CN111436917A - Photoelectric volume pulse wave acquisition method - Google Patents
Photoelectric volume pulse wave acquisition method Download PDFInfo
- Publication number
- CN111436917A CN111436917A CN202010267648.0A CN202010267648A CN111436917A CN 111436917 A CN111436917 A CN 111436917A CN 202010267648 A CN202010267648 A CN 202010267648A CN 111436917 A CN111436917 A CN 111436917A
- Authority
- CN
- China
- Prior art keywords
- light
- receiving end
- photosensitive
- photoplethysmography
- signal receiving
- 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
Links
- 238000000034 method Methods 0.000 title claims abstract description 14
- 238000013186 photoplethysmography Methods 0.000 claims abstract description 25
- 238000007493 shaping process Methods 0.000 claims abstract description 22
- 230000003287 optical effect Effects 0.000 claims abstract description 17
- 238000000576 coating method Methods 0.000 claims description 13
- 239000011248 coating agent Substances 0.000 claims description 10
- 239000000463 material Substances 0.000 claims description 6
- 238000010521 absorption reaction Methods 0.000 claims description 3
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 claims 1
- 229910052802 copper Inorganic materials 0.000 claims 1
- 239000010949 copper Substances 0.000 claims 1
- HEQBUZNAOJCRSL-UHFFFAOYSA-N iron(ii) chromite Chemical compound [O-2].[O-2].[O-2].[Cr+3].[Fe+3] HEQBUZNAOJCRSL-UHFFFAOYSA-N 0.000 claims 1
- 238000006073 displacement reaction Methods 0.000 description 5
- 238000010586 diagram Methods 0.000 description 3
- 238000001579 optical reflectometry Methods 0.000 description 3
- GXDVEXJTVGRLNW-UHFFFAOYSA-N [Cr].[Cu] Chemical compound [Cr].[Cu] GXDVEXJTVGRLNW-UHFFFAOYSA-N 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 2
- 206010070834 Sensitisation Diseases 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- 230000008313 sensitization Effects 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
- G02B27/09—Beam shaping, e.g. changing the cross-sectional area, not otherwise provided for
- G02B27/0916—Adapting the beam shape of a semiconductor light source such as a laser diode or an LED, e.g. for efficiently coupling into optical fibers
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
- G02B27/09—Beam shaping, e.g. changing the cross-sectional area, not otherwise provided for
- G02B27/0938—Using specific optical elements
- G02B27/095—Refractive optical elements
- G02B27/0955—Lenses
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
- G02B27/30—Collimators
Landscapes
- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Optics & Photonics (AREA)
- General Physics & Mathematics (AREA)
- Surgery (AREA)
- General Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Engineering & Computer Science (AREA)
- Animal Behavior & Ethology (AREA)
- Biomedical Technology (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Physiology (AREA)
- Cardiology (AREA)
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
A photoplethysmography acquisition method comprises the following steps: 1) the light emitting end generates divergent light; 2) shaping the diverging light into parallel light or quasi-parallel light; 3) placing a photosensitive element in a grid collimator with a specific depth, so that a photosensitive signal receiving end can only receive light signals incident at an angle larger than a specific angle; the collecting device comprises a light emitting end, a shaping optical element and a photosensitive signal receiving end, wherein the shaping optical element is arranged around the light emitting end and is used for shaping divergent light into parallel light; the photosensitive signal receiving end is a photosensitive element and further comprises a grid collimator, and after the photosensitive signal receiving end is placed on the grid collimator, the grid collimator is of a grid-shaped structure and allows collimated incident light to reach the photosensitive signal receiving end. By introducing the optical shaping unit and the grid collimator, the anti-interference capability of the photoplethysmography acquisition during human body movement is improved.
Description
Technical Field
The invention relates to the fields of biomedicine and optics, in particular to a method for acquiring photoplethysms.
Background
Wearable equipment for acquiring pulse wave signals by using photoplethysmography is widely applied, but is generally difficult to acquire good pulse wave signals under the conditions of human body movement and shaking. The reasons include: 1) the light emitting end of the current wearable device adopting a photoplethysmography uses a light emitting diode with a large emitting angle as a light source, and the distribution of light signals incident to a human body is greatly changed due to small relative displacement between the light emitting end and the surface of the human body, so that the collected signals are greatly disturbed; 2) the shaking of the wearable equipment easily causes that ambient light penetrates through the gap and is incident on the photosensitive element at a certain small angle, so that great interference is generated on pulse wave light signals; 3) the parallel light emitted by the light source is emitted and scattered by the skin to become large-angle light which is incident to the photosensitive signal receiving end, so that the pulse light signal is greatly changed due to the small displacement of the photosensitive element and the surface of the skin. Based on the problems, the existing photoelectric volume pulse wave acquisition method is not high in robustness, is not beneficial to dealing with movement interference, and cannot obtain reliable pulse wave signals on wearable equipment.
Disclosure of Invention
The invention aims to solve the problems in the prior art, and the invention aims to provide a photoplethysmogram acquisition method which is suitable for application scenes of wearable equipment.
In order to realize the purpose, the following technical scheme is adopted:
a photoplethysmography method, the method comprising the steps of:
1) the light emitting end generates divergent light; 2) shaping the diverging light into parallel light or quasi-parallel light; 3) the photosensitive element is placed in the grid collimator with a specific depth, so that the photosensitive signal receiving end can only receive the light signals incident at an angle larger than a specific angle.
The invention also aims to provide a photoplethysmography acquisition device.
In order to realize the purpose, the following technical scheme is adopted:
a photoplethysmography acquisition device comprises a light emitting end, a shaping optical element and a photosensitive signal receiving end, wherein the light emitting end is used as a light source to generate divergent light; the shaping optical element is arranged around the light-emitting end and shapes the divergent light into parallel light; the photosensitive signal receiving end is a photosensitive element and further comprises a grid collimator, and after the photosensitive signal receiving end is placed on the grid collimator, the grid collimator is of a grid-shaped structure and allows light rays incident at an angle larger than a specific angle to reach the photosensitive signal receiving end.
Further, the photosensitive signal receiving end is a photosensitive element.
Furthermore, the light-emitting end is a light-emitting diode, the shaping optical element is a convex lens, the convex lens is placed in front of the light-emitting diode, the distance is one time of the focal length of the convex lens, and the convex lens shapes divergent light emitted by the light-emitting diode into parallel light.
Further, the shaping optical element is a condensing reflector which is arranged behind the light-emitting end side.
Further, the grid collimator comprises an outer wall and grid-shaped through holes, the side walls of the outer wall and the through holes are coated with coatings, and the coatings are made of materials with large absorption coefficient and small reflection coefficient on infrared light.
Preferably, the outer wall and the side wall of the through hole are coated with infrared blackening coatings.
Preferably, the infrared blackening coating is a copper chromium black material.
Furthermore, the grid collimator has a specific depth, and the photosensitive signal receiving end is placed in the grid collimator with the specific depth, so that the photosensitive signal receiving end can only receive the light signal incident at an angle larger than the specific angle.
Another object of the present invention is to provide a wearable device.
In order to realize the purpose, the following technical scheme is adopted:
a wearable device utilizes the photoplethysmography acquisition device.
The invention has the following beneficial effects:
1. the convex lens is added to converge the light with a large emitting angle of the light-emitting diode, so that the light is emitted into a human body in a parallel light mode, and the anti-interference capability of the photoplethysmography at the light-emitting end when longitudinal micro displacement exists between the light-emitting end and the human body is improved.
2. The depth grid collimator is arranged, interference to pulse light signals caused by direct reflection of ambient light is prevented by using the specific depth grid collimator at the photosensitive signal receiving end, the photosensitive element can only receive light signals incident at an angle larger than a specific angle, and the motion interference resistance of the pulse wave signal acquisition system in the wearable equipment is improved.
In conclusion, the anti-interference capability of the photoplethysmography collection during human body movement is improved by introducing the optical shaping unit and the grid collimator.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to the drawings without creative efforts.
FIG. 1 is a schematic diagram of the light emitting end of the photoplethysmography of the present invention.
FIG. 2 is a schematic diagram of a photo-sensing signal receiving end according to the photoplethysmography method of the present invention.
FIG. 3 is a structural diagram of a photosensitive signal receiving end of the photoplethysmography according to the present invention.
Reference numerals:
the device comprises an outer wall 1, a through hole 2, a side wall 3, a light-emitting end 4, a shaping optical element 5, parallel light 6 and a photosensitive signal receiving end 8.
Detailed Description
Reference will now be made in detail to the exemplary embodiments, examples of which are illustrated in the accompanying drawings. When the following description refers to the accompanying drawings, like numbers in different drawings represent the same or similar elements unless otherwise indicated. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present invention. Rather, they are merely examples of apparatus and methods consistent with certain aspects of the invention, as detailed in the appended claims.
The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used in this specification and the appended claims, the singular forms "a", "an", and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. It should also be understood that the term "and/or" as used herein refers to and encompasses any and all possible combinations of one or more of the associated listed items.
It is to be understood that although the terms first, second, third, etc. may be used herein to describe various information, these information should not be limited to these terms. These terms are only used to distinguish one type of information from another. For example, first information may also be referred to as second information, and similarly, second information may also be referred to as first information, without departing from the scope of the present invention. The word "if" as used herein may be interpreted as "at … …" or "when … …" or "in response to a determination", depending on the context.
The present invention will be described in detail below by way of examples.
Example 1
A photoplethysmography method, the method comprising the steps of: 1) the light emitting end generates divergent light; 2) shaping the diverging light into parallel light or quasi-parallel light; 3) after the photosensitive element is placed in the grid collimator with a specific depth, the photosensitive signal receiving end can only receive the light signal incident at an angle larger than a specific angle.
The light-emitting end generates divergent light which is light with a large emission angle, the light with the large emission angle is shaped, so that light signals are incident to a human body as parallel light or quasi-parallel light, the distribution of the light signals incident to the human body is not obviously changed due to the tiny relative displacement of the light-emitting end and the surface of the human body, and the robustness of a light source is improved.
Aiming at the problem of signal disturbance possibly caused by ambient light and scattered light, the photosensitive signal receiving end only allows light to be incident on the photosensitive element at an angle larger than a specific angle by embedding the photosensitive element into the grid collimator at a specific depth, so that the ambient light mainly incident on the photosensitive end at a small angle is isolated. By controlling the shape of the grid collimator, i.e. the depth-to-width ratio of the individual meshes, a further collimation effect can be achieved, thereby reducing the motion disturbance of the change in distance of the light-sensitive element from the skin.
Example 2
A photoelectric volume pulse wave acquisition device comprises a light-emitting end 4, a shaping optical element 5 and a photosensitive signal receiving end 8, wherein the light-emitting end is used as a light source to generate divergent light; the shaping optical element is arranged around the light-emitting end and shapes the divergent light into parallel light; the photosensitive signal receiving end is a photosensitive element and further comprises a grid collimator, and after the photosensitive signal receiving end is placed on the grid collimator, the grid collimator is of a grid-shaped structure and allows collimated incident light to reach the photosensitive signal receiving end.
The photosensitive signal receiving end is a photosensitive element.
Parallel light is used as a light signal source of the photoplethysmography, interference to pulse light signals caused by direct reflection of ambient light is prevented by using a grid collimator structure, and the motion interference resistance of a pulse wave signal acquisition system in wearable equipment is improved.
Example 3
Referring to fig. 1, the light emitting end 4 is a light emitting diode, the shaping optical element 5 is a convex lens, the convex lens is placed right in front of the light emitting diode, the distance is one focal length time longer than that of the convex lens, and the convex lens shapes divergent light emitted by the light emitting diode into parallel light 6.
The convex lens is placed in front of the light emitting diode, and the distance is one time of the focal length of the convex lens. At this time, the light beam shaped by the convex lens becomes parallel light or quasi-parallel light beam.
By adding the convex lens, the light with a large emission angle of the light-emitting diode is converged, so that the light is incident to a human body in a parallel light mode. The convex lens structure can improve the anti-interference capability of the photoplethysmogram when longitudinal micro displacement exists between the light-emitting end and the human body.
Referring to fig. 2-3, the grid collimator includes an outer wall 1 and a grid-shaped through hole 2, light passes through the through hole 2 and reaches a photosensitive signal receiving end, the outer wall 1 and a side wall 3 of the through hole 2 are coated with a coating, and the coating is made of a material with a large absorption coefficient and a small reflection coefficient for infrared light.
Further, the outer wall 1 and the side wall 3 of the through hole 2 are coated with an infrared blackening coating.
The grid collimator has a specific depth, after the photosensitive signal receiving end is placed in the grid collimator with the specific depth, the outer wall and the side wall of the through hole are light-tight and have low light reflectivity, the light signal 7 incident at a specific angle is less than or equal to that of the light signal 7 incident at the specific angle, the light incident to the photosensitive signal receiving end cannot directly irradiate the photosensitive element through the outer wall and the side wall of the through hole, and cannot be reflected to the photosensitive element through the four walls, so that the photosensitive signal receiving end can only receive the light signal 6 incident at an angle greater than the specific angle.
At the photosensitive signal receiving end, the photosensitive signal receiving end is arranged in the grid collimator of the infrared blackening coating with the specific depth, so that the photosensitive element can only receive the light signals incident at an angle larger than a specific angle. This structure can block the ambient light of passing through skin reflection to the sensitization end when wearable equipment motion shakes, prevents the interference of ambient light to pulse light signal. The pulse wave acquisition method can improve the robustness of signals of the wearable device in daily life.
Preferably, the infrared blackening coating is a copper chromium black material.
The four walls of the grid collimator with the specific depth are light-tight and low in light reflectivity, and light incident to the receiving end cannot penetrate through the four walls to directly irradiate the photosensitive element or cannot be reflected to the photosensitive element through the four walls.
The grid-like structure of the grid collimator of a certain depth achieves the same incident angle limitation as the grid collimator of a single cell at a smaller depth.
Example 4
This embodiment is different from embodiment 3 in that the shaping optical element is a condensing mirror placed behind the light emitting end side.
And at the photosensitive signal receiving end, the photosensitive element is placed in a grid collimator with a specific depth. The four walls of the grid collimator are light-tight and low in light reflectivity, light incident to the receiving end cannot directly irradiate the photosensitive element through the four walls, and cannot be reflected to the photosensitive element through the four walls, so that the photosensitive element can only receive light signals incident at an angle larger than a specific angle.
The above description is only for the purpose of illustrating the preferred embodiments of the present invention and is not to be construed as limiting the invention, and any modifications, equivalents, improvements and the like made within the spirit and principle of the present invention should be included in the scope of the present invention.
Claims (10)
1. A photoplethysmography acquisition method is characterized by comprising the following steps:
1) the light emitting end generates divergent light; 2) shaping the diverging light into parallel light or quasi-parallel light; 3) the photosensitive element is placed in the grid collimator with a specific depth, so that the photosensitive signal receiving end can only receive the light signals incident at an angle larger than a specific angle.
2. The photoplethysmography acquisition device is characterized by comprising a light emitting end (4), a shaping optical element (5) and a photosensitive signal receiving end (8), wherein the light emitting end (4) is used as a light source to generate divergent light; the shaping optical element (5) is arranged around the light-emitting end and shapes the divergent light into parallel light; the photosensitive signal receiving end is a photosensitive element and further comprises a grid collimator, and after the photosensitive signal receiving end is placed on the grid collimator, the grid collimator is of a grid-shaped structure and allows light rays incident at an angle larger than a specific angle to reach the photosensitive signal receiving end.
3. The photoplethysmography apparatus according to claim 2, wherein the photosensitive signal receiving end is a photosensitive element.
4. The photoplethysmography acquisition device according to claim 2, wherein the light emitting end (4) is a light emitting diode, the shaping optical element (5) is a convex lens, the convex lens is placed right in front of the light emitting diode and is a distance twice as long as the focal length of the convex lens, and the convex lens shapes divergent light emitted by the light emitting diode into parallel light.
5. The photoplethysmography acquisition device according to claim 2, wherein the shaping optical element (5) is a light-gathering reflector placed behind the light-emitting end side.
6. The photoplethysmography acquisition device according to claim 2, wherein the grid collimator comprises an outer wall (1) and a grid-shaped through hole (2), the outer wall (1) and a side wall (3) of the through hole (2) are coated with a coating, and the coating is made of a material with a large absorption coefficient and a small reflection coefficient for infrared light.
7. The photoplethysmography acquisition device according to claim 6, wherein the outer wall (1) and the side walls (3) of the through-hole (2) are coated with an infrared blackening coating.
8. The photoplethysmography device of claim 5, wherein the infrared black coating is a copper chrome black material.
9. The photoplethysmography apparatus according to claim 6, wherein the grid collimator has a specific depth, and the receiving end of the photosensitive signal is disposed behind the grid collimator with the specific depth, such that the receiving end of the photosensitive signal can only receive the light signal incident at an angle greater than a specific angle.
10. A wearable device using the photoplethysmography apparatus according to any of the above claims 2-9.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010267648.0A CN111436917A (en) | 2020-04-08 | 2020-04-08 | Photoelectric volume pulse wave acquisition method |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010267648.0A CN111436917A (en) | 2020-04-08 | 2020-04-08 | Photoelectric volume pulse wave acquisition method |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN111436917A true CN111436917A (en) | 2020-07-24 |
Family
ID=71650093
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202010267648.0A Pending CN111436917A (en) | 2020-04-08 | 2020-04-08 | Photoelectric volume pulse wave acquisition method |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN111436917A (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114376532A (en) * | 2020-10-02 | 2022-04-22 | 柯尼卡美能达株式会社 | Reflection-type photoplethysmography sensor and biological information measuring device |
| CN115590466A (en) * | 2021-07-07 | 2023-01-13 | 隆达电子股份有限公司（Tw） | Detection device |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1392507A (en) * | 2001-06-18 | 2003-01-22 | 日本电气株式会社 | Finger print input device |
| EP3081152A1 (en) * | 2015-04-17 | 2016-10-19 | Nokia Technologies Oy | Electrode for a user wearable apparatus |
| US10067056B2 (en) * | 2015-01-06 | 2018-09-04 | Ricoh Company, Ltd. | Optical sensor, optical inspection device, and optical property detection method for detecting light propagated inside a test object |
-
2020
- 2020-04-08 CN CN202010267648.0A patent/CN111436917A/en active Pending
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1392507A (en) * | 2001-06-18 | 2003-01-22 | 日本电气株式会社 | Finger print input device |
| US10067056B2 (en) * | 2015-01-06 | 2018-09-04 | Ricoh Company, Ltd. | Optical sensor, optical inspection device, and optical property detection method for detecting light propagated inside a test object |
| EP3081152A1 (en) * | 2015-04-17 | 2016-10-19 | Nokia Technologies Oy | Electrode for a user wearable apparatus |
Non-Patent Citations (1)
| Title |
|---|
| 刘鹏飞等: "铜铬黑涂层的制备及其红外辐射性能", 《材料热处理学报》 * |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114376532A (en) * | 2020-10-02 | 2022-04-22 | 柯尼卡美能达株式会社 | Reflection-type photoplethysmography sensor and biological information measuring device |
| CN114376532B (en) * | 2020-10-02 | 2024-03-15 | 柯尼卡美能达株式会社 | Reflection type photoplethysmography sensor and biological information measuring device |
| CN115590466A (en) * | 2021-07-07 | 2023-01-13 | 隆达电子股份有限公司（Tw） | Detection device |
| US12342652B2 (en) | 2021-07-07 | 2025-06-24 | Lextar Electronics Corporation | Detection device |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US7321359B2 (en) | Method and device for optical navigation | |
| CA3012691C (en) | Lidar based 3-d imaging with far-field illumination overlap | |
| US4467193A (en) | Parabolic light emitter and detector unit | |
| JP2021099365A (en) | Three dimensional lidar system with targeted field of view | |
| CN109073756A (en) | The imaging of the 3-D based on LIDAR is carried out with the irradiation field density of variation | |
| JP2023110085A (en) | Adaptive multiple-pulse lidar system | |
| EP0864853A3 (en) | Particle analyser and composite lens formed by lens elements of different focal points | |
| CN111436917A (en) | Photoelectric volume pulse wave acquisition method | |
| CN109581323B (en) | Micro-electromechanical laser radar system | |
| CA2101996A1 (en) | Validation of Optical Ranging of a Target Surface in a Cluttered Environment | |
| CN109964421B (en) | Receiver, method, terminal device, light transmission structure and system for visible light communication | |
| CN106950557A (en) | A kind of single photon ranging ambient noise filtering method and single photon range unit modulated based on photon trajectory angular momentum | |
| Dolin et al. | Theory of imaging through wavy sea surface | |
| JP2018513721A (en) | Biological function detection sensor | |
| CN101546016B (en) | Method and apparatus of obtaining directivity | |
| CN210038328U (en) | Optical scanning device and laser radar | |
| CN114296100A (en) | Common-aperture underwater optical system | |
| CA2057545A1 (en) | Light source device | |
| Vollmerhausen et al. | Modeling the target acquisition performance of laser-range-gated imagers | |
| CN209640493U (en) | A kind of laser radar system | |
| CN210181223U (en) | Compact laser radar ranging optical system | |
| RU92002762A (en) | LASER TELESCOPIC SIGHT | |
| CN217820827U (en) | Laser wind measuring radar | |
| US12025742B2 (en) | Scanning flash lidar with micro shutter array | |
| RU2083031C1 (en) | Semiconductor radiator |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| RJ01 | Rejection of invention patent application after publication | ||
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20200724 |