WO2026029574A1 - Dispositif électronique de mesure de glycémie à l'aide d'une diode laser à rétroaction distribuée - Google Patents

Dispositif électronique de mesure de glycémie à l'aide d'une diode laser à rétroaction distribuée

Info

Publication number
WO2026029574A1
WO2026029574A1 PCT/KR2025/011362 KR2025011362W WO2026029574A1 WO 2026029574 A1 WO2026029574 A1 WO 2026029574A1 KR 2025011362 W KR2025011362 W KR 2025011362W WO 2026029574 A1 WO2026029574 A1 WO 2026029574A1
Authority
WO
WIPO (PCT)
Prior art keywords
light
electronic device
blood glucose
glucose measurement
reflected
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
PCT/KR2025/011362
Other languages
English (en)
Korean (ko)
Inventor
이중기
이재혁
김영현
슈키아리아지나
안중우
윤용규
이용경
이준영
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Hana Optronics Inc
Samsung Electronics Co Ltd
Original Assignee
Hana Optronics Inc
Samsung Electronics Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from KR1020250028411A external-priority patent/KR20260017941A/ko
Application filed by Hana Optronics Inc, Samsung Electronics Co Ltd filed Critical Hana Optronics Inc
Publication of WO2026029574A1 publication Critical patent/WO2026029574A1/fr
Pending legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01S—DEVICES USING THE PROCESS OF LIGHT AMPLIFICATION BY STIMULATED EMISSION OF RADIATION [LASER] TO AMPLIFY OR GENERATE LIGHT; DEVICES USING STIMULATED EMISSION OF ELECTROMAGNETIC RADIATION IN WAVE RANGES OTHER THAN OPTICAL
    • H01S5/00—Semiconductor lasers
    • H01S5/10—Construction or shape of the optical resonator, e.g. extended or external cavity, coupled cavities, bent-guide, varying width, thickness or composition of the active region
    • H01S5/12—Construction or shape of the optical resonator, e.g. extended or external cavity, coupled cavities, bent-guide, varying width, thickness or composition of the active region the resonator having a periodic structure, e.g. in distributed feedback [DFB] lasers
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01S—DEVICES USING THE PROCESS OF LIGHT AMPLIFICATION BY STIMULATED EMISSION OF RADIATION [LASER] TO AMPLIFY OR GENERATE LIGHT; DEVICES USING STIMULATED EMISSION OF ELECTROMAGNETIC RADIATION IN WAVE RANGES OTHER THAN OPTICAL
    • H01S5/00—Semiconductor lasers
    • H01S5/20—Structure or shape of the semiconductor body to guide the optical wave ; Confining structures perpendicular to the optical axis, e.g. index or gain guiding, stripe geometry, broad area lasers, gain tailoring, transverse or lateral reflectors, special cladding structures, MQW barrier reflection layers
    • H01S5/22—Structure or shape of the semiconductor body to guide the optical wave ; Confining structures perpendicular to the optical axis, e.g. index or gain guiding, stripe geometry, broad area lasers, gain tailoring, transverse or lateral reflectors, special cladding structures, MQW barrier reflection layers having a ridge or stripe structure
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01S—DEVICES USING THE PROCESS OF LIGHT AMPLIFICATION BY STIMULATED EMISSION OF RADIATION [LASER] TO AMPLIFY OR GENERATE LIGHT; DEVICES USING STIMULATED EMISSION OF ELECTROMAGNETIC RADIATION IN WAVE RANGES OTHER THAN OPTICAL
    • H01S5/00—Semiconductor lasers
    • H01S5/30—Structure or shape of the active region; Materials used for the active region
    • H01S5/34—Structure or shape of the active region; Materials used for the active region comprising quantum well or superlattice structures, e.g. single quantum well [SQW] lasers, multiple quantum well [MQW] lasers or graded index separate confinement heterostructure [GRINSCH] lasers

Definitions

  • the present disclosure relates to an electronic device for measuring blood glucose, and more particularly, to an electronic device for noninvasively measuring blood glucose using a distributed feedback laser diode.
  • Invasive blood glucose measurement methods involve collecting a blood sample from a specific body part and measuring blood glucose levels using a glucometer. Because invasive blood glucose measurement methods involve collecting a blood sample, they can cause damage to the user's skin.
  • Noninvasive blood glucose measurement methods refer to methods that measure blood glucose levels by irradiating the skin with light of a specific wavelength and analyzing the reflected light. Because noninvasive blood glucose measurement methods irradiate light and measure blood glucose levels based on the reflected light, they can measure the user's blood glucose level without damaging the skin. Noninvasive blood glucose measurement methods can be used when regular blood glucose monitoring is required.
  • the technical problem to be achieved by the present disclosure is to provide an electronic device capable of non-invasively measuring blood sugar levels in the body using a distributed feedback (DFB) laser diode.
  • DFB distributed feedback
  • a non-invasive blood glucose measurement device including a light source unit for forming light having a plurality of wavelength bands; a light reflector unit for converting a propagation path of the light into a vertical direction through reflection of the light; and a light detector unit for receiving the reflected light that is reflected when the light propagating through the light reflector is incident on the user's skin and is reflected, and converting the reflected light into an electrical signal.
  • a light source is formed on a substrate, and light can be focused onto a light reflector through an optical waveguide formed on the substrate.
  • the light reflector can redirect light traveling substantially parallel to the substrate into a substantially perpendicular direction.
  • an optical system is provided so that the light can be focused onto the skin or fingers of a human body, and the path of the light can be changed. Accordingly, reflected light reflected from the skin is formed outside the path of the incident light, and can be incident onto a photodiode.
  • Figure 1 is a flowchart illustrating a blood sugar level measurement method of an electronic device according to one embodiment.
  • FIG. 2 is a flowchart illustrating a method for setting reference data of the electronic device according to one embodiment.
  • FIG. 3 is a diagram illustrating a non-invasive blood glucose measurement electronic device according to one embodiment.
  • a plurality of DFB laser diodes can be combined to form a DFB laser array. That is, the DFB laser array is composed of a plurality of DFB laser diodes that form light of different wavelength bands, and the DFB laser array can generate a plurality of lights of different wavelength bands to irradiate light onto the skin of a human body.
  • At least some of the light detected can react to blood sugar levels within the skin. Accordingly, when the light reflected from the skin is measured using a photodiode, spectral changes can be identified. Based on these spectral changes in the measured light, blood sugar levels can be measured.
  • the wavelength band and optical output of the DFB laser array change depending on the change in ambient temperature and the amount of current applied, it is necessary to measure the temperature change of the laser light source and adjust the optimal current applied to the laser light source to achieve the desired amount of light in order to control the wavelength band and optical output more accurately.
  • a look-up table can be utilized to derive current application conditions. For example, changes in optical output and wavelength band according to changes in applied current and temperature can be measured in a range of about 10°C to about 40°C. Using the changes in wavelength band and optical output as parameters, a correlation between temperature changes and changes in applied current can be derived. In the present disclosure, a table that organizes the correlation between temperature changes and changes in applied current is called a current look-up table. Using the current look-up table, the amount of applied current for each laser light source to obtain a specific wavelength band and optical output can be determined for the temperature and applied current when the laser light source irradiates light.
  • temperature changes of the laser light source can be measured using a temperature sensor, and wavelength band changes of the laser light source can be measured using an interferometer-based sensor.
  • a temperature sensor can be typically implemented as a thermistor.
  • a thermistor is a sensor that utilizes the change in resistance of a material depending on temperature and can be used to detect the temperature of a circuit.
  • temperature sensors may not be limited to this.
  • temperature sensors can be configured in various ways, such as thermocouples, resistance temperature detectors (RTDs), and infrared temperature sensors.
  • an interferometer-based sensor can be implemented as a Mach-Zehnder interferometer-based sensor.
  • a Mach-Zehnder interferometer-based sensor can precisely measure changes in the wavelength band of a laser by measuring the phase difference of the laser source.
  • interferometer-based sensors may not be limited to this.
  • the photodiode can output a photoelectric signal, which is an electrical signal corresponding to the incident measurement light. Since the photoelectric signal contains noise, it can be filtered.
  • light reflected from the skin and blood can be received, converted into a photoelectric signal via a photodiode, and then filtered to pass only signals of a specific wavelength band. For example, signals of different frequencies can be filtered by modulating a light source and a photodiode at a certain frequency.
  • the signal gain of the filtered specific wavelength band can be calculated. The user's blood sugar level can be measured using the calculated signal gain of the specific wavelength band.
  • Figure 1 is a flowchart illustrating a blood sugar level measurement method according to one embodiment.
  • the operations may be performed sequentially, but are not necessarily performed sequentially.
  • the order of the operations may be changed, and at least two operations may be performed in parallel.
  • S100 to S200 may be understood to be performed in a processor of an electronic device (e.g., processor (900) of FIG. 6).
  • the reference data can be formed by comparing the response gain of multiple wavelength bands of reflected light (measured light) using laser light calculated using the mathematical equation 1 described below with the user's known blood sugar level, and matching the response gain in a specific wavelength band with a large fluctuation with the blood sugar level.
  • the user's known blood sugar level refers to the user's blood sugar level measured using a blood sugar meter according to the prior art. That is, the reference data is provided in the form of a look-up table, and can represent the correlation between the user's actual known blood sugar level and the response gain in a specific wavelength band.
  • FIG. 2 is a flowchart for explaining the reference data setting step of FIG. 1 according to one embodiment.
  • the operations may be performed sequentially, but are not necessarily performed sequentially.
  • the order of the operations may be changed, and at least two operations may be performed in parallel.
  • S110 to S140 may be understood to be performed in a processor of an electronic device (e.g., processor (900) of FIG. 6).
  • an electronic device can determine a user's blood glucose level, which is already known (S110).
  • the user's blood glucose level can be determined by measuring it in advance using an invasive device or other device, and the electronic device can determine the user's blood glucose level based on the user's input blood glucose level information.
  • the electronic device can determine the user's blood glucose level by receiving blood glucose level information stored in another device.
  • the electronic device can irradiate light, for example, laser light, to the user's skin (S120).
  • the electronic device can obtain a response gain from the reflected light (S130). For example, the electronic device can obtain a response gain from the reflected laser light reflected on the skin.
  • glucose exists in the body in extremely small amounts, it is difficult to directly target laser light to glucose via blood vessels.
  • increased blood glucose levels can induce physiological changes in adjacent skin or muscle tissue.
  • changes in blood sugar levels can alter the fluid composition of skin tissue.
  • These changes in skin fluid composition can alter the degree of scattering and absorption of light incident on the skin, thereby altering the characteristics of the reflected light reflected by the skin.
  • the present disclosure can perform the task of setting reference data for each user.
  • the operation of setting the reference data may include a step of determining the user's blood glucose level (S110), a step of irradiating laser light on the user's skin, for example, a body part such as a finger (S120), a step of obtaining a response gain from the reflected laser light by analyzing the response characteristics of the reflected laser light reflected from the laser light irradiated on the skin to obtain a response gain of a specific wavelength band (S130), and a step of deriving a correlation between the user's blood glucose level and the response gain of the reflected laser light to form a look-up table according to the response gain (S140).
  • S110 the user's blood glucose level
  • S120 a step of irradiating laser light on the user's skin, for example, a body part such as a finger
  • S130 a step of obtaining a response gain from the reflected laser light by analyzing the response characteristics of the reflected laser light reflected from the laser light irradiated on the
  • the laser light applied to the present disclosure has multiple wavelength band characteristics, and the response gain for a specific wavelength band ⁇ 1 within the reflected laser light is expressed by the following mathematical expression 1.
  • the above mathematical formula 1 is merely an example to aid understanding, and embodiments of the present disclosure may not be limited thereto.
  • the above mathematical formula 1 may be modified, applied, or expanded in various ways.
  • G ⁇ 1 represents the response gain in the wavelength band ⁇ 1
  • Ir represents the amplitude of the reflected laser light in the wavelength band ⁇ 1
  • Io represents the reference amplitude of the laser light in the wavelength band ⁇ 1 .
  • the electronic device can perform individual blood sugar measurement (S200).
  • an electronic device may irradiate a user's skin with laser light having multiple wavelength bands for blood sugar measurement.
  • the user's measurement site may be a finger.
  • the electronic device may measure the response gain of the reflected laser light reflected through the skin of the measurement site and compare it with a look-up table.
  • the electronic device can noninvasively measure the user's blood sugar by comparing the measured response gain with a stored lock-up table.
  • FIG. 3 is a diagram illustrating a non-invasive blood glucose measurement electronic device according to one embodiment.
  • the non-invasive blood glucose measurement electronic device may include a light source unit (100), a light reflector unit (200), and a light detector unit (300).
  • the light source unit (100) can form laser light having multiple wavelength bands.
  • a plurality of DFB laser diodes can be used to form the laser light, and wires can be connected to each of the DFB laser diodes.
  • the light source unit (100) can include a DFB laser array (110), an optical waveguide (120), and wires (130).
  • the light source unit (100), the light reflector unit (200), and the light detector unit (300) may be accommodated in a housing (600).
  • the housing (600) may form the exterior of the blood glucose measurement electronic device.
  • FIG. 4 is a cross-sectional view illustrating a DFB laser diode according to one embodiment.
  • the DFB laser diode may include an n-type cladding layer (112), an active layer (113), a p-type cladding layer (115), and a contact layer (116) in the form of a compound semiconductor on a substrate (111).
  • a plurality of ridges (10r) can be formed by etching the surface of the contact layer (116). When a plurality of ridges (10r) are formed through etching, a ridge channel can be formed between two adjacent ridges (10r).
  • the ridge (10r) refers to a portion that protrudes upwardly and is formed by a portion of the p-type cladding layer (115) and a portion of the contact layer (116).
  • the ridge channel (10) may be etched to a depth that extends into the active layer (113). In one embodiment, the ridge channel (10) may be etched to a depth that extends to the upper portion of the active layer (113). In other words, the ridge channel (10) may not be etched to the inside of the active layer (113).
  • the depth of the ridge channel (10) may be adjusted in consideration of the mode shape of the emitted light and in accordance with the structure of the optical waveguide.
  • the mode shape of the light refers to the distribution shape of the intensity of the light in a plane perpendicular to the light emitted by the DFB laser diode.
  • a diffraction grating layer (114) may be formed at the bottom of the ridge channel (10).
  • the diffraction grating layer (114) may have a function of allowing light (laser light) emitted from the active layer (113) to emit only a specific wavelength due to a change in refractive index caused by the grating period. That is, the diffraction grating layer (114) may be formed to control the wavelength band of the light emitted from the active layer (113).
  • the wavelength band of the light may include a specific wavelength (or representative wavelength) and a certain band of wavelengths centered on the specific wavelength.
  • the diffraction grating layer (114) may be formed in a grating shape so as to diffract light. Therefore, only light of a specific wavelength band may pass through the diffraction grating layer (114). In other words, the wavelength band of light may be controlled by the diffraction grating layer (114). For example, the wavelength band of light that may pass through the diffraction grating layer (114) may be changed depending on the pitch of the plurality of gratings (or the plurality of slits) forming the diffraction grating layer (114).
  • a protruding ridge (10r) may be formed between two ridge channels (10).
  • An anode (118) may be formed on the ridge (10r).
  • the cathode (117) may be formed on the back surface of the substrate (111).
  • the back surface of the substrate (111) may be polished, and then the cathode (117) may be formed on the back surface of the substrate (111).
  • the polishing may be performed to remove scratches that occur when processing the back surface of the substrate (111) to reduce the thickness of the substrate (111).
  • the polishing may be performed by chemical mechanical polishing (CMP).
  • the anode (118) may be formed on the upper portion of the ridge (10r).
  • an insulating film (119) made of, for example, SiO 2 or Si 3 N 4 material may be formed, and the insulating film (119) on the upper surface of the ridge (10r) may be etched to open a portion of the upper surface of the ridge (10r).
  • a metal material may be deposited on a portion of the upper surface of the opened ridge (10r) to form the anode (118).
  • the anode (118) may be formed to extend to the upper surface of the insulating film (119) formed on the inner surface of the adjacent ridge channel (10) and the upper surface of the insulating film (119) formed on the upper surface of the adjacent ridge (10r). By extending the anode (118) in this way, smooth contact with the anode (118) can be ensured when performing wire bonding or flip-chip processes in subsequent processes.
  • the active layer (113) may have a multi-quantum well structure.
  • the multi-quantum well structure may include a plurality of quantum wells. Barriers may be formed between the plurality of quantum wells. Accordingly, the multi-quantum well may have a structure in which quantum wells and barriers are repeated.
  • the wavelength band of light emitted by the DFB laser diode may be determined by the composition of the compound semiconductor forming the quantum well.
  • FIG. 5 is a cross-sectional view illustrating a DFB laser array in which the DFB laser diodes of FIG. 4 are combined according to one embodiment.
  • a DFB laser array (110) may include a plurality of DFB laser diodes (11, 12, 13).
  • the pitches of the diffraction grating layers (114a, 114b, 114c) formed under the ridge channels (11a, 12a, 13a) of the plurality of DFB laser diodes (11, 12, 13) may be different from each other. Accordingly, the plurality of DFB laser diodes (11, 12, 13) may emit laser light of different wavelength bands.
  • anodes (118a, 118b, 118c) may be individually formed on the plurality of DFB laser diodes (11, 12, 13).
  • the plurality of DFB laser diodes (11, 12, 13) may share an n-type cladding layer (112) and an active layer (113).
  • the p-type cladding layer (115) may be mutually separated in the process of forming the ridge channels (11a, 12a, 13a) of the plurality of DFB laser diodes (11, 12, 13).
  • the plurality of DFB laser diodes (11, 12, 13) may share the p-type cladding layer (115).
  • a plurality of anodes (118) corresponding to a plurality of ridges (10r) are formed in the plurality of DFB laser diodes (11, 12, 13), and since the n-type cladding layer (112) is commonly used, a single cathode (117) may be formed.
  • a plurality of DFB laser diodes may have a plurality of anodes (118a, 118b, 118c) and a common cathode (117).
  • the common cathode (117) may be connected to ground.
  • an optical waveguide (120) may be connected to a plurality of DFB laser diodes (11, 12, 13) of a DFB laser array (110).
  • the optical waveguide (120) is provided for each of the DFB laser diodes, and laser light oscillating in the active layer may be incident on the optical waveguide (120).
  • the optical waveguide (120) may include a core and a clad surrounding the core.
  • the optical waveguide may be formed of SiN4, and the clad may be formed of SiO2.
  • Laser light oscillating in the active layer may be incident on the core of the optical waveguide (120).
  • the optical waveguide (120) may be formed on a substrate (111).
  • the optical waveguide (120) may form a photonic integrated circuit (PIC) together with DFB laser diodes.
  • PIC photonic integrated circuit
  • multiple laser lights emitted from multiple DFB laser diodes of a DFB laser array (110) can be collected into a smaller area than the multiple DFB laser diodes.
  • a plurality of wires (130) connected to anodes are formed on one side of a DFB laser array (110). Through current supplied to the plurality of wires (130), a plurality of DFB laser diodes of the DFB laser array (110) are individually driven, and the output of the formed laser light can be controlled.
  • laser light including a plurality of wavelength bands supplied through a plurality of optical waveguides (120) of a light source unit (100) may be incident on a light reflection unit (200).
  • the light reflection unit (200) may be formed to change the propagation direction of the laser light.
  • the light reflection unit (200) may be a mirror or a prism.
  • light incident horizontally toward the light reflection unit (200) may have its propagation direction changed to a vertical direction at the light reflection unit (200).
  • the light reflecting portion (200) may be surface treated to reflect incident laser light.
  • a metal film such as aluminum (Al) may be coated on the surface of the prism.
  • a high refractive index thin film and a low refractive index thin film may be alternately laminated using a dielectric to form the surface of the light reflecting portion (200).
  • a low refractive index material e.g., MgF 2
  • a high refractive index material e.g., ZnS
  • laser light traveling upward through the light reflector (200) may be incident on the user's skin and reflected on the user's skin to form reflected laser light.
  • the reflected laser light may be incident on the light detection unit (300).
  • the light detection unit (300) may be positioned at a different location from the light reflection unit (200) and may convert the incident reflected laser light into an electrical signal.
  • the light detection unit (300) may include a photodiode.
  • the photodiode may receive reflected laser light and convert it into an electrical signal.
  • the electrical signal may include various wavelength bands. Accordingly, in a subsequent step, the electrical signal formed by the photodiode may be demodulated for each specific wavelength band, and a response gain may be obtained through the intensity of the demodulated signal.
  • a separate device may be provided to control the direction of the reflected laser light reflected through the user's skin during the above process.
  • a protective material (400) may be installed so that the user's finger can be fixed in a specific direction.
  • the protective material (400) may be installed in the housing (600).
  • the protective material (400) may be a typical material that is transparent to both incident laser light and incident reflected laser light.
  • the protective material (400) may be formed of a transparent material through which laser light can pass.
  • the protective material (400) may be arranged at a certain angle with respect to the lower surface (601) of the housing (600) and in a slanted shape. This allows the reflected laser light reflected by the user's skin to travel along a different path from the path of the laser light traveling from the light reflection unit (200). Accordingly, the phenomenon of the reflected laser light being re-incident to the light reflection unit (200) and re-incident to the DFB laser array (110) can be prevented.
  • FIG. 6 is a block diagram of a non-invasive blood glucose measurement electronic device according to one embodiment of the present disclosure.
  • a non-invasive blood glucose measurement electronic device may include a processor (900), a memory (910), a light source unit (100), a light detection unit (300), and a power supply unit (920).
  • the processor (900) can measure the user's blood sugar level by controlling the light source unit (100) and the light detection unit (300). For example, the processor (900) can control the light source unit (100) to emit laser light including multiple wavelength bands. The laser light emitted from the light source unit (100) can be reflected by a measurement target, such as the user's finger, and incident on the light detection unit (300).
  • a measurement target such as the user's finger
  • the light detection unit (300) can convert the incident reflected laser light into an electrical signal and transmit it to the processor (900).
  • the processor (900) may include a blood sugar determination unit (901).
  • the blood sugar determination unit (901) may obtain a response gain of an electrical signal transmitted from the light detection unit (300).
  • the blood sugar determination unit (901) may compare the response gain with a lookup table stored in the memory (910) to determine the user's blood sugar level.
  • the blood sugar determination unit (901) may be formed using software.
  • the blood sugar determination unit (801) may be formed integrally with the processor (900) or may be formed separately.
  • a non-invasive blood glucose measurement electronic device may include one or more processors (900).
  • the one or more processors (900) may include one or more of a central processing unit (CPU), a many integrated core (MIC), a field programmable gate array (FPGA), a digital signal processor (DSP), and a hardware accelerator.
  • the one or more processors (900) may control any one or any combination of components of the blood glucose measurement device, or perform operations or data processing in relation to communication.
  • the one or more processors (900) execute one or more programs stored in at least one memory (910).
  • the number of processors (900) may be one or more.
  • the processor (900) may have a multi-core processor structure such as a dual core, a quad core, or a hexa core.
  • the processor (900) can control the operations of the electronic device by executing instructions stored in the memory (910).
  • the processor (900) may correspond to a plurality of processors that collectively perform a plurality of operations by dividing them among the processors.
  • the memory (910) can store a look-up table.
  • the memory (910) can store a look-up table formed in the reference data setting step of FIGS. 1 and 2.
  • the memory (910) can store a look-up table indicating a correlation between a known user's blood sugar level and reflected laser light.
  • the memory (910) is executed by the processor (900) and may include computer instructions that enable the processor (900) to perform its functions.
  • the power supply unit (920) may be configured to supply power to electronic components constituting the blood glucose measurement electronic device.
  • the power supply unit (920) may supply power to the processor (900), memory (910), light source unit (100), and light detection unit (300).
  • a non-invasive blood glucose measurement electronic device may include a current control unit (930) and a temperature sensor (932).
  • the temperature sensor (932) can measure the temperature around the blood glucose measurement electronic device and transmit an electrical signal containing temperature information to the processor (900).
  • a thermistor can be used as the temperature sensor (932).
  • the current control unit (930) is formed to be able to control the amount of current supplied from the power supply unit (920) to the light source unit (100).
  • the processor (900) can control the current control unit (930) in response to an electric signal input from a temperature sensor (932).
  • the processor (900) can control the current control unit (930) according to the ambient temperature of the blood glucose measurement electronic device to supply an optimal current corresponding to the ambient temperature to the light source unit (100).
  • the processor (900) can recognize the optimal current value according to temperature using the current look-up table stored in the memory (910).
  • a noninvasive blood glucose measurement electronic device may include a display (940).
  • the display (940) may be configured to display the blood sugar level measured by the processor (900).
  • the processor (900) may control the display (940) to display the user's measured blood sugar level on the display (940).
  • a non-invasive blood glucose measurement electronic device may include a communication unit (950).
  • FIG. 7 is a diagram illustrating a non-invasive blood glucose measurement electronic device according to one embodiment.
  • the configuration of the light source unit (100) is substantially the same as that described in FIG. 3. That is, it has a DFB laser array (110) composed of a plurality of DFB laser diodes, and the DFB laser array (110) can generate laser light including a plurality of wavelength bands. The generated laser light can travel to the light reflection unit (200) through the optical waveguide (120).
  • the light reflector (200) can change the path of the laser light in a substantially vertical direction.
  • the optical system (500) may include at least two lenses (510, 520).
  • the optical system (500) may include a first lens (510) and a second lens (520).
  • the first lens (510) and the second lens (520) may have a shape in which their side surfaces are in contact with each other.
  • the light detection unit (300) may include a photodiode.
  • the photodiode may receive reflected laser light and convert it into an electrical signal.
  • the electrical signal may have various wavelength bands. Therefore, in a subsequent step, the electrical signal formed by the photodiode may be demodulated for each specific wavelength band, and a response gain may be obtained through the intensity of the demodulated signal.
  • the auxiliary processor (1023) may control at least a portion of functions or states associated with at least one component (e.g., the display module (1060), the sensor module (1076), or the communication module (1090)) of the electronic device (1001), for example, on behalf of the main processor (1021) while the main processor (1021) is in an inactive (e.g., sleep) state, or together with the main processor (1021) while the main processor (1021) is in an active (e.g., application execution) state.
  • the auxiliary processor (1023) e.g., an image signal processor or a communication processor
  • the wireless communication module (1092) may support various technologies for securing performance in a high-frequency band, such as beamforming, massive multiple-input and multiple-output (MIMO), full dimensional MIMO (FD-MIMO), array antenna, analog beam-forming, or large scale antenna.
  • the wireless communication module (1092) may support various requirements specified in the electronic device (1001), an external electronic device (e.g., the electronic device (1004)), or a network system (e.g., the second network (1099)).
  • commands or data may be transmitted or received between the electronic device (1001) and an external electronic device (1004) via a server (1008) connected to a second network (1099).
  • Each of the external electronic devices (1002 or 1004) may be the same or a different type of device as the electronic device (1001).
  • all or part of the operations executed in the electronic device (1001) may be executed in one or more of the external electronic devices (1002, 1004, or 1008).
  • each component e.g., a module or a program of the above-described components may include one or more entities, and some of the entities may be separated and placed in other components.
  • one or more components or operations of the aforementioned components may be omitted, or one or more other components or operations may be added.
  • a plurality of components e.g., a module or a program
  • the integrated component may perform one or more functions of each of the plurality of components identically or similarly to those performed by the corresponding component among the plurality of components prior to the integration.
  • the operations performed by a module, program, or other component may be executed sequentially, in parallel, iteratively, or heuristically, or one or more of the operations may be executed in a different order, omitted, or one or more other operations may be added.
  • a non-invasive blood glucose measurement electronic device may include a light source unit (e.g., 100 of FIG. 3) for forming light including a plurality of wavelength bands, a light reflector unit (200 of FIG. 3) for reflecting the light and converting the light's propagation path into a vertical direction, and a light detector unit (300 of FIG. 3) for receiving the reflected light reflected by the light reflector and incident on the user's skin and converting it into an electrical signal.
  • a light source unit e.g., 100 of FIG. 3
  • a light reflector unit 200 of FIG. 3
  • a light detector unit 300 of FIG. 3
  • the DFB laser diode may include an n-type cladding layer formed on a substrate, an active layer formed on the n-type cladding layer and performing a light-emitting operation, a p-type cladding layer formed on the active layer, and a ridge channel formed by etching the p-type cladding layer.
  • the plurality of DFB laser diodes may determine an emission wavelength band by a period of a diffraction grating layer formed under the ridge channel.
  • the plurality of DFB laser diodes may share the n-type cladding layer and the active layer.
  • the light reflecting portion may have a prism, and the prism may be coated with a metal film or have an alternating laminated structure of a high refractive index thin film and a low refractive index thin film.
  • the non-invasive blood glucose measurement device may further include a protective material (400 in FIG. 3) to enable the user's skin to be fixed in a specific direction.
  • a protective material 400 in FIG. 3
  • a non-invasive blood glucose measurement device may further include an optical system (500 in FIG. 7) disposed above the light reflecting portion, for focusing the light reflected from the light reflecting portion, and for transmitting the reflected light reflected from the user's skin to the light sensing portion.
  • an optical system 500 in FIG. 7
  • the optical system may include a first lens (510 in FIG. 7) for focusing the light and a second lens (520 in FIG. 7) for focusing the reflected light.
  • the first lens and the second lens may have a shape in which their side surfaces are in contact with each other.
  • the first lens and the second lens may have a lens shape in the direction in which the light propagates.
  • the second lens can transmit the reflected light to the light detection unit.
  • a non-invasive blood glucose measurement device may further include a processor (900 of FIG. 6) that controls the light source unit and the light detection unit to measure the user's blood glucose level.
  • the non-invasive blood glucose measurement device may further include a memory (910 of FIG. 6) that stores a look-up table representing a correlation between the user's known blood glucose level and the reflected light.

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Abstract

L'invention concerne un dispositif électronique non invasif pour la mesure de la glycémie à l'aide d'un réseau laser comprenant une pluralité de bandes de longueur d'onde formées dans une diode laser à rétroaction distribuée. Le dispositif électronique non invasif pour la mesure de la glycémie comprend : une unité de source de lumière pour former de la lumière comportant une pluralité de bandes de longueur d'onde ; une unité de réflexion de lumière pour réfléchir la lumière pour changer un trajet de déplacement de la lumière vers la direction verticale ; et une unité de détection de lumière pour recevoir une lumière réfléchie dans laquelle la lumière se déplaçant après avoir été réfléchie par l'unité de réflexion de lumière est incidente sur la peau d'un utilisateur puis réfléchie, et la convertir en un signal électrique.
PCT/KR2025/011362 2024-07-30 2025-07-30 Dispositif électronique de mesure de glycémie à l'aide d'une diode laser à rétroaction distribuée Pending WO2026029574A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
KR10-2024-0101087 2024-07-30
KR20240101087 2024-07-30
KR10-2025-0028411 2025-03-05
KR1020250028411A KR20260017941A (ko) 2024-07-30 2025-03-05 분포 궤환 레이저 다이오드를 이용한 혈당 측정 전자 장치

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WO2026029574A1 true WO2026029574A1 (fr) 2026-02-05

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PCT/KR2025/011362 Pending WO2026029574A1 (fr) 2024-07-30 2025-07-30 Dispositif électronique de mesure de glycémie à l'aide d'une diode laser à rétroaction distribuée

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090043178A1 (en) * 2006-07-25 2009-02-12 Edward Belotserkovsky Optical non-invasive blood monitoring system and method
KR20140048791A (ko) * 2012-10-16 2014-04-24 한국전자통신연구원 측정 장치 및 그것의 당 농도 측정 방법
KR20140130936A (ko) * 2013-05-02 2014-11-12 한국전자통신연구원 리지 도파로형 반도체 레이저 다이오드 및 그 제조방법
KR20160051471A (ko) * 2014-11-03 2016-05-11 삼성전자주식회사 수직 적층 구조를 갖는 분광기 및 이를 포함하는 비침습형 생체 센서
KR20200014524A (ko) * 2018-08-01 2020-02-11 삼성전자주식회사 대상체의 성분 분석 장치 및 방법과, 이미지 센서

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090043178A1 (en) * 2006-07-25 2009-02-12 Edward Belotserkovsky Optical non-invasive blood monitoring system and method
KR20140048791A (ko) * 2012-10-16 2014-04-24 한국전자통신연구원 측정 장치 및 그것의 당 농도 측정 방법
KR20140130936A (ko) * 2013-05-02 2014-11-12 한국전자통신연구원 리지 도파로형 반도체 레이저 다이오드 및 그 제조방법
KR20160051471A (ko) * 2014-11-03 2016-05-11 삼성전자주식회사 수직 적층 구조를 갖는 분광기 및 이를 포함하는 비침습형 생체 센서
KR20200014524A (ko) * 2018-08-01 2020-02-11 삼성전자주식회사 대상체의 성분 분석 장치 및 방법과, 이미지 센서

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