CN111110234B - Skin jaundice detector and detection method - Google Patents
Skin jaundice detector and detection method Download PDFInfo
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- CN111110234B CN111110234B CN201911266978.1A CN201911266978A CN111110234B CN 111110234 B CN111110234 B CN 111110234B CN 201911266978 A CN201911266978 A CN 201911266978A CN 111110234 B CN111110234 B CN 111110234B
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- 238000001514 detection method Methods 0.000 title claims abstract description 52
- 206010023126 Jaundice Diseases 0.000 title claims abstract description 40
- 239000013307 optical fiber Substances 0.000 claims abstract description 83
- 230000001681 protective effect Effects 0.000 claims abstract description 34
- 239000004973 liquid crystal related substance Substances 0.000 claims description 11
- 238000000034 method Methods 0.000 claims description 5
- 238000003825 pressing Methods 0.000 claims description 3
- 241001662043 Icterus Species 0.000 claims 4
- 230000002500 effect on skin Effects 0.000 claims 3
- 238000005259 measurement Methods 0.000 abstract description 13
- 238000013461 design Methods 0.000 abstract description 4
- 229910052724 xenon Inorganic materials 0.000 description 28
- FHNFHKCVQCLJFQ-UHFFFAOYSA-N xenon atom Chemical compound [Xe] FHNFHKCVQCLJFQ-UHFFFAOYSA-N 0.000 description 28
- 239000000835 fiber Substances 0.000 description 27
- 230000004907 flux Effects 0.000 description 10
- 230000003321 amplification Effects 0.000 description 8
- 238000003199 nucleic acid amplification method Methods 0.000 description 8
- 238000010586 diagram Methods 0.000 description 7
- BPYKTIZUTYGOLE-IFADSCNNSA-N Bilirubin Chemical compound N1C(=O)C(C)=C(C=C)\C1=C\C1=C(C)C(CCC(O)=O)=C(CC2=C(C(C)=C(\C=C/3C(=C(C=C)C(=O)N\3)C)N2)CCC(O)=O)N1 BPYKTIZUTYGOLE-IFADSCNNSA-N 0.000 description 6
- 238000012545 processing Methods 0.000 description 6
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- 208000014674 injury Diseases 0.000 description 2
- 230000003287 optical effect Effects 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 230000003595 spectral effect Effects 0.000 description 2
- PDWBGRKARJFJGI-UHFFFAOYSA-N 2-phenylcyclohexa-2,4-dien-1-one Chemical compound O=C1CC=CC=C1C1=CC=CC=C1 PDWBGRKARJFJGI-UHFFFAOYSA-N 0.000 description 1
- 208000012260 Accidental injury Diseases 0.000 description 1
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 1
- 208000027418 Wounds and injury Diseases 0.000 description 1
- 230000000903 blocking effect Effects 0.000 description 1
- 239000003990 capacitor Substances 0.000 description 1
- 230000006378 damage Effects 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 238000004146 energy storage Methods 0.000 description 1
- 238000001914 filtration Methods 0.000 description 1
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- 229910052710 silicon Inorganic materials 0.000 description 1
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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
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/053—Measuring electrical impedance or conductance of a portion of the body
- A61B5/0531—Measuring skin impedance
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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
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
- A61B5/0064—Body surface scanning
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
- G01J1/00—Photometry, e.g. photographic exposure meter
- G01J1/42—Photometry, e.g. photographic exposure meter using electric radiation detectors
- G01J1/44—Electric circuits
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/02—Details of sensors specially adapted for in-vivo measurements
- A61B2562/0233—Special features of optical sensors or probes classified in A61B5/00
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Abstract
The invention discloses a skin jaundice detector, which comprises a laser control output module, a laser output assembly, a skin reflection return light detection assembly and a skin impedance detection module, wherein the laser control output module is used for controlling the laser output assembly to output laser; the laser output assembly is provided with an optical fiber head protective cover, four contact electrodes and a laser output optical fiber, wherein the four contact electrodes are positioned on the optical fiber head protective cover, the laser output optical fiber is positioned at the central position and is provided with a skin contact electrode, and the skin contact electrode and the four contact electrodes on the protective cover form an electric connection and ensure that emergent light is perpendicular to a detected skin surface. The skin jaundice detector and the detection method have the advantages of scientific and reasonable design, easy control of light paths, less interference, high safety, high measurement accuracy and precision, longer service life and lower failure rate.
Description
Technical Field
The invention relates to the technical field of medical detection equipment, in particular to design of a skin jaundice detector and a corresponding detection method.
Background
Most of the existing skin jaundice detection instruments use a high-pressure xenon lamp or an LED lamp to flash strongly, the strong light is guided into the skin through an optical fiber, then the light reflected from the inside of the skin is decomposed and filtered to form light with two wavelengths of 450nm and 550nm, the light intensity of the two wavelengths is converted into an electric signal, and then relevant mathematical operation is carried out to obtain a bilirubin value in the skin. And the xenon lamp has short light-emitting maintaining time, the flash time cannot be controlled, and the repeatability of the measuring result is poor. In addition, such instruments are not provided with a safety protection device, and if the detection optical fiber head is accidentally pressed down, the detection flash can be triggered, so that the eyes of the newborn can be injured. And because do not press angle detection device, cause and also can trigger when detecting that the optic fibre head is not perpendicularly pressed on the skin surface and detect, detection numerical value at this moment will have great error, cause and detect the repeatability relatively poor, the testing result has great relation with operator's gimmick proficiency.
Because the light emitted by the xenon lamp of the percutaneous jaundice detector is a light wave with a wide frequency spectrum range, namely, near whiteThe intensity of light of effective wavelengths (450nm and 550nm) contained in the facet is weak. According to the light source characteristics of the xenon lamp, the luminous efficiency of the xenon lamp is 40 lumens/watt, the power of the short-arc xenon lamp on the percutaneous jaundice meter is not more than 40 watts, and the conversion is carried out to obtain the luminous flux of about 1600 lumens, but because the xenon lamp is a divergent point light source, the light emitted by the point light source needs to be guided to a measuring position through an optical fiber. The xenon lamp has luminous flux of 1600 lumens on the whole spherical surface with the luminous point as the center, and the optical fiber has a light receiving area of about 0.75cm at the optical fiber input port about 3cm away from the luminous point2The total spherical area with a radius of 3cm is about 113cm2Therefore, the actual luminous flux at the input port of the optical fiber is about 1600 x 0.75/113, about 10 lumens (fig. 1), which indicates that the xenon lamp has a high brightness but a low effective light energy utilization rate. In addition, the part of the light is filtered by using a filter, so that the luminous flux of effective light waves (the wavelength of 450nm and the wavelength of 550nm required for measurement) in the part of the light is lower. From the xenon lamp spectral energy distribution diagram (fig. 2, wherein, in fig. 2, 1 xenon lamp cannon luminous point is marked, 2 xenon lamp bulb shell, 3 total luminous flux (1 ═ 1600 lumen) of the whole spherical surface range of the xenon lamp bulb, 4 effective light source input optical fiber head of xenon lamp light source, 5 effective luminous flux (about 1 lumen) of xenon lamp light source input optical fiber, 6 spherical surface of xenon lamp light source at the optical fiber, and 7 effective light source input optical fiber), it can be seen that the energy of two effective wavelengths (450nm wavelength and 550nm wavelength) required by xenon lamp measurement is less than 10% of the total light energy of the whole xenon lamp. Thus, the luminous flux of the effective light wave actually used for measurement does not exceed 1 lumen. Compared with a xenon lamp, the laser has high light efficiency, is light with single wavelength, does not need a filter, and therefore has high light energy utilization rate. After examining the data, it can be known that the output luminous efficiency of the laser is about 683 lumen/watt, for example, the luminous flux of a 450nm wavelength laser with the luminous power of 100mW is 68.3 lumens, and because the laser is monochromatic light, no filter is needed for processing, the directionality and the collimation of the laser are very good, no divergence exists, the laser is easy to collect, and assuming that all the light energy enters the light guide fiber and no light loss exists, the effective luminous flux capable of being measured is 68.3 lumens, which is about sixty times higher than that of a 40 watt xenon lamp light source, so that only about 50mW of laser is needed in practical useThe light source can reach and exceed the light efficiency of a xenon lamp. The laser measurement has high light intensity and better skin penetration effect, so the measured signal-to-noise ratio is high, and the result is more accurate and stable. The xenon lamp can separate the light with two wavelengths through the optical filter, but the optical filter has short service life, and generally ages after several years, so that the filtering effect is reduced, and the accuracy of the measured result is greatly influenced because the light with other wavelengths is mixed into the measuring channel. Moreover, the xenon lamp needs to be started at high voltage for flash starting, and the xenon lamp can be excited to emit light to perform corresponding detection only by enabling a built-in high-voltage circuit of the instrument to realize high-voltage energy storage charging every time the xenon lamp is used, so that continuous measurement and monitoring can not be realized continuously at a required time interval (generally 3-5 seconds), and the failure rate of the instrument is high due to repeated charging and discharging of the built-in high-voltage circuit.
Disclosure of Invention
The invention aims to provide a skin jaundice detector and a detection method.
In order to overcome the defects in the prior art, the invention adopts the following technical scheme:
a skin jaundice detector comprises a laser control output module, a laser output assembly, a skin reflection return light detection assembly, a skin impedance detection module, a CPU module and a display liquid crystal screen; one end of the laser control output module is connected with the laser output assembly, the other end of the laser control output module is connected with the CPU module, and the skin reflection return light detection assembly, the skin impedance detection module and the display liquid crystal screen are respectively connected with the CPU module; the laser output assembly is provided with an optical fiber head protective cover, four contact electrodes and a laser output optical fiber, the four contact electrodes are located on the optical fiber head protective cover, the laser output optical fiber is located at the center, the laser output optical fiber is provided with a skin contact electrode, and the skin contact electrode and the four contact electrodes on the protective cover form an electric connection at the same time.
Further, the laser output fibers comprise a green 532nm wavelength laser output fiber, a blue 450nm wavelength laser output fiber and a shared fiber head, and the fiber head and the shared fiber head are positioned on the fiber head protective cover.
Furthermore, the optical fiber head protective cover can elastically retract, a positioning column and a retraction spring are arranged on the optical fiber head protective cover, a skin contact electrode is arranged on the positioning column and matched with the four contact electrodes, and the retraction spring is sleeved on the positioning column to enable the optical fiber head protective cover to move backwards and contact with the skin when the detected optical fiber head presses the surface of the skin.
Furthermore, the green 532nm wavelength laser output optical fiber, the blue 450nm wavelength laser output optical fiber, the laser control output module, the skin reflection return light detection component, the CPU module and the display liquid crystal screen are all arranged on the shell.
Further, install detachable battery in the casing, lid behind the battery is installed to the tip of casing.
A method for detecting skin jaundice comprises the following steps,
1) a pair of skin reflection return light detection sensors of the jaundice detector detect and receive green 532nm wavelength reflection laser, a pair of blue 450nm wavelength return light detection sensors receive 450nm wavelength laser reflected by skin, a green 532nm wavelength laser output optical fiber and a blue 450nm wavelength laser output optical fiber alternately output twice, and a skin reflection return light detection assembly records the average value of the return light after the two outputs of the same wavelength;
2) after the measurement is started, the CPU module compares and calculates the average light intensity of the two wavelengths to obtain the value of bilirubin in the skin, and therefore the result is displayed on a display liquid crystal screen.
Further, in 1), the lasers with two wavelengths are alternately output twice in turn, each time of output is 10-30ms, the skin reflection return light detection assembly records information, and the CPU module calculates the average value of the return reflected light after the outputs with the same wavelength are twice.
Further, in 1) when jaundice detector's laser output optic fibre and optical fiber head protection casing all set for the dynamics and press perpendicularly on skin, the electricity intercommunication, skin jaundice detects and just can start, and laser can send.
Further, in 1), the jaundice detector judges whether the laser output optical fiber is vertically pressed on the surface of the skin through whether the skin contact electrode on the laser output optical fiber and the four contact electrodes on the optical fiber head protective cover are simultaneously connected, and light leakage is avoided when the output laser is detected.
Further, the CPU module judges whether the laser output optical fiber is in good contact with the skin and vertically placed on the surface of the skin before measurement by judging the level of the circuit output level signal of the skin impedance detection module.
The skin jaundice detector and the detection method provided by the invention are scientific and reasonable in design, and have the following advantages:
1. the invention omits a light filter required by the traditional jaundice detector and has no light attenuation caused by the light filter. The laser is adopted, so that the directivity and the intensity of the laser are stable, the light path is easier to control, the interference is less, and the precision and the accuracy of detection are better;
2. the working voltage of the laser control output module and the laser output assembly is low, the light concentration is good, so that a high-voltage charging and discharging part of a traditional jaundice detecting instrument can be omitted, the laser luminous intensity is stable, uninterrupted or continuous monitoring can be carried out, waiting of a charging process of a xenon lamp light source is not needed, the medical clinical use is greatly facilitated, and the use scene is expanded.
3. The security is better, has increased safe fiber optic head protection casing and has prevented the laser edge leakage design, prevents to examine time measuring, and the unexpected injury to the human body of laser leakage.
4. Precision and degree of accuracy are better, have increased and have pressed the electrode structure who detects perpendicularly, have guaranteed the accuracy of measuring at every turn, prevent the maloperation, and of course the while has also increased the security.
5. Because the laser light source and the corresponding components are adopted, the service life of the instrument is longer, and the failure rate is lower.
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 inventive exercise:
FIG. 1 is a short arc xenon lamp spectral power distribution plot;
FIG. 2 is a schematic diagram of the effective luminous flux of a xenon lamp;
FIG. 3 is a schematic diagram of a functional module of a percutaneous jaundice detector of the present application;
FIG. 4 is a schematic diagram of a pre-amplification circuit of a skin reflection return light detection assembly of the jaundice detector;
FIG. 5 is a schematic diagram of a jaundice meter;
FIG. 6 is a top view of the jaundice meter;
FIG. 7 is a schematic circuit diagram of a skin reflection return light detection assembly of the jaundice meter;
fig. 8 is a schematic circuit diagram of a skin impedance detection module of the jaundice detector.
Detailed Description
The present invention will be described in detail with reference to the drawings and specific embodiments, which are illustrative of the present invention and are not to be construed as limiting the present invention.
As shown in fig. 3-6, a skin jaundice detector includes a laser control output module 190, a laser output assembly, a skin reflection return light detection assembly 180, a skin impedance detection module, a CPU module 170, and a display liquid crystal screen 100; one end of the laser control output module is connected with the laser output assembly, the other end of the laser control output module is connected with the CPU module, and the skin reflection return light detection assembly, the skin impedance detection module and the display liquid crystal screen 100 are respectively connected with the CPU module 170; the laser output assembly is provided with an optical fiber head protective cover 30, four contact electrodes 20 and laser output optical fibers, wherein the four contact electrodes 2090 degree are distributed, the four contact electrodes 20 are positioned on the optical fiber head protective cover 30, the laser output optical fibers are positioned at the center, the laser output optical fibers are provided with skin contact electrodes 10, and the skin contact electrodes 10 and the four contact electrodes 20 on the optical fiber head protective cover 30 form electric connection at the same time. Specifically, the optical fiber head protective cover 30 has a light shielding function and can also be called as an optical fiber head protective cover 30, four contact electrodes 20 on the optical fiber head protective cover 30 are located on the same plane, the optical fiber head protective cover is perpendicular to the plane of the contact electrodes, if the plane of the contact electrodes is in parallel contact with the plane of the skin, the four contact electrodes 20 must be in simultaneous contact with the skin, if one or more contact electrodes 20 in the four contact electrodes 20 are not in contact with the skin, the plane of the contact electrodes 20 must not be parallel to the plane of the skin, and according to the principle of solid geometry, the optical fiber head protective cover 30 cannot be perpendicular to the plane of the skin. Therefore, the equivalent correspondence of four contact electrodes 20 contacting the skin simultaneously with the fiber tip shield 30 contacting the skin perpendicularly to the skin.
The laser output fibers include a green 532nm wavelength laser output fiber 40 and a blue 450nm wavelength laser output fiber 60, and a common fiber tip 40, all of which are located on a fiber tip shield 30.
In some embodiments, the fiber tip protection cover 30 is elastically retractable, the fiber tip protection cover 30 is provided with a positioning column 110 and a retraction spring 80, the positioning column 110 is provided with a skin contact electrode 10, the skin contact electrode 10 is matched with the four contact electrodes 20, and the retraction spring 80 is sleeved on the positioning column 110 to move the fiber tip protection cover 30 backward and contact with the skin when the detected fiber tip is pressed on the skin surface.
When jaundice is detected, the detection head is pressed on the skin, the optical fiber head protective cover 30 moves upwards under the action of pressure, the skin contact electrode 10 of the middle optical fiber is in contact with the skin at the moment, the four contact electrodes 20 on the optical fiber head protective cover 30 are in close contact with the skin under the action of the elastic force of the retraction spring 80, at the moment, if the optical fiber head protective cover 30 is perpendicular to the skin, the contact electrodes 20 on the four optical fiber head protective covers 30 and the skin contact electrode 10 of the middle optical fiber form four conductive loops at the same time, the circuit of the skin impedance detection module can output high level, the CPU module can enter a starting mode after detecting the output high level of the skin impedance detection circuit, and the laser control output module and the laser output assembly are allowed to work. If the fiber head protective cover 30 is not enough in pressing, the middle fiber electrode cannot be in good contact with the skin, the skin impedance detection outputs a low level, the CPU module prevents the laser control output module from working, and the measurement cannot be carried out at the moment. Only when the four contact electrodes 20 are in good contact with the conductive loops at this time, it is indicated that the optical fiber head protective cover 30 is in good contact with the detected optical fiber head and skin, and the direction of the optical fiber head protective cover is vertically placed correctly, and at this time, laser output can be started to detect jaundice. Install trigger formula starting switch 90 of being connected with laser control output module electricity on the casing, the laser head/the optic fibre head that detects is detected to the inside CPU control processing module of jaundice detector and skin contact well and the direction is perpendicular, just can open laser control output module after pressing starting switch 90 again, start going on of detecting, otherwise the instrument can report to the police and report to the wrong suggestion instrument and not place correctly.
Preferably, a green 532nm wavelength laser output fiber, a blue 450nm wavelength laser output fiber, a laser control output module, a skin reflection return light detection assembly, a CPU module and a display liquid crystal screen 100 are mounted on the housing 50. A detachable battery is installed in the case 50, and a battery rear cover is installed at an end of the case 50.
A method for detecting skin jaundice comprises the following steps,
1) a pair of skin reflection return light detection sensors of the jaundice detector detect and receive green 532nm wavelength reflection laser, a pair of blue 450nm wavelength return light detection sensors receive 450nm wavelength laser reflected by skin, a green 532nm wavelength laser output optical fiber and a blue 450nm wavelength laser output optical fiber alternately output twice, and a skin reflection return light detection assembly records the average value of the return light after the two outputs of the same wavelength;
2) after the measurement is started, the CPU module compares and calculates the average light intensities of the two wavelengths to obtain the value of bilirubin in the skin, and the result is displayed on the display liquid crystal panel 100.
In the step 1), the lasers with two wavelengths are alternately output twice in turn, each time of output is 10-30ms, the skin reflection return light detection assembly records information, and the CPU module calculates the average value of the return reflected light after being output twice with the same wavelength. In 1) when jaundice detector's laser output optic fibre and optical fiber head protection casing 30 all set for the dynamics and press perpendicularly on skin, the skin jaundice detects and just can start, and laser can send. In 1) jaundice detector judges whether laser output optical fiber is pressed on skin surface perpendicularly through skin contact electrode 10 that is located laser output optical fiber and four contact electrode 20 that are located optical fiber head protection casing 30, and it goes out to ensure not have light to leak when detecting output laser
Specifically, the circuit of the light intensity detection module and the circuit of the skin impedance detection module are briefly explained as follows:
as shown in fig. 7-8, the PD in the light intensity detection circuit detects the core element silicon photocell, and the PD generates a photocurrent after receiving the returned laser light intensity signal, and the photocurrent generates a voltage on the resistor RL, because the voltage is very weak, and is about microvolt (uv), and the PD enters the post-stage amplification circuit to perform the next amplification processing after passing through the 6-pin output voltage Vo of the IC after performing the preliminary proportional amplification through the 3-pin input end of the IC (LF356 high input impedance operational amplifier chip). The pre-amplified light intensity signal enters a single signal input end and enters a post-stage amplification processing circuit after linear amplification processing (about 100 times amplification) and output impedance conversion of a middle-stage precise amplification module AMP3508, because the maintaining time of each emission of laser is about 20ms, the time of the light intensity signal detected by a photocell is equivalent to a pulse signal, and therefore, in order to increase the signal-to-noise ratio of the signal, the direct current component of the signal needs to be cut off, a blocking capacitor C1 of the signal input end is arranged, and the light intensity signal is transmitted to the post-stage through a C1, further amplified and then output to a CPU module through a pin 7 of a chip LM324 for AD conversion and digital signal operation processing. Meanwhile, a comparison signal (output from the end of the resistor R17) is output through the 8 pins of the chip, whether the intensity of the returned light intensity signal meets the requirement is judged, if the intensity cannot meet the requirement, an error message is given by the instrument, the instrument is prompted to measure again, and the measuring accuracy of the instrument is further ensured.
The optical fiber center skin contact electrode 10 and the four contact electrodes 20 on the optical fiber head protective cover 30 form four voltage comparator electrodes, and +5V direct current voltage is applied to the optical fiber center skin contact electrode 10. When the optical fiber center electrode and the four electrodes on the edge of the optical fiber head protective cover 30 are in good contact with the skin, the +5V voltage on the optical fiber center skin contact electrode 10 generates direct current signal partial voltage under the action of the contact resistance of the skin in the input ends of four voltage comparators, and compares the direct current signal partial voltage with the set threshold voltage, if the signal partial voltage exceeds the set threshold value, a low level is output in the comparators, if the contact electrodes 20 of the four optical fiber head protective covers 30 and the skin contact electrode 10 of the center optical fiber are in good contact, the four voltage comparators output a low level through the conversion of an OR gate circuit, and finally a low level is output at the output ends, if any one of the contact electrodes of the four optical fiber head protective covers 30 and the skin contact electrode 10 of the optical fiber center is not in good contact with the skin, a high level signal is output by a circuit, so that the CPU module judges the level of the output signal of the skin impedance detection module, whether the optical fiber head detected by the laser before measurement is in good contact with the skin and vertically placed on the surface of the skin can be judged, and the inaccurate measurement result and accidental injury caused by starting measurement when the optical fiber head is not placed correctly are avoided.
In conclusion, the invention omits a light filter required by the traditional jaundice detector, has no light attenuation caused by the light filter, has stable directivity and intensity because of the laser, is easier to control the light path, has less interference, and has better detection precision and repeatability. Meanwhile, the working voltage of the optical fiber assembly module is low, the light concentration is good, so that a high-voltage charging and discharging part of a traditional jaundice detecting instrument can be omitted, the laser luminous intensity is stable, uninterrupted or continuous monitoring can be carried out all the time, the charging process of a xenon lamp light source does not need to be waited, and the medical clinical use is greatly facilitated.
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 that fall within the spirit and principle of the present invention are intended to be included therein.
Claims (5)
1. A skin jaundice detector comprises a laser control output module, a laser output assembly, a skin reflection return light detection assembly, a skin impedance detection module, a CPU module and a display liquid crystal screen; the method is characterized in that:
one end of the laser control output module is connected with the laser output assembly, the other end of the laser control output module is connected with the CPU module, and the skin reflection return light detection assembly, the skin impedance detection module and the display liquid crystal screen are respectively connected with the CPU module; the laser output assembly is provided with an optical fiber head protective cover, four contact electrodes and a laser output optical fiber, the four contact electrodes are located on the optical fiber head protective cover, the laser output optical fiber is located at the center position, the laser output optical fiber is also provided with a skin contact electrode, and the electrode and the four contact electrodes on the protective cover form corresponding electric connection at the same time.
2. The icterus dermal detector of claim 1, wherein:
the laser output optical fibers comprise a green 532nm wavelength laser output optical fiber, a blue 450nm wavelength laser output optical fiber and a shared optical fiber head, and the laser output optical fibers and the shared optical fiber head are positioned on the optical fiber head protective cover.
3. The icterus dermal detector of claim 2, wherein:
but the optical fiber head protection casing elastic retraction is equipped with reference column and retraction spring on the optical fiber head protection casing, is equipped with skin contact electrode on the reference column, and skin contact electrode matches with four contact electrodes, and the retraction spring cover moves back and contact with the skin when pressing the optical fiber head that will detect on the reference column skin surface.
4. The icterus dermal detector of claim 3, wherein:
the green 532nm wavelength laser output optical fiber, the blue 450nm wavelength laser output optical fiber, the laser control output module, the skin reflected light detection assembly, the CPU module and the display liquid crystal screen are all arranged on the shell.
5. The icterus skin detector of claim 4, wherein:
the casing is internally provided with a detachable battery, and the end part of the casing is provided with a battery rear cover.
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| CN201911266978.1A CN111110234B (en) | 2019-12-11 | 2019-12-11 | Skin jaundice detector and detection method |
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| CN201911266978.1A CN111110234B (en) | 2019-12-11 | 2019-12-11 | Skin jaundice detector and detection method |
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