CN120678425A - Laser Doppler heterodyne noninvasive blood glucose concentration measurement device and method - Google Patents
Laser Doppler heterodyne noninvasive blood glucose concentration measurement device and methodInfo
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- CN120678425A CN120678425A CN202510843723.6A CN202510843723A CN120678425A CN 120678425 A CN120678425 A CN 120678425A CN 202510843723 A CN202510843723 A CN 202510843723A CN 120678425 A CN120678425 A CN 120678425A
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- 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
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- 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
- A61B5/14532—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 for measuring glucose, e.g. by tissue impedance measurement
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
- A61B8/488—Diagnostic techniques involving Doppler signals
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Abstract
The invention discloses a laser Doppler heterodyne noninvasive blood glucose concentration measuring device and method, which belong to the technical field of medical detection, and comprise a laser generating module, an interference light path module and a light path module, wherein the laser generating module comprises a laser, a first 1/2 wave plate and a polarization beam splitter prism which are sequentially connected with the laser, and the interference light path module is respectively connected to two sides of the polarization beam splitter prism and comprises a first optical fiber coupler connected with the polarization beam splitter prism, and a second 1/2 wave plate and a second optical fiber coupler which are sequentially connected with the other side of the polarization beam splitter prism. The invention has the advantages of realizing noninvasive detection, avoiding blood sampling wounds, improving comfort level of patients, having high measurement precision and being capable of rapidly and accurately acquiring blood glucose values by using heterodyne interference and frequency shift technology.
Description
Technical Field
The invention belongs to the technical field of medical detection, and particularly relates to a laser Doppler heterodyne noninvasive blood glucose concentration measuring device and method.
Background
Traditional blood sugar monitoring relies on blood sampling mode, has pain, infection risk and long-term consumable high cost scheduling problem. The existing noninvasive technology (such as near infrared spectrum, impedance method and the like) is difficult to meet clinical requirements due to the problems of insufficient precision, easiness in motion interference or overlarge equipment volume and the like.
Therefore, the laser Doppler heterodyne noninvasive blood glucose concentration measuring device and the laser Doppler heterodyne noninvasive blood glucose concentration measuring method are designed, and high-precision noninvasive blood glucose measurement in a dynamic blood flow environment is achieved through combining Doppler frequency shift theory and a multichannel signal processing algorithm through a laser heterodyne interference technology.
Disclosure of Invention
The invention aims to provide a laser Doppler heterodyne noninvasive blood glucose concentration measuring device and a laser Doppler heterodyne noninvasive blood glucose concentration measuring method, so as to solve the problems in the prior art.
The technical scheme is that the laser Doppler heterodyne noninvasive blood glucose concentration measuring device comprises a laser generating module, an interference light path module and a signal processing module, wherein the laser generating module comprises a laser, a first 1/2 wave plate and a polarization beam splitter prism which are sequentially connected with the laser, the interference light path module is respectively connected to two sides of the polarization beam splitter prism and comprises a first optical fiber coupler connected with the polarization beam splitter prism, a second 1/2 wave plate and a second optical fiber coupler which are sequentially connected with the other side of the polarization beam splitter prism, and the signal processing module is arranged between the first optical fiber coupler and the second optical fiber coupler and comprises an optical fiber beam combiner connected between the first optical fiber coupler and the second optical fiber coupler, and a photoelectric detector and a signal processor which are connected with the optical fiber beam combiner.
Preferably, the initial laser generated by the laser device sequentially passes through the first 1/2 wave plate and the polarization beam splitter prism and then is split into two beams of signal light and local oscillation light with 90 degrees.
Preferably, after the signal light passes through a human blood vessel, the signal light loaded with blood sugar information is generated and then enters the first optical fiber coupler.
Preferably, the local oscillation light sequentially passes through a second 1/2 wave plate and a second optical fiber coupler.
Preferably, the laser produces an initial laser wavelength of 1.55 microns.
Preferably, the first optical fiber coupler and the optical fiber combiner are connected through an optical fiber.
Preferably, the second optical fiber coupler and the optical fiber combiner are connected through an optical fiber.
A method for measuring the blood sugar concentration by laser Doppler heterodyne includes such steps as generating initial laser by S1, rotating it by a certain angle by the first 1/2 wave plate, dividing it into signal light and local oscillator light by polarized light-dividing prism, generating the signal light for loading blood sugar information by S2, introducing it to optical fiber combiner by optical fiber, introducing it to optical fiber after polarization direction is rotated by 90 deg, introducing it to optical fiber by the second 1/2 wave plate, introducing it to optical fiber combiner by optical fiber, heterodyning interference by S4, converting it to electric signal by photoelectric detector, transmitting it to signal processor, processing to obtain heterodyne frequency or phase difference value of blood sugar concentration, and inverting it by algorithm.
Preferably, the signal light in S1 passes through a blood vessel of a human body, and the frequency shift is generated due to the blood flow rate, and the calculation formula of the frequency shift is Δf=λ2vcos θ, wherein Δf represents the frequency shift of the signal light passing through the blood vessel of the human body due to the blood flow rate, λ is the wavelength of the initial laser, the value is 1.55 micrometers, v is the blood flow rate, and cos θ is the light irradiation angle of the signal light.
The invention has the beneficial effects that the initial laser is emitted by the laser, and is divided into signal light and local oscillation light by the polarization beam splitter prism. After the signal light passes through the blood vessel of human body, the frequency shift is generated due to the velocity of blood and the blood sugar information is loaded, the signal light enters the optical fiber beam combiner, the local oscillation light is led into the optical fiber beam combiner through the optical fiber, after heterodyne interference, the signal light is converted into an electric signal by the photoelectric detector, and the electric signal is processed by the signal processor to obtain the blood sugar concentration. The invention can realize noninvasive detection, avoid blood sampling wounds, improve comfort level of patients, has high measurement precision, and can rapidly and accurately acquire blood glucose values by using heterodyne interference and frequency shift technology.
Drawings
FIG. 1 is a schematic diagram of the structure of the present invention;
fig. 2 is a plot of the laser profile in the present invention.
The reference numerals in the figure are 1, a laser light source module, 2, an interference light path module, 3, a signal processing module, 11, a laser, 12, a first 1/2 wave plate, 13, a polarization beam splitter prism, 21, a first optical fiber coupler, 22, a second 1/2 wave plate, 23, a second optical fiber coupler, 31, an optical fiber beam combiner, 32, a photoelectric detector, 33 and a signal processor.
Detailed Description
The following description of the embodiments of the present invention will be made clearly and completely with reference to the accompanying drawings, in which it is apparent that the embodiments described are only some embodiments of the present invention, but not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
Specific example 1:
1-2, in the embodiment, the laser Doppler heterodyne noninvasive blood glucose concentration measuring device comprises a laser generating module 1, a first 1/2 wave plate 12 and a polarization beam splitter prism 13, wherein the first 1/2 wave plate 12 and the polarization beam splitter prism 13 are sequentially connected with the laser 11;
The laser generating module 1 is used for generating laser to perform heterodyne interference, the laser 11 generates initial laser, the initial laser is linear polarized laser, the polarization direction of the initial laser is adjusted through the first 1/2 wave plate 12, and the initial laser is divided into two beams of light which are perpendicular to each other through the polarization beam splitting prism 13, namely signal light and local oscillation light.
The interference light path module 2 is respectively connected to two sides of the polarization splitting prism 13, and comprises a first optical fiber coupler 21 connected with the polarization splitting prism 13, and a second 1/2 wave plate 22 and a second optical fiber coupler 23 which are sequentially connected with the other side of the polarization splitting prism 13;
The interference light path module 2 is used for guiding and processing the signal light and the local oscillation light, so that the signal light and the local oscillation light can enter the optical fiber combiner correctly to perform heterodyne interference. After the signal light passes through the blood vessel of the human body, the signal light loaded with blood sugar information is generated, and the signal light is efficiently coupled into the optical fiber through the first optical fiber coupler 21, so that the transmission loss of the optical signal in the optical fiber is minimum. The signal light is then transmitted to the optical fiber combiner 31 through an optical fiber. The local oscillation light is processed by the second 1/2 wave plate 22, the polarization direction of the local oscillation light is adjusted, the polarization direction of the local oscillation light is rotated by 90 degrees and then coupled into an optical fiber through the second optical fiber coupler 23, and the local oscillation light is transmitted to the optical fiber combiner 31 through the optical fiber.
The signal processing module 3 is disposed between the first optical fiber coupler 21 and the second optical fiber coupler 23, and includes an optical fiber combiner 31 connected between the first optical fiber coupler 21 and the second optical fiber coupler 23, and a photodetector 32 and a signal processor 33 connected to the optical fiber combiner 31.
The signal processing module 3 is used for converting the optical signal from the interference light path module into an electrical signal and further processing to extract blood glucose concentration information. The optical fiber combiner 31 is configured to combine the signal light and the local oscillator into one beam, and ensure heterodyne interference of the signal light and the local oscillator on the same path. The optical signal generated by heterodyne interference contains frequency difference information of signal light and local oscillation light, and the information is related to blood glucose concentration. The optical pad detector 32 converts the received optical signal into an electrical signal, and the output electrical signal contains the frequency and phase information of the heterodyne interference signal, and then transmits the electrical signal to the signal processor 33 to calculate the blood glucose concentration. The signal processor includes a filter, an amplifier, and a digital signal processing unit. The filter is used for removing noise, the amplifier is used for enhancing signal intensity, and the digital signal processing unit analyzes the signals through an algorithm to extract blood glucose concentration information. The signal processor converts the extracted frequency or phase difference value into a blood glucose concentration value through algorithm inversion and displays the blood glucose concentration value on a user interface.
The initial laser generated by the laser 11 sequentially passes through the first 1/2 wave plate 12 and the polarization splitting prism 13 and is split into two signal lights and local oscillation lights with 90 degrees.
The polarization directions of the signal light and the local oscillation light are mutually perpendicular and form an angle of 90 degrees, so that clear interference signals can be generated when heterodyne interference is performed.
The laser 11 produces an initial laser wavelength of 1.55 microns. After passing through the blood vessel of the human body, the signal light for loading blood sugar information is generated and enters the first optical fiber coupler 21.
The laser 11 emits an initial laser light having a wavelength of 1.55 microns. The wavelength of 1.55 microns is less scattered in biological tissue and has moderate absorption of water (one of the main components of blood) and can effectively penetrate the blood vessel of a human body and carry blood glucose information back or directly enter the first optical fiber coupler 21.
The local oscillation light sequentially passes through a second 1/2 wave plate 22 and a second optical fiber coupler 23.
The initial laser beam is split into two beams of vertical light, signal light and local oscillation light by a polarization splitting prism 13. The local oscillation light passes through the second 1/2 wave plate (22) and rotates by 90 degrees through changing the polarization direction of the light, so that the polarization directions of the local oscillation light and the signal light are the same at the moment, and heterodyne interference of the two beams of light is ensured.
The first optical fiber coupler 21 and the optical fiber combiner 31 are connected by an optical fiber.
The second optical fiber coupler 23 and the optical fiber combiner 31 are connected through optical fibers.
The first optical fiber coupler 21 and the second optical fiber coupler 23 can couple signal light and local oscillation light into the optical fibers, so that efficient optical signal transmission is realized.
The laser Doppler heterodyne noninvasive blood glucose concentration measurement method is characterized by comprising the following steps of:
s1, generating initial laser by a laser 11, rotating the initial laser by a certain angle through a first 1/2 wave plate 12, and dividing the initial laser into signal light and local oscillation light through a polarization beam splitter prism 13;
s2, the signal light passes through a human blood vessel to generate signal light loaded with blood glucose information, the signal light is led into an optical fiber through a first optical fiber coupler 21, and the signal light loaded with the blood glucose information enters an optical fiber combiner 31 through the optical fiber;
S3, local oscillation light passes through the second 1/2 wave plate 22, the polarization direction is rotated by 90 degrees, the local oscillation light is led into an optical fiber through the second optical fiber coupler 23, and the local oscillation light enters the optical fiber combiner 31 through the optical fiber;
S4, heterodyne interference is carried out on the signal light and the local oscillation light in the optical fiber combiner 31, then the optical signal is converted into an electric signal through the photoelectric detector 32, the electric signal is transmitted to the signal processor 33, heterodyne frequency or phase difference value of the blood glucose concentration is obtained through processing, and then the blood glucose value is obtained through algorithm inversion.
The signal light in the S1 passes through the blood vessel of the human body, and frequency shift is generated due to the velocity of blood, and the calculation formula of the frequency shift is as follows:
Δf=λ2vcosθ
Wherein Δf represents the frequency shift of the signal light passing through the blood vessel of the human body due to the blood flow velocity, λ is the wavelength of the initial laser, the value is 1.55 μm, v is the blood flow velocity, and cos θ is the angle of the signal light irradiation.
When the signal light passes through a blood vessel of a human body, the frequency of the signal light changes due to the flow of blood, and this phenomenon is called doppler shift. The magnitude of the doppler shift is related to the blood flow velocity, the wavelength of the signal light, and the angle between the signal light and the blood flow direction. By calculating the Doppler shift, the blood flow velocity can be indirectly measured, thereby assisting in the measurement of the blood glucose concentration. In the present invention, since the signal light passes through the blood vessel of the human body directly, the incident angle of the signal light is 0 and the value of the incident angle is 1.
The working principle is that when in use, the laser 11 generates initial laser, the polarization direction of the initial laser is adjusted by the first 1/2 wave plate 12, and then the initial laser is divided into two beams of mutually perpendicular light, namely signal light and local oscillation light by the polarization beam splitter prism 13. After the signal light passes through the blood vessel of the human body, the signal light loaded with blood sugar information is generated, and the signal light is efficiently coupled into the optical fiber through the first optical fiber coupler 21 and is efficiently transmitted to the optical fiber combiner 31 through the optical fiber. The local oscillation light is processed by the second 1/2 wave plate 22, the polarization direction of the local oscillation light is adjusted to make the polarization directions of the local oscillation light and the signal light identical, and then the local oscillation light is coupled into the optical fiber through the second optical fiber coupler 23, and then the local oscillation light is transmitted to the optical fiber combiner 31 through the optical fiber. The optical fiber combiner 31 optically couples the signal light and the local oscillation into one beam, and transmits the beam to the photodetector 32, and the photodetector 32 converts the received optical signal into an electrical signal and transmits the electrical signal to the signal processor 33. The signal processor 33 processes and analyzes the received electrical signals to extract key parameters related to blood glucose concentration, such as heterodyning frequency or phase difference. The signal processor 33 converts the extracted frequency or phase difference value into a blood glucose concentration value through an algorithm inversion, and displays the blood glucose concentration value on a user interface.
The preferred embodiments have been shown and described, but are not to be construed as limiting the invention itself. Various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims.
Claims (9)
1. The laser Doppler heterodyne noninvasive blood glucose concentration measuring device is characterized by comprising
The laser generating module (1) comprises a laser (11), a first 1/2 wave plate (12) and a polarization beam splitter prism (13), wherein the first 1/2 wave plate (12) and the polarization beam splitter prism (13) are sequentially connected with the laser (11);
The interference light path module (2), the interference light path module (2) is respectively connected at two sides of the polarization beam splitter prism (13), and comprises a first optical fiber coupler (21) connected with the polarization beam splitter prism (13), a second 1/2 wave plate (22) and a second optical fiber coupler (23) which are sequentially connected with the other side of the polarization beam splitter prism (13), and
The signal processing module (3) is arranged between the first optical fiber coupler (21) and the second optical fiber coupler (23), and comprises an optical fiber combiner (31) connected between the first optical fiber coupler (21) and the second optical fiber coupler (23), and a photoelectric detector (32) and a signal processor (33) which are connected with the optical fiber combiner (31).
2. The laser Doppler heterodyne noninvasive blood glucose concentration measuring device according to claim 1, wherein the initial laser generated by the laser (11) sequentially passes through the first 1/2 wave plate (12) and the polarization beam splitting prism (13) and is split into two signal lights and local oscillation lights with 90 degrees.
3. The laser Doppler heterodyne noninvasive blood glucose concentration measurement device according to claim 2, wherein the signal light passes through a blood vessel of a human body, generates signal light loaded with blood glucose information, and enters the first optical fiber coupler (21).
4. The laser Doppler heterodyne noninvasive blood glucose concentration measuring device according to claim 3, wherein the local oscillation light sequentially passes through a second 1/2 wave plate (22) and a second optical fiber coupler (23).
5. The laser Doppler heterodyne noninvasive blood glucose concentration measuring device according to claim 4, wherein the initial laser wavelength generated by the laser (11) is 1.55 microns.
6. The laser Doppler heterodyne noninvasive blood glucose concentration measuring device according to claim 5, wherein the first optical fiber coupler (21) and the optical fiber combiner (31) are connected through optical fibers.
7. The laser Doppler heterodyne noninvasive blood glucose concentration measuring device according to claim 6, wherein the second optical fiber coupler (23) and the optical fiber combiner (31) are connected through optical fibers.
8. The laser Doppler heterodyne noninvasive blood glucose concentration measurement method is characterized by comprising the following steps of:
S1, generating initial laser by a laser (11), rotating the initial laser by a certain angle through a first 1/2 wave plate (12), and dividing the initial laser into signal light and local oscillation light through a polarization beam splitter prism (13);
S2, the signal light passes through a human blood vessel to generate signal light loaded with blood sugar information, the signal light is led into an optical fiber through a first optical fiber coupler (21), and the signal light loaded with the blood sugar information enters an optical fiber combiner (31) through the optical fiber;
S3, after the polarization direction of the local oscillation light passes through a second 1/2 wave plate (22) and rotates 90 degrees, the local oscillation light is led into an optical fiber through a second optical fiber coupler (23), and the local oscillation light enters an optical fiber combiner (31) through the optical fiber;
S4, heterodyne interference is carried out on the signal light and the local oscillation light in the optical fiber combiner (31), then the optical signal is converted into an electric signal through the photoelectric detector (32), the electric signal is transmitted to the signal processor (33), heterodyne frequency or phase difference value of the blood glucose concentration is obtained through processing, and then the blood glucose value is obtained through algorithm inversion.
9. The method for non-invasive blood glucose concentration measurement by laser Doppler heterodyne according to claim 8, wherein the signal light in S1 passes through a blood vessel of a human body, and a frequency shift is generated due to a blood flow velocity, and a calculation formula of the frequency shift is as follows:
Δf=λ2vcosθ
Wherein Δf represents the frequency shift of the signal light passing through the blood vessel of the human body due to the blood flow velocity, λ is the wavelength of the initial laser, the value is 1.55 μm, v is the blood flow velocity, and cos θ is the angle of the signal light irradiation.
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN120983007A (en) * | 2025-10-24 | 2025-11-21 | 北京工业大学 | Physiological parameter detection devices and wearable devices |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN120983007A (en) * | 2025-10-24 | 2025-11-21 | 北京工业大学 | Physiological parameter detection devices and wearable devices |
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