present invention.

Referring to Fig. 1, a flowchart depicting a method for non-invasive body fluid sampling and analysis according to one embodiment of the present invention is provided. In step 102, the permeability of an area of biological membrane is enhanced. In one embodiment, the area of biological membrane may be located on the volar forearm of a mammalian subject. In another embodiment, the area of biological membrane may be located on a thigh of a mammalian subject. In yet another embodiment, the area of biological membrane may be located on the abdomen. In still another embodiment, the area of biological membrane may be located on the back. Other body locations may also be used.

In general, several techniques may be used to enhance the permeability of the biological membrane, such as creating physical micropores, physically disrupting the lipid bilayers, chemically modifying the lipid bilayers, physically disrupting the stratum comeum, and chemically modifying the stratum comeum. The creation of micropores, or the disruption thereof, may be achieved by physical penetration using a needle, a microneedle, a silicon microneedle, a laser, a laser in combination with an absorbing dye, a heat source, an ultrasonic needle, an ultrasonic transducer, cryogenic ablation, RF ablation, photo-acoustic ablation, and combinations thereof.

In a preferred embodiment, ultrasound may be applied to the area of biological membrane to enhance its permeability. Ultrasound is generally defined as sound at a frequency of greater than about 20 kHz. Therapeutic ultrasound is typically between 20 kHz and 5 MHz. Near ultrasound is typically about 10 kHz to about 20 kHz. It should be understood that in addition to ultrasound, near ultrasound may be used in embodiments of the present invention.

In general, ultrasound, or near ultrasound, is preferably applied to the area of biological membrane at a frequency sufficient to cause cavitation and increase the permeability of the biological membrane. In one embodiment,

CA 02374751 2007-08-27 ultrasound may be applied at a frequency of from about 10 kHz to about 500 kHz. In another embodiment, ultrasound may be applied at a frequency of from about 20 kHz to about 150 kHz. In yet another embodiment, the ultrasound may be applied at 50 kHz. Other frequencies of ultrasound may be applied to enhance the permeability level of the biological membrane.

In one embodiment, the ultrasound may have an intensity in the range of about 0 to about 100 watt/cm², and preferably in the range of 0 to about 20 watt/cm². Other appropriate intensities may be used as desired.

Techniques for increasing the permeability of a biological membrane are disclosed in U.S. Patent No. 6,190,315 to Kost et al.

In step 104, body fluid is extracted through or out of the area of biological membrane. In one embodiment, an external force, such as an osmotic force, may assist in the extraction. In one embodiment, the osmotic force may be controlled before, during, and after the permeability of the biological membrane is enhanced.

In one embodiment, the osmotic force may be generated by the application of an osmotic agent to the area of biological membrane. The osmotic agent may be in the form of an element, a molecule, a macromolecule, a chemical compound, or combinations thereof. The osmotic agent may also be combined with a liquid solution, a hydrogel, a gel, or an agent having a similar function.

In step 106, the magnitude, intensity, and duration of the external force may be regulated by at least one additional first energy and/or force. In one embodiment, the first additional energy and/or force may be applied to control and regulate the movement and function of the osmotic agent for extraction of body fluid through and out of the biological membrane. The first additional energy and/or force may be provided in the form of heat, a temperature force, a pressure force, an electromotive force, a mechanical agitation, ultrasound, iontophoresis, an electromagnetic force, a magnetic force, a photothermal force, a photoacoustic force, and combinations thereof. The effect of an electric field and ultrasound on

CA 02374751 2007-08-27 transdermal drug delivery is disclosed in U.S. Patent No. 6,041,253.

In one embodiment, if the first additional energy and/or force is provided by ultrasound, the frequency of the ultrasound may be provided at a different frequency than the frequency used to enhance the permeability of the biological membrane. In one embodiment, the frequency of the first additional energy/force ultrasound may be higher than the frequency of the permeability enhancing ultrasound.

In step 108, the body fluid may be collected in a receiver. In one embodiment, the receiver may be contacted with the biological membrane in a form of a patch, a wearable reservoir, a membrane, an absorbent strip, a hydrogel, or a structure that performs an equivalent function. Other types and configurations of receivers may be used.

In one embodiment, the receiver may be provided with a secondary receiver having an analyte concentration that is continuously maintained to be substantially lower than the analyte concentration in the body fluid, so the chemical concentration driving force between body fluid and secondary receiver is maximized. This may be achieved by chemical reaction or volume for dilution or similar means.

In one embodiment, a second external energy/force may be applied between the first receiver and the secondary receiver. In one embodiment, the second external energy/force may be different (e.g., a different type of external force) from the first external energy/force. In another embodiment, the second external energy/force may be the same (e.g., the same type of external force) as the first external energy/force. The first and second external energy/force may vary in type, duration, and intensity, and may be controlled through different additional energy and/or forces.

In step 110, the collected body fluid may be analyzed. In one embodiment, the analysis may include the use of appropriate methods, such as electrochemical, biochemical, optical, fluorescence, absorbance, reflectance,

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Raman, magnetic, mass spectrometry, infra-red (IR) spectroscopy measurement, and combinations thereof.

In one embodiment, multiple analytes may be analyzed simultaneously, in parallel, or in series. The results from these multiple analyses may be used in combination with algorithms, for example, to increase the accuracy, or precision, or both, of the analysis and measurements.

In one embodiment, the receiver may be removed from contact with the biological membrane in order to analyze the collected body fluid. In another embodiment, the receiver may remain in contact with the biological membrane as the collected body fluid is analyzed.

Referring to Fig. 2, a device for the controlled application of ultrasound to biological membrane to enhance the permeability of a biological membrane according to one embodiment of the present invention is shown. Device 200 includes controller 202, which interfaces with ultrasound applicator 204 by any suitable means, such as a cable. Controller 202 controls the application of ultrasound to the area of biological membrane. In one embodiment, ultrasound or near ultrasound having an intensity in the range of about 0 to about 20 watt/cm²may be generated by controller 202 and ultrasound applicator 204. In one embodiment, the ultrasound may have a frequency of about 20 kHz to about 150 kHz. In another embodiment, the ultrasound may have a frequency of 50 kHz. Other ultrasound frequencies may also be used.

In addition, controller 202 may include a display, such as a LCD or a LED display, in order to convey information to the user as required. Controller 202 may also include a user interface as is known in the art.

Ultrasound applicator 204 may be provided with cartridge 206, which contains ultrasound coupling solution 208. Cartridge 206 may be made of any material, such as plastic, that may encapsulate ultrasound coupling solution 208. Suitable ultrasound coupling solutions 208 include, but is not limited to, water, saline, alcohols including ethanol and isopropanol (in a concentration range of 10 to 100% in aqueous solution), surfactants such as Triton’X-100, SLS, or SDS

CA 02374751 2007-08-27 (preferably in a concentration range of between 0.001 and 10% in aqueous solution), DMSO (preferably in a concentration range of between 10 and 100% in aqueous solution), fatty acids such as linoleic acid (preferably in a concentration range of between 0.1 and 2% in ethanol-water (50:50) mixture), azone (preferably in a concentration range of between 0.1 and 10% in ethanol-water (50:50) mixture), polyethylene glycol in a concentration range of preferably between 0.1 and 50% in aqueous solution, histamine in a concentration range of preferably between 0.1 and 100 mg/ml in aqueous solution, EDTA in a concentration range of preferably between one and 100 mM, sodium hydroxide in a concentration range of preferably between one and 100 mM, sodium octyl sulfate, N-lauroylsarcosine, octyltrimethyl ammoniumbromide, dodecyltrimethyl ammoniumbromide, tetradecyltrimethyl ammoniumbromide, hexadecyltrimethyl ammoniumbromide, dodecylpyridinium

TM TM chlonde hydrate, SPAN 20, BRU 30, glycolic acid ethoxylate 4-ter-butyl phenyl ether, IGEPAIjCO^IO, and combinations thereof.

In one embodiment, the coupling medium may also include a chemical enhancer. Transport enhancement may be obtained by adding capillary permeability enhancers, for example, histamine, to the coupling medium. The concentration of histamine in the coupling medium may be in the range of between 0.1 and 100 mg/ml. These agents may be delivered across the biological membrane during application of ultrasound and may cause local edema that increases local fluid pressure and may enhance transport of analytes across the biological membrane. In addition, the occurrence of free fluid due to edema may induce cavitation locally so as to enhance transport of analytes across the biological membrane.

In one embodiment, cartridge 206 may be pierced when inserted into ultrasound applicator 204, and ultrasound coupling solution 208 may be transferred to a chamber (not shown).

A target identifying device, such as target ring 210, may be attached to the area of biological membrane that will have its permeability increased. Target ring 210 may be attached to the area of biological membrane by a transdermal

CA 02374751 2007-08-27 adhesive (not shown). In one embodiment, target ring 210 may have the transdermal adhesive pre-applied, and may be disposed after each use. In another embodiment, target ring 210 may be reusable.

Target ring 210 may be made of any suitable material, including plastic, ceramic, rubber, foam, etc. In general, target ring 210 identifies the area of biological membrane for permeability enhancement and body fluid extraction. In one embodiment, target ring 210 may be used to hold receiver 214 in contact with the biological membrane after the permeability of the biological membrane has been increased.

In one embodiment, target ring 210 may be used to monitor the permeability level of the biological membrane, as disclosed in PCT International Patent Publication No. WO 00/35351, entitled “Method and Apparatus for Producing Homogenous Cavitation to Enhance Transdermal Transport”. In such an embodiment, target ring 210 may interface with ultrasound applicator 204.

Ultrasound applicator 204 may be applied to target ring 210 and activated to expose ultrasound coupling solution 208 to the biological membrane. Controller 202 controls ultrasound applicator 204 to transmit ultrasound through ultrasound coupling solution 208. During ultrasound exposure, controller 202 may monitor changes in biological membrane permeability, and may display this information to the user.

Controller 202 may cease, or discontinue, the application of ultrasound once a predetermined level of biological membrane permeability is reached. This level of permeability may be preprogrammed, or it may be determined in real-time as the ultrasound is applied. The predetermined level of permeability may be programmed for each individual due to biological membrane differences among individuals.

After the predetermined level of permeability is reached, ultrasound coupling solution 208 may be vacuated from chamber (not shown) into cartridge 206, which may then be discarded. In another embodiment, ultrasound coupling

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Referring to Fig. 3, an device for the analysis of body fluid 5 according to one embodiment of the present invention is provided. Receiver 214 may be placed into target ring 210 to perform a discrete, or on-demand, extraction of body fluid through and/or out of the biological membrane. Receiver 214 may contain a medium, such as a hydrogel layer, that incorporates an osmotic agent. In one embodiment, the hydrogel may be formulated to contain phosphate buffered saline (PBS), with the saline being sodium chloride having a concentration range of about 0.01 M to about 10 M. The hydrogel may be buffered at pH 7. Other osmotic agents may also be used in place of, or in addition to, sodium chloride. Preferably, these osmotic agents are non-irritating, non-staining, and nonimmunogenic. Examples of such osmotic agents include, inter alia, lactate and magnesium sulfate.

In another embodiment, receiver 214 may include a fluid or liquid medium, such as water or a buffer, that is contained within a semi-permeable membrane. Receiver 214 may also include a spongy material, such as foam.

Receiver 214 may be applied to the biological membrane to contact 20 the ultrasound exposed biological membrane. In one embodiment, receiver 214 may be applied to the biological membrane for a time period sufficient to collect an amount of body fluid sufficient for detection. In another embodiment, receiver 214 may be applied to the biological membrane for a sufficient time period to collect a predetermined amount of body fluid. In yet another embodiment, receiver 214 may be applied to the biological membrane for a predetermined time. In one embodiment, the contact between receiver 214 and the biological membrane may last for 15 minutes or less. In another embodiment, the contact between receiver 214 and the biological membrane may last for 5 minutes or less. In still another embodiment, the contact between receiver 214 and the biological membrane may

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PCT/US01/08489 last for 2 minutes or less. The actual duration of contact may depend on the sensitivity of the detection method used for analysis.

In one embodiment, the medium of receiver 214 may contain at least one reagent (not shown) in order to detect the presence of certain analytes in the body fluid that has been extracted from or through the biological membrane. In one embodiment, the hydrogel layer of receiver 214 may contain the reagents, and the reagents may be attached to the hydrogel by ionic and/or covalent means, or may be immobilized by gel entrapment. The reagents may also be arranged as an adjacent layer to the hydrogel wherein the analyte from the body fluid that has been extracted into the hydrogel can diffuse into and react to generate by-products. The by-products may then be detected using electrochemical, biochemical, optical, fluorescence, absorbance, reflectance, Raman, magnetic, mass spectrometry, IR spectroscopy measurement methods and combinations thereof.

The. detection methods may be performed by meter 212. Meter 212 may include a processor (not shown) and a display, such as an LCD display. Other suitable displays may be provided.

In one embodiment, meter 212 may provide an interface that allows information be downloaded to an external device, such as a computer. Such an interface may allow the connection of interface cables, or it may be a wireless interface.

Meter 212 may be configured to determine body fluid glucose concentration by incorporating glucose oxidase in the medium of receiver 214. In one embodiment, glucose from extracted body fluid may react with glucose oxidase to generate hydrogen peroxide. Hydrogen peroxide may be detected by the oxidation of hydrogen peroxide at the surface of electrodes incorporated into receiver 214. The oxidation of hydrogen peroxide transfers electrons onto the electrode surface which generates a current flow that can be quantified using a potentiostat, which may be incorporated into meter 212. A glucose concentration proportional to the concentration of hydrogen peroxide may be calculated, and the result may be reported to the user via a display. Various configurations of

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PCT/US01/08489 electrodes and reagents, known to those of ordinary skill in the art, may be incorporated to perform detection and analysis of glucose and other analytes.

Meter 212 may also be configured to simultaneously measure the concentration of an analyte, such as glucose, where the body fluid concentration is expected to fluctuate, and an analyte, like creatinine or calcium, where the body fluid concentration is expected to remain relatively stable over minutes, hours, or days. An analyte concentration, which may be determined by an algorithm that takes into account the relative concentrations of the fluctuating and the more stable analyte, may be reported to the user via a display.

In another embodiment, meter 212 may analyze multiple analytes simultaneously, in parallel, or in series. The results from these multiple analyses may be used in combination with algorithms, for example, to increase the accuracy, or precision, or both, of the analysis and measurements.

Receiver 214 may be discarded after the extraction and measurement steps. In another embodiment, receiver 214 may be reused. In one embodiment, receiver 214 may be cleaned, sanitized, etc. before it may be reused. Various configurations of electrodes and reagents, known to those of ordinary skill in the art, may be incorporated to perform detection and analysis of glucose and other analytes.

Referring to Fig. 4, an device for the continuous extraction and analysis of body fluid to infer analyte concentrations according to another embodiment of the present invention is provided. As shown in the figure, a biological membrane site on the forearm, the abdomen, or thigh may be exposed to ultrasound; other biological membrane sites, such as those on the back, may also be used. Receiver 402, which may be similar to receiver 214, may contact the ultrasound exposed biological membrane site to perform continuous extraction of body fluid. In one embodiment, receiver 402 may contain a medium, such as a hydrogel layer, that may incorporate an osmotic agent, such as sodium chloride. The hydrogel is formulated to contain phosphate buffered saline (PBS), with the

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PCT/US01/08489 saline being sodium chloride in the concentration range of .01 M to 10 M. The hydrogel may be buffered at pH 7.

Other osmotic agents may also be used in place of, or in addition to, sodium chloride. These osmotic agents are preferably non-irritating, non-staining, and non-immunogenic. Examples of these other osmotic agents may include, inter alia, lactate and magnesium sulfate. Receiver 402 may be applied to contact the ultrasound exposed biological membrane. In one embodiment, the duration of this contact may be 12-24 hours, or more. In another embodiment, other durations of contact, including substantially shorter durations, and substantially longer durations, may be used as desired.

In another embodiment, receiver 402 may include a fluid or liquid medium, such as water or a buffer, that is contained within a semi-permeable membrane. Receiver 402 may also include a spongy material, such as foam.

In one embodiment, the medium of receiver 402 may contain at least 15 one reagent (not shown) that detects the presence of analytes in the body fluid that has been extracted thorough and out of the biological membrane. In one embodiment, the hydrogel layer of receiver 402 may contain reagents that may be attached by ionic and covalent means to the hydrogel, or may be immobilized by gel entrapment. The reagents may also be arranged as an adjacent layer to the hydrogel wherein the analyte from the body fluid that has been extracted into the hydrogel may diffuse into and react to generate by-products. The by-products may be detected using electrochemical, biochemical, optical, fluorescence, absorbance, reflectance, Raman, magnetic, mass spectrometry, IR spectroscopy measurement methods and combinations thereof.

The detection methods and results may be performed and presented to the user by meter 404, which may be similar in function to meter 212, discussed above. In one embodiment, meter 404 may be wearable. For example, as depicted in the figure, meter 404 may be worn a manner similar to the way a wristwatch is worn. Meter 404 may also be worn on a belt, in a pocket, etc.

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Meter 404 may incorporate power and electronics to control the periodic extraction of body fluid, to detect analyte, and to present the analyte concentration in a continuous manner. Meter 404 may contain electronics and software for the acquisition of sensor signals, and may perform signal processing, and may store analysis and trending information.

In one embodiment, meter 404 may provide an interface that allows information be downloaded to an external device, such as a computer. Such an interface may allow the connection of interface cables, or it may be a wireless interface.

Meter 404 may be configured to determine body fluid glucose concentration by incorporating glucose oxidase in the medium. In one embodiment, glucose from extracted body fluid may react with glucose oxidase to generate hydrogen peroxide. Hydrogen peroxide may be detected by the oxidation of hydrogen peroxide at the surface of electrodes incorporated into receiver 402. The oxidation of hydrogen peroxide transfers electrons onto the electrode surface which generates a current flow that can be quantified using a potentiostat, which may be incorporated into meter 404. A glucose concentration proportional to the concentration of hydrogen peroxide may be calculated and the result may be reported to the user via a display. Various configurations of electrodes and reagents, known to those of ordinary skill in the art, may be incorporated to perform detection and analysis of glucose and other analytes.

In one embodiment, meter 404 may also be configured to simultaneously measure concentration of an analyte, such as glucose, where the body fluid concentration is expected to fluctuate, and an analyte, like creatinine or calcium, where the body fluid concentration is expected to remain relatively stable over minutes, hours, or days. An analyte concentration, which may be determined by an algorithm that takes into account the relative concentrations of the fluctuating and the more stable analyte, may be reported to the user via a display.

In another embodiment, meter 404 may analyze multiple analytes simultaneously, in parallel, or in series. The results from these multiple analyses

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PCT/US01/08489 may be used in combination with algorithms, for example, to increase the accuracy, or precision, or both, of the analysis and measurements.

In another embodiment, receiver 402 may be removed from contact with the biological membrane for analysis by meter 404. Receiver 402 may be put in contact with the biological membrane after such analysis.

Meter 404 may provide analyte readings to the user in a periodic or a continuous manner. For example, in one embodiment, in continuous monitoring of the analyte glucose, glucose concentration may be displayed to the user every 30 minutes, more preferably every 15 minutes, most preferable every 5 minutes, or even more frequently. In another embodiment, the glucose concentration may be displayed continuously. The period may depend on the sensitivity and method of analyte detection. In continuous glucose monitoring, in one embodiment, glucose detection may be performed by an electrochemical method using electrodes and reagents incorporated into receiver 402 and detection and analysis performed by meter 404. During the measurement period, osmotic extraction of body fluid may be performed continuously by the hydrogel layer of receiver 402. Body fluid may accumulate in the hydrogel of receiver 402. Glucose in body fluid diffuses to react with glucose oxidase and is converted into hydrogen peroxide. The hydrogen peroxide is consumed by poising the working electrode with respect to a reference electrode. During the resting period, hydrogen peroxide accumulates and is consumed or destroyed before the measuring period. The magnitude of the working potential can be applied to rapidly consume the build up of hydrogen peroxide.

Referring to Fig. 5, an approach to periodic monitoring of an analyte by performing periodic osmotic extractions of body fluid according to another embodiment of the present invention is shown. The osmotic extraction intensity and frequency may be manipulated by using an osmotic agent that dissociates into multiple charged species, and an electrical potential may be used to move the concentration of charges toward and away from biological membrane surface 550. Receiver 500 may include grid, mesh, or screen 504; medium 506, which may be a hydrogel layer; membrane 508; counter grid, mesh, or screen 510; oxidase layer

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512; and detection layer 514. Grid 504 and counter grid 510 may be connected to voltage source 516. Membrane 508 may be a semi-permeable membrane that is used to induce a concentration gradient barrier for the osmotic agent contained in medium 506. The preferable osmotic agent may contain negative and positive species or counter ions. Manipulating the concentration of charged species at the boundary adjacent to the stratum comeum of the ultrasound-exposed biological membrane may provide periodic extraction of body fluid.

In one embodiment, receiver 500 may make contact with the skin though contact medium 502, which may be a hydrogel, or other suitable medium.

The concentration of the charged species may be manipulated by applying a potential difference between grid 504 and counter grid 510 using voltage source 516. In one embodiment, the potential difference may be of a magnitude that is sufficient to manipulate the osmotic agent. The polarity of the grid may also be changed to transport charges toward and away from biological membrane surface 550. Grid 504 and counter grid 510 may be configured with optimum porosity as to allow body fluid and/or analyte to travel out of stratum comeum, through grid 504, through grid 510, and into oxidase layer 512, and ultimately to detection layer 514. Oxidase layer 512 may be used with an appropriate catalyst, or enzyme, to confer specificity of analyte detection. Detection layer 514 may include working and reference electrodes (not shown) that allow for the detection of the byproducts of oxidase layer 512 to quantify the concentration of the desired analyte of detection.

EXAMPLE

In order to better understand the present invention, an example is provided. The example does not limit the present invention in any way, and is intended to illustrate an embodiment of the present invention.

The following is a description of experiments which implemented painless extraction, collection, and analysis of body fluid to determine body fluid glucose concentration in a human using a hyperosmotic extraction fluid and comparing this condition with iso-osmotic extraction fluid, in accordance with one

CA 02374751 2007-08-27 embodiment of the present invention. Although body fluid glucose concentration serves as an example to demonstrate feasibility, other analytes are within the contemplation of the present invention. In addition, multiple analytes may be measured and/or analyzed simultaneously, in parallel, or in series, and results from these multiple measurements may be used in combination with algorithms, for example, to increase the accuracy or precision or both of measurements. As may be recognized by one of ordinary skill in the art, these steps may be automated and implemented with the device described above.

Four sites on the volar forearm of a human volunteer were treated with ultrasound using the device described in Fig. 2. The ultrasound transducer and its housing were placed on the volar forearm of the volunteer with enough pressure to produce a good contact between the skin and the outer transducer housing, and to prevent leaking. The area surrounding the transducer was then filled with a coupling medium of sodium dodecyl sulfate and silica particles in phosphate15 buffered saline (PBS). Ultrasound was briefly applied (5 - 30 s), the transducer apparatus was removed from the biological membrane, and the skin was rinsed with tap water and dried.

Fig. 6 describes the components of wearable extraction chamber 600. Four extraction chambers were placed on each sonicated site of the human volunteer. Thin circular foam chamber 602 was constructed using foam MED 5636 Avery Dennison (7/16 ID x 1 1/8 OD). Foam chambers 602 were attached concentrically to the sonicated biological membrane sites using double-sided adhesive (Adhesive Arcade 8570, 7/16 ID x 7/8 OD) attached to one side of element 602. The other side of foam chamber 602 was attached concentrically to double-sided adhesive 604 (Adhesive Arcade 8570, 7/16 ID x 7/8 OD). Thin

TM transparent lid 606 was made of 3M Polyester 1012 (1 1/8 x 1 1/8). Double-sided adhesive 604 permitted thin transparent lid 606 to be attached to foam chamber 602 after placement of liquid into the inner diameter of foam chamber 602 when attached to biological membrane. Thin transparent lid 606 acted as a lid to prevent

CA 02374751 2007-08-27 liquid from leaking out of the extraction chamber, and to allow the extraction chambers to be wearable for an extended period of time.

Each extraction chamber was alternately filled with 100 μΐ of extraction solution for 15 min and 100 μΐ hydration solution for 10 - 40 min.

Extraction solution was PBS; on two sites the PBS contained additional NaCl to bring the total concentration of NaCl to 1 M. Hydration solution was PBS for all sites.

Solutions were collected and analyzed for glucose concentration using high-pressure liquid chromatography. The results of the HPLC concentration were normalized for the injection amount and the total solution volume, and were reported as glucose flux (Q_g), the mass of glucose that crossed the sonicated site per unit time per unit area. Body fluid glucose concentrations (Cbg) were obtained by testing capillary blood obtained from a lanced finger in a Bayer Glucometer Elite meter. It was hypothesized that Q_g would be linearly proportional to C*_g. Fig. 7 shows a graph of Q_g versus Cbg. Unexpectedly, Q_g from the sonicated sites exposed to 1 M NaCl correlated to Cbg much more strongly than Q_g from the sonicated sites exposed to 0.15 M NaCl.

Other embodiments and uses of the invention will be apparent to those skilled in the art from consideration of the specification and practice of the invention disclosed herein. It is intended that the specification and examples be considered exemplary only, with the true scope and spirit of the invention indicated by the following claims.