Non-invasive glucose measurement device with intensity control mechanism

Abstract

The present invention discloses a non-invasive glucose measurement device for monitoring blood glucose levels. This device (100) comprises a finger placement hole (102) for convenient placement of the user's finger and a glucose sensor module (104) that generates beams of infrared and visible laser light. A photodiode (120) receives the refracted light, enabling the determination of voltage output and blood glucose concentration. The device is controlled by a controller (106) that analyzes the light signals, generates intensity adjustment signals, and activates the screen (108) for displaying the measured blood glucose level. The method (300) for measuring blood glucose levels involves positioning the user's finger, generating and receiving beams of light, determining voltage output, adjusting the intensity of the visible laser light, calculating the blood glucose concentration, and displaying the result on the screen. The method ensures automatic intensity adjustment of the visible laser light within a specific range.

Description

BACKGROUND

[001] Field of the invention

[002] Embodiments of the present invention generally relate to an optoelectronicblood glucose measuring device and particularly to a non-invasive glucose measurementdevice equipped with an intensity controlmechanism to eliminate errors caused by human skin variations duringglucose measurements.

[003] Description of Related Art

[004] Diabetes is a global health concern affecting over 12% of the worldpopulation. It poses serious risks to vital organs and increases thelikelihood of heart disease, stroke, neuropathy, kidney failure, blindness,and congenital disabilities. While there is no cure for diabetes, patientsmay effectively manage their condition by monitoring their blood glucoselevels. Typically, a normal glucose concentration ranges between 70 and140 mg / dL for non-diabetics. Levels above 140 mg / dL after an 8-hourfasting period or above 180 mg / dL after 2 hours without eating indicateelevated glucose concentrations. Clinical guidelines recommend regularglucose monitoring, with diabetic patients advised to measure theirglucose levels at least three times a day (up to ten times for Type 1diabetes patients).

[005] Over the past few decades, numerous techniques have beenexplored to develop non-invasive blood glucose monitors. Optical methodssuch as fluorescence spectroscopy, photoacoustic spectroscopy,polarimetry, optical coherence tomography, near-infrared spectroscopy,and Raman spectroscopy have received significant attention. However,these methods suffer from poor signal-to-noise ratio, inadequate linearityand sensitivity, susceptibility to environmental variations, lack of accuracy,and challenges related to skin composition.

[006] Alternative methods, including reverse iontophoresis, bio impedancespectroscopy, ultrasound, and electromagnetic glucose sensingtechniques, have also been studied extensively. However, they aresensitive to environmental changes, skin thickness, and affected byphysiological time lags associated with blood glucose levels.

[007] However, existing methods face challenges, including the cost ofdisposable test strips, invasiveness, and the lack of clinically dependablenon-invasive blood glucose monitors. Recently introduced minimallyinvasive monitors have limitations such as limited lifespan, unstableaccuracy, and the need for invasive calibration methods.

[008] There is thus a need for a system and method for measuring theglucose level of the user in a more efficient manner by eliminating theneed for pain, discomfort, and the associated risks of infection and skinirritation that may arise from invasive procedures.SUMMARY

[009] Embodiments in accordance with the present invention provide anon-invasive glucose measurement device designed to measure bloodglucose levels in users. The non-invasive glucose measurement devicecomprises a finger placement hole designed upon a body to receive auser's finger for measuring blood glucose levels. It includes a glucosesensor module with an infrared transmitter and a visible laser transmitter,along with a photodiode for receiving refracted beams of light. The devicealso features a screen for displaying the measured blood glucose level. Acontroller is connected to these components and is responsible forreceiving and analyzing the light signals, determining voltage output andnumerical values of blood glucose concentration, generating intensityadjustment signals, and activating the screen. The device is powered by apower supply module and can be operated using a power adapter.

[0010] Embodiments in accordance with the present invention furtherprovide method for measuring blood glucose levels using the non-invasiveglucose measurement device. The method involves several steps. Itbegins with positioning the user's finger through the finger placement hole.The device generates a first beam of infrared light using the infraredtransmitter, which is received by the photodiode. The voltage output fromthe received infrared light is determined, and an intensity adjustment signalis generated based on this output. The method adjusts the intensity of thesecond beam of visible laser light using the intensity adjustment signal.The adjusted visible light is transmitted, received by the photodiode, andused to calculate the blood glucose concentration. Finally, the calculatedglucose concentration is displayed on the screen. The method ensuresautomatic intensity adjustment of the visible laser light within a specificrange, optimizing accuracy in the measurement process.

[0011] Embodiments of the present invention may provide a number ofadvantages depending on its particular configuration. First, embodimentsof the present application provide a system and a method for measuringblood glucose levels without the need of invasive procedures such asfinger pricking or blood sampling.

[0012] Next, embodiments of the present application may offer a pain-freeand more comfortable experience for the users, especially for individualswith needle phobia or sensitive skin.

[0013] Next, embodiments of the present application may allow user tomeasure their blood glucose levels conveniently and frequently without theneed for complex procedures or specialized training.

[0014] Next, embodiment of the present application may enable the user tomonitor their glucose level consistently, leading to better management oftheir condition and improved health outcomes.

[0015] These and other advantages will be apparent from the presentapplication of the embodiments described herein.

[0016] The preceding is a simplified summary to provide an understandingof some embodiments of the present invention. This summary is neither anextensive nor exhaustive overview of the present invention and its variousembodiments. The summary presents selected concepts of theembodiments of the present invention in a simplified form as anintroduction to the more detailed description presented below. As will beappreciated, other embodiments of the present invention are possibleutilizing, alone or in combination, one or more of the features set forthabove or described in detail below.BRIEF DESCRIPTION OF THE DRAWINGS

[0017] The above and still further features and advantages ofembodiments of the present invention will become apparent uponconsideration of the following detailed description of embodiments thereof,especially when taken in conjunction with the accompanying drawings,and wherein:

[0018] FIG. 1 illustrates a block diagram depicting a non-invasive glucosemeasurement device;

[0019] FIG. 2A depicts a circuit diagram of the proposed device;

[0020] FIG. 2B depicts a circuit diagram of the trans-impedance amplifier;

[0021] FIG. 3A-3C depicts graphical representation of in vitromeasurement results obtained during the experiment;

[0022] FIG. 4A illustrates the working of the non-invasive blood glucosemonitoring device;

[0023] FIG. 4B shows a graphical representation of the comparisonbetween the blood glucose levels measured by the non-invasive prototypeand the active Accu-check machine;

[0024] FIG. 5 depicts a flowchart of a method for measuring the bloodglucose concentration, according to an embodiment of the presentinvention.

[0025] The headings used herein are for organizational purposes only andare not meant to be used to limit the scope of the description or the claims.As used throughout this application, the word "may" is used in apermissive sense (i.e., meaning having the potential to), rather than themandatory sense (i.e., meaning must). Similarly, the words "include","including", and "includes" mean including but not limited to. To facilitateunderstanding, like reference numerals have been used, where possible,to designate like elements common to the figures. Optional portions of thefigures may be illustrated using dashed or dotted lines, unless the contextof usage indicates otherwise.DETAILED DESCRIPTION

[0026] The following description includes the preferred best mode of oneembodiment of the present invention. It will be clear from this descriptionof the invention that the invention is not limited to these illustratedembodiments but that the invention also includes a variety of modificationsand embodiments thereto. Therefore, the present description should beseen as illustrative and not limiting. While the invention is susceptible tovarious modifications and alternative constructions, it should beunderstood, that there is no intention to limit the invention to the specificform disclosed, but, on the contrary, the invention is to cover allmodifications, alternative constructions, and equivalents falling within thespirit and scope of the invention as defined in the claims.

[0027] In any embodiment described herein, the open-ended terms"comprising," "comprises," and the like (which are synonymous with"including," "having" and "characterized by") may be replaced by therespective partially closed phrases "consisting essentially of," consistsessentially of," and the like or the respective closed phrases "consistingof," "consists of, the like.

[0028] As used herein, the singular forms "a", "an", and "the" designateboth the singular and the plural, unless expressly stated to designate thesingular only.

[0029] FIG. 1 illustrates a block diagram depicting a non-invasive glucosemeasurement device 100, according to an embodiment of the presentinvention. The device 100 may be configured to measure the bloodglucose level of a user. The user may be, for example, but not limited to aperson with diabetes or an individual who needs to check their bloodglucose level. Embodiments of the present invention are intended toinclude or otherwise cover any type of the user including known, relatedart, and / or later developed technologies. Further, the device 100 may beconfigured to provide a more convenient method of monitoring glucoselevels by making the process painless and comfortable for the users.Furthermore, the device 100 provides a more comprehensive picture ofglucose fluctuations and helps the user to make more informed decisionabout their diet, medication, and lifestyle choices. Furthermore, the device100 may be configured to improve the quality of life for people withdiabetes or other conditions that require regular glucose monitoring.

[0030] According to an embodiment of the present invention, the device100 may be adapted to house various components of the device 100 suchas a finger placement hole 102, a glucose sensor module 104, a controller106, a screen 108, a power supply module 110, a power adaptor 112 anda DC voltage buffer 114, and so forth. According to embodiments of thepresent invention, the components of the device 100 may be housed in abody 130 of the device 100.

[0031] Furthermore, the body 130 of the device 100 may be made up of amaterial, for example, but not limited to metal, plastic, polymers, ceramicsand so forth. Embodiments of the present invention are intended to includeor otherwise cover any type of the material including known, related art,and / or later developed technologies. According to embodiments of thepresent invention the body 130 of the device 100 may be of differentshapes and sizes, such as, but not limited to, a cuboid, a cube, acylindrical, a hexagonal, a square, a rectangular, and so forth.Embodiments of the present invention are intended to include or otherwisecover any of the shape and the size for the body 130 of the device 102including known, related art, and / or later developed technologies.

[0032] The finger placement hole 102, located on the body 130 of thedevice 100, is specifically designed to accommodate the user's finger formeasuring their blood glucose level. The hole is carefully constructed toensure a comfortable and secure fit, facilitating accurate measurements.To maintain hygiene, the material used for the hole is smooth, nonirritating, and easy to clean.

[0033] In accordance with the varying thickness of finger skin amongindividuals, the human skin acts as a highly absorbing medium.Recognizing this variability, the device incorporates a consideration of thedifferent layers of skin. Specifically, six layers of skin are taken intoaccount, namely: Epidermis, Capillary Loop, Upper Plexus, ReticularDermis, Deep Plexus, and Hypodermis. These layers contribute to theabsorption rate of the skin, which directly affects the accuracy of glucosemeasurements. Moreover, it is essential to note that the finger placementhole 102 is designed not only to provide a secure fit but also to minimizeexternal ambient light interferences. This design feature ensures that theaccuracy of measurements is not compromised by unwanted external lightsources.

[0034] The glucose sensor module 104 is a vital component of thenon-invasive glucose measurement device, designed to detect and measurethe glucose level in the user's blood using a variety of sensingtechnologies. In particular, it utilizes laser light as a means of accuratelymeasuring blood glucose levels.

[0035] To ensure precise measurements, the glucose sensor module 104incorporates multiple beams of light that are transmitted onto the user'sskin. These beams interact with the skin and undergo changes, such asrefraction and absorption, which are influenced by the user's skinthickness. By detecting the voltage drop in the transmitted and refractedrays caused by the skin thickness, the module104 adjust the intensity ofthe visible laser light accordingly.

[0036] The glucose sensor module 104 employs sophisticated algorithmsand calibration techniques to interpret the electrical signals generated bythe photodiode. These algorithms analyze the changes in the transmittedand refracted light signals to determine the blood glucose concentrationaccurately. By considering factors such as the intensity, wavelength, andcharacteristics of the light signals, the module calculates the glucose levelusing established calibration curves and reference data.

[0037] Further, the glucose sensor module 104 incorporates three keycomponents, an infrared transmitter 116, a visible laser transmitter 118,and a photodiode 120. The infrared transmitter 116 emits a first beam ofinfrared light, while the visible laser transmitter 118 emits a second beamof visible laser light. These beams of light are directed onto the user's skin,where they interact with the underlying blood vessels and tissues.According to a preferred embodiment of the present invention, thewavelength of the second beam of visible laser light is 650 Nanometers(nm).

[0038] The photodiode 120 within the glucose sensor module 104 serves acrucial role in detecting the refracted light from the user's finger. Inaccordance with the embodiment of the present invention, the photodiode120 receives the refracted light as it emerges from the finger. Thisphotodiode 120 is capable of converting the incident light into electricalenergy. The photodiode 120 may be constructed using various materialssuch as silicon, germanium, indium gallium arsenide, or other monolithicphotodiode technologies. The embodiments of the present inventionencompass all types of photodiodes, including existing, related art, andfuture technologies. For instance, the preferred embodiment employs anOPT101 photodiode integrated with an on-chip transimpedance amplifier300.

[0039] The OPT101 photodiode 120, when combined with an on-chiptransimpedance amplifier 300, offers several advantages. It facilitates thedetection, amplification, and conversion of the current generated by thephotodiode into a voltage output. The transimpedance amplifier 300 playsa pivotal role in amplifying the weak current signal produced by thephotodiode 120. This amplifier 300 receives the photodiode's currentsignal and increases its magnitude to provide a stronger and more reliablevoltage output. The precise functioning of the transimpedance amplifier300 is discussed in detail in conjunction with FIG. 2B of the accompanyingdiagram.

[0040] The controller 106 plays a crucial role in analyzing and processingthe data received from the various components of the glucose sensormodule 104. It performs calculations, adjusts the laser intensity, andoutputs the measured blood glucose concentration to the screen 108 forconvenient display to the user.

[0041] In accordance with the embodiment of the present invention, thecontroller 106 may take various forms, including but not limited to aProgrammable Logic Control unit (PLC), a microcontroller, amicroprocessor, a computing device, or a development board. Theembodiments of the present invention encompass all types of controllers,including existing, related art, and future technologies. As an example, thepreferred embodiment utilizes an Arduino Uno board equipped with theATmega328P microcontroller as the controller 106.

[0042] The controller 106 is connected to the infrared (IR) transmitter 116,visible laser transmitter 118, photodiode 120, and screen 108, enabling itto receive the necessary input and provide the desired output. It receives afirst refracted beam of infrared light and a second beam of refracted visiblelaser light from the photodiode 120 of the glucose sensor module 104.

[0043] Using the received input, the controller 106 determines the voltageoutput of the first refracted beam of infrared light and calculates thenumerical value representing the blood glucose concentration based onthe second refracted beam of visible laser light. To ensure accuratemeasurements, the controller 106 compares the determined voltage outputof the first refracted beam of infrared light with pre-stored intensityadjustment data in its memory. This comparison allows the controller 106to generate an intensity adjustment signal, which automatically adjusts theintensity of the second beam of visible laser light. Simultaneously, thecontroller 106 generates an activation signal based on the determinednumerical value of blood glucose concentration. This activation signaltriggers the screen 108, enabling it to display the numerical value of themeasured blood glucose concentration.

[0044] Further, the controller 106 utilizes six slabs, as defined in Table 1,to categorize the voltage drop readings associated with different skinthicknesses. These slabs indicate the transmitted voltage and receivervoltage values that correspond to specific voltage drops.Table1

[0045] By comparing the measured voltage difference with thepreprogrammed six slabs defined in Table 1, the controller 106 determinesthe appropriate intensity level for the second beam of laser light. Theintensity levels are defined in Table 2, which specifies the intensity of thelaser light corresponding to each voltage drop slab.Table 2

[0046] Through this mechanism, the controller 106 ensures precision innon-invasive blood glucose monitoring by dynamically adjusting theintensity of the laser light based on the skin thickness, as determined bythe voltage drop measurements.

[0047] The screen 108 is strategically positioned at the top portion of thedevice 100 to provide easy visibility and accessibility. The screen 108provides a visual or tactile representation of the measured blood glucoseconcentration. Once the controller 106 determines the blood glucose levelusing the data from the glucose sensor module 104, it triggers theappropriate information to be displayed on the screen 108.

[0048] The screen 108 is designed to present the user's blood glucoseconcentration in a clear and easily understandable format. It may utilizevarious display technologies, including CRT, LCD, LED, plasma, OLED, ortouch screen, among others. The embodiments of the present inventionencompass and include any type of display screen 108, including existingtechnologies and those that may be developed in the future.

[0049] Upon displaying the measured blood glucose concentration, thescreen 108 may also be accompanied by an audible alert through abuzzer 128130. This additional feedback mechanism ensures that the useris promptly notified of their blood glucose readings, providing acomprehensive user experience.

[0050] Furthermore, the glucose sensor module 104, the controller 106,and the screen 108 are supplied power through the power supply module110. Further, the power supply module 110 may be configured to ensurethat the device 100 has a stable and reliable power source to functionproperly. According to an embodiment of the present invention, the powersupply module 110 further includes a power switch 122, a voltageregulator 124, and a DC power jerk 126,

[0051] The power switch 122 may be configured to control the powersupply of the device 100. Further, the power switch 122 may be adaptedto turn ON and OFF the device 100. According to an embodiment of thepresent invention, the power switch 122 may be, for example, but notlimited to pushbutton switch, level switch, membrane switch, pull chainswitch and so forth. Embodiments of the present invention are intended toinclude or otherwise cover any type of the power switch 122 includingknown, related art, and / or later developed technologies to turn on / off thedevice 100. In an exemplary scenario, when the user turns ON the powerswitch 122, the power supply module 110 enables the passage of anelectrical circuit, initiating the operation of the device 100. In a differentscenario, if the user turns OFF the power switch 122, the power supplymodule 110 obstructs the current flow, leading to the cessation of device100 functionality in order to preserve power.

[0052] The voltage regulator 124 plays a crucial role in ensuring a stableand regulated output voltage to power the components of the device 100.Regardless of variations in the input voltage received from the powersource, the voltage regulator 124 maintains a constant output voltage. Thepower source may be a battery, an external power supply, or any othersuitable source. The embodiments of the present invention encompassand include various types of power sources, including existing and futuretechnologies. By preventing voltage fluctuations, the voltage regulator 124ensures the proper and uninterrupted operation of the device 100. It maybe implemented using linear regulators, switch-mode regulators, or othersimilar technologies. In the preferred embodiment, an LM7805 voltageregulator is utilized to provide a reliable and consistent voltage level,enabling the efficient and safe functioning of the device 100.

[0053] The DC power jack 126 serves as the interface for connecting anexternal power source to the device 100. It features a cylindrical shapewith a center pin or socket for the positive voltage connection and anoutlet barrel for the ground connection. The DC power jack 126 enablesthe device 100 to be powered by an external DC power supply, such as awall adapter or a dedicated power source.

[0054] Integrated into the device 100, the power adaptor 112 ensures astable power supply from the external source. It safeguards the device 100by preventing excessive current flow and protecting it from damage. Thepower adaptor 112 is designed to facilitate the safe operation of the device100. In the preferred embodiment, a 12VDC power adaptor is utilized toprovide the regulated DC power required by the internal components andcircuits of the device 100.

[0055] The DC voltage buffer 114 plays a critical role in maintaining theintegrity of the input voltage received from the power adaptor 112 at itsoutput without amplification. It safeguards against signal degradation ordistortion and ensures signal integrity, impedance matching, and signalisolation within the electronic circuit. By preserving the accuracy andquality of the measured signals as they pass through the different stagesof the device 100, the DC voltage buffer 114 contributes to maintainingaccuracy in the measured blood glucose concentration. It may beimplemented using operational amplifiers (op-amps), transistors, bufferICs, voltage follower circuits, or other similar technologies. In the preferredembodiment, two LM358 operational amplifiers are used, with the firstconfigured as a non-inverting amplifier and the second as an invertingamplifier, to remove DC offset from the power adaptor 112.

[0056] FIG. 2A depicts a circuit diagram 200 of proposed device 100's,according to an embodiment of the present invention.

[0057] This device operates by utilizing variations in laser light intensity.The circuit incorporate a resistor R1 of 100k ohm, a Light DependentResistor (LDR) R2, R3 of 3.3M ohm, R4 of 3.3M ohm, R5 of 1 mega ohm,R6 of 100k ohm, R7 of 220k ohm, R8 of 15k ohm, R9 of 15k, R10 of 10Mega ohm, R11, a capacitor C1 of 100 nano Farad, C2 of 10μF, C3 of 470nano farad. The components of the circuit are connected to each other ina specified format as shown in FIG. 2A.

[0058] Further, when a finger is inserted into the finger slot 102, a resistorlabeled R2, that is a Light Dependent Resistor (LDR), detects the subtlechanges in light intensity resulting from fluctuations in blood glucose levelsand skin characteristics. These light variations are then converted intominute voltage fluctuations. To amplify these voltage fluctuations, a two-stageamplifier is employed. The first stage involves a non-invertingoperational amplifier (IC1a), while the second stage employs an invertingoperational amplifier (IC1b). This two-stage amplification process results ina gain of approximately 800, which is determined by resistors R5, R7, andR10. The amplified voltage output is obtained from pin 7 of IC1b. Toensure accurate measurements, a miniature button-type LDR is usedinstead of the bulkier ORP12. This choice allows the sensor surface to becompletely covered by the user's finger, effectively preventing any straylight from interfering with the readings. Overall, the device 100demonstrates its functionality by detecting and translating minute changesin light intensity caused by varying blood glucose levels and skincharacteristics. These changes are converted into voltage fluctuations,which are then amplified using a two-stage amplifier, ultimately providingan output indicative of the user's blood glucose concentration.

[0059] FIG. 2B depicts a circuit diagram of the trans-impedance amplifier300, according to an embodiment of the present invention. The photodiode120 in the circuit detects incoming radiant energy and converts it into theequivalent electrical current. The intensity of transmitted light is directlyinfluenced by the concentration of glucose. A higher concentration ofglucose results in more photons striking the surface of the photodiode,thereby increasing the output light intensity and photodiode current.

[0060] The relationship between the photodiode current and the intensityof light is determined by factors such as quantum efficiency and radiantenergy. Quantum efficiency represents the fraction of incident photon fluxthat contributes to the photocurrent in the photodiode 120. Thisrelationship may be described by the equation:η=Ipd(hv / P optical).........(5)Where, η = Quantum efficiencyIpd = Photodiode currentq = Charge of electron (1.60217662x10-19 Columbus)h = Plank's constant (6.626176 x 10-34 Joule-seconds)v= Frequency of photons (P) opticalP optical = Radiant energy in watts

[0061] The on-chip transimpedance amplifier 300, integrated with thephotodiode 120, is responsible for converting the current into a voltageoutput. The voltage output is given by the equation:Ipd=q η(Poptical / hv)=q ηPoptical (λ / hc)λ= wavelength of incident lightc = speed of light in vacuum

[0062] The detected current is then converted into a voltage output using atrans-impedance amplifier (TIA), which detects the incoming radiantenergy and converts it into an equivalent voltage output.Vo=IdRF

[0063] The voltage output (Vo) is directly related to the photodiode currentoutput. The gain of the TIA is determined by the feedback resistor (RF).The photodiode current output increases with glucose concentration, asmore photons reach the photodiode 120 due to the bending of incidentlight. Consequently, the photodiode voltage output increases, enabling theestimation of blood glucose concentration levels (as shown in FIG.2B).Further, the amplifier sends voltage to the controller 106 for furtherprocessing.

[0064] FIG. 3A-3C depicts graphical representation of in vitromeasurement results obtained during the experiment. The measurementswere conducted using an aqueous solution of Glucose-D in distilled water.Separate experimental setups were used to measure the laser refractionproperties and voltage output.

[0065] The visible red laser light passes through the glucose solution andfalls on the screen. The screen is designed to measure the circular spot ofthe laser and its refraction characteristics. The size and properties of thelaser circular spot are influenced by the concentration of Glucose-D in theaqueous solution. These measurements follow the principles andcalculations governed by Snell's law. To measure the voltage outputcorresponding to changes in glucose concentration, a photodiode waspositioned behind the sample holder. The photodiode 120 detects thetransmitted light and converts it into an equivalent voltage output, which isdisplayed on a personal computer.Table

[0066] The graph 300 of the voltage measurement results are furtherdepicted in FIG. 3A. Similarly, the graph 302 illustrates the relationshipbetween the voltage output and the levels of blood glucose concentration.As the concentration of glucose solution increases, the output voltageshows an upward trend.

[0067] In order to establish a mathematical relationship between bloodglucose levels and the voltage output, the below mentioned equation isderived from the plot shown in FIG. 3C:Y = 47.186X + 27.246

[0068] Whereas, FIG. 3C demonstrates the linearity of the in vitromeasurement results with varying glucose concentration, supporting theaccuracy and reliability of the developed non-invasive blood glucosemonitoring system.

[0069] FIG. 4A illustrates the working of the non-invasive blood glucosemonitoring device 100, specifically by placing the human forefinger into theflexible finger hole of the device. The module consists of, the IR transmitter116, the visible light transmitter 118, the photodiode 120, and fingerplacement hole 102. The laser transmitter emits a continuous laser sourcewith a wavelength of 650nm. This laser light passes through the humanforefinger inserted into the flexible finger hole 102.

[0070] The transmitted light falls onto the surface of the photodiode 120.The photodiode detects and converts the intensity of the transmitted lightinto an equivalent current output. To ensure accuracy, the module 104 iscovered to block ambient light that could interfere with the measurements.The current output is then amplified and converted into a voltage output bythe trans-impedance amplifier (TIA) 300. This voltage output is directlyproportional to the concentration of glucose levels in the blood.

[0071] In the experimental setup, voltage measurements were taken fordifferent subjects before and two hours after a meal, considering theintensity levels based on the subjects' skin thickness. The voltagemeasurements were acquired using the controller 106. To ensureprecision and accuracy, each subject's voltage measurement was takenfive times.

[0072] After each voltage measurement, the blood glucose levels of thesubjects were measured using an Accu-check glucose monitoringmachine. The measured voltage and corresponding glucose levels werethen compared to estimate the glucose concentration in the blood. Thisprocess was repeated for 110 volunteer subjects before breakfast in themorning and two hours after lunch. Blood glucose levels typically rise aftera meal and gradually decline over the course of four to five hours.

[0073] The in vivo measurement results are summarized in Table 4, whichpresents the comparison between the voltage measurements obtainedusing the non-invasive device and the blood glucose levels measured bythe invasive Accu-check active blood glucose monitor. The measurementswere conducted before a meal and two hours after food intake.Table

[0074] Additionally, Table 5 provides a typical comparison of blood glucoselevel measurements between the device 100 and the active Accu-checkmachine for each subject.Table

[0075] Further, to visualize the data, FIG. 4B shows a graphicalrepresentation of the comparison between the blood glucose levelsmeasured by the non-invasive device 100 and the active Accu-checkmachine. The graph demonstrates the correlation between the twomeasurement methods, validating the accuracy and effectiveness of thenon-invasive blood glucose monitoring system.

[0076] FIG. 5 presents a flowchart 400 illustrating the method formeasuring the blood glucose concentration using the non-invasive glucosemeasurement device 100, according to an embodiment of the presentinvention. By leveraging infrared and visible light, along with preciseintensity adjustments, this method provides a reliable and user-friendlyapproach to monitoring blood glucose levels.

[0077] At step 402:The method begins by positioning the user's fingerthrough the finger placement hole 102 of the device 100. This allows foraccurate measurement of the blood glucose level without the need forinvasive procedures.

[0078] At step 404: Next, an infrared transmitter 116 within the glucosesensor module 104 generates a first beam of infrared light. This light isspecifically chosen for its ability to penetrate the user's finger and interactwith the glucose molecules present in the blood.

[0079] At step 406: The refracted first beam of infrared light is received bythe photodiode 120 within the glucose sensor module 104.

[0080] At step 408: The voltage output of the received refracted first beamof infrared light is determined, which provides valuable information aboutthe blood glucose level.

[0081] At step 410: The determined voltage output serves as a basis forgenerating an intensity adjustment signal.

[0082] At step 412: Using the intensity adjustment signal, the intensity ofthe second beam of visible laser light is adjusted. The purpose of thisadjustment is to optimize the measurement process and enhance theaccuracy of the blood glucose concentration calculation. The intensity ofthe second beam of visible laser light is automatically adjusted within therange of 5 Mega Watt mW to 10 mW.

[0083] At step 414: The adjusted second beam of visible light istransmitted onto the user finger placed on the finger slot 102.

[0084] At step 416: The refracted beam of second visible light is receivedby the photodiode 120 within the glucose sensor module 104. Therefracted beam of visible light contains important information about theinteraction between the light and the glucose molecules in the blood.

[0085] At step 418: Based on the received refracted beam of visible light,the blood glucose concentration is calculated. This calculation involvesanalyzing the characteristics of the refracted light, such as its intensity andother relevant parameters.

[0086] At step 420: Finally, the calculated blood glucose concentration isdisplayed on the screen 108 of the device 100. This provides the user withreal-time information about their blood glucose level, enabling them tomake informed decisions regarding their health and well-being.

[0087] While the invention has been described in connection with what ispresently considered to be the most practical and various embodiments, itis to be understood that the invention is not to be limited to the disclosedembodiments, but on the contrary, is intended to cover variousmodifications and equivalent arrangements included within the spirit andscope of the appended claims.

[0088] This written description uses examples to disclose the invention,including the best mode, and also to enable any person skilled in the art topractice the invention, including making and using any devices or systemsand performing any incorporated methods. The patentable scope theinvention is defined in the claims, and may include other examples thatoccur to those skilled in the art. Such other examples are intended to bewithin the scope of the claims if they have structural elements that do notdiffer from the literal language of the claims, or if they include equivalentstructural elements within substantial differences from the literal languagesof the claims.

Claims

1. A non-invasive glucose measurement device (100), comprising: a finger placement hole (102) designed upon a body (130) and configured to receive a user's finger for measurement of blood glucose level. a glucose sensor module (104) configured to sense signals representing blood glucose level, wherein the glucose sensor module (104) comprises: an infrared (IR) transmitter (116) configured to generate a first beam of infrared light. a visible laser transmitter (118) configured to generate a second beam of visible laser light. a photodiode (120) configured to receive the refracted beam of infrared light as well as the beam of visible laser. a screen (108) configured to display the measured blood glucose level a controller (106) connected to the infrared (IR) transmitter (116), visible laser transmitter (118), photodiode (120), and screen (108), wherein the controller (106) is configured to: receive a first refracted beam of infrared light and a second beam of refracted visible laser light from the photodiode (120) of the glucose sensor module (104). determine a voltage output of the received first refracted beam of infrared light and a numerical value of the blood glucose concentration of the received second refracted beam of visible laser light. compare the determined voltage output of the first received refracted beam of infrared light with intensity adjustment data pre-stored in a memory. generate an intensity adjustment signal based on the comparison of the first received refracted beam of infrared light with the intensity adjustment data and an activation signal based on the determined numerical value of blood glucose concentration. activate the screen (108) to display the numerical value of the measured blood glucose concentration.

2. The device as claimed in claim 1, wherein the intensity adjustment signal is configured to automatically adjust the intensity of the second beam of visible laser light.

3. The device as claimed in claim 1, wherein the intensity of the second beam of visible laser light may be adjusted within the range of 5 Mega Watt (mW) to 10 mW.

4. The device as claimed in claim 1, wherein the wavelength of the second beam of visible laser light is 650 nm.

5. The device as claimed in claim 1, further including a power supply module (110) configured to supply electrical power to multiple components of the device (100).

6. The device as claimed in claim 5, wherein the power supply module (110) further includes a power switch (122), a voltage regulator (124), and a DC power jack (126).

7. The device as claimed in claim 5, wherein the device (100) includes a power adapter (112) that provides power supply from an external source, wherein the external source may be a battery or the like.

8. The device as claimed in claim 1, further including a DC voltage buffer (114) to replicate the input voltage received from the power adapter (112).

9. A method (300) for measuring blood glucose level of the user, the method (300) comprising the steps of: positioning a user's finger through a finger placement hole (102) of a non-invasive glucose measurement device (100); generating a first beam of infrared light using an infrared transmitter (116) of a glucose sensor module (104) within the device (100); receiving the refracted first beam of infrared light using a photodiode (120) within the glucose sensor module (104); determining a voltage output from the received refracted first beam of infrared light; generating an intensity adjustment signal based on the determined voltage output of the first beam of infrared light; adjusting the intensity of the second beam of visible laser light based on the intensity adjustment signal; transmitting the second beam of visible light with adjusted intensity; receiving the refracted beam of visible light using a photodiode within the glucose sensor module; calculating the blood glucose concentration based on the received refracted beam of visible light; displaying the calculated blood glucose concentration on the screen (108).

10. The method as claimed in claim 9, wherein the intensity adjustment signal automatically adjusts the intensity of the second beam of visible laser light within the range of 5 Mega Watt (mW) to 10 mW.