Optical fiber recording and blood oxygen combined detection equipment

Abstract

The utility model provides optical fiber recording and blood oxygen combined detection equipment, which solves the problem that brain neuron activity reflected by data measured by a conventional fluorescence signal detection means cannot realize self-certification, and adopts the main scheme that the optical fiber recording and blood oxygen combined detection equipment comprises a first light source group and a second light source group which respectively comprise a plurality of LED (Light Emitting Diode) excitation light sources with different central wavelengths, the detector comprises a CMOS (Complementary Metal Oxide Semiconductor) sensor and a photomultiplier; the lens group comprises a dichroscope and an optical filter, each LED exciting light source optical fiber is input into a specific brain region of the experimental animal, and meanwhile, reflected fluorescence signals are screened according to wavelengths and guided into the detector; the light source driving circuit is electrically connected with the first light source group and the second light source group; the acquisition card is electrically connected with the detector so as to perform data interaction with external analysis software; and the control circuit is electrically connected with the acquisition card and the light source driving circuit.

Description

Technical Field

[0001] The utility model relates to the technical field of neuron detection in animal brains, in particular to an optical fiber recording and blood oxygen combined detection device. Background Art

[0002] Fiber optic recording, as a conventional means of recording fluorescent signals, has been increasingly widely used. However, since the data it measures reflects the activity of brain neurons, it is not self-evident, so it is necessary to conduct joint measurements with other devices to compare and verify the data. Blood oxygen concentration is an important indicator of human health. Traditional blood oxygen measurement equipment mainly uses pulse oximeters, which have the advantages of convenient measurement and low cost, but their measurement precision and accuracy are relatively low.

[0003] To this end, we propose a fiber optic recording and blood oxygen joint detection device to solve the above problems. Utility Model Content

[0004] The technical problem to be solved by the utility model is to overcome the defects of the existing technology. The utility model proposes xx, a fiber optic recording and blood oxygen joint detection device. The utility model uses three types of excitation light of 405nm / 470nm / 580nm to record the fluorescence signal variables of specific brain areas of experimental animals. At the same time, this optical fiber also transmits two wavelength light sources of 660nm and 810nm to measure the blood oxygen saturation of specific brain areas of experimental animals through reflected light intensity. The device can prove the changes in neurons in the brain areas of experimental animals from two dimensions: fluorescence signal changes and blood oxygen changes, and realize mutual verification of data.

[0005] In order to solve the above technical problems, the technical solution adopted by the utility model is: an optical fiber recording and blood oxygen joint detection device, comprising:

[0006] A first light source group and a second light source group respectively include a plurality of LED excitation light sources with different central wavelengths, wherein the first light source group is used to excite corresponding fluorescent signals of experimental animals, and the second light source group is used to reflect changes in blood oxygen concentration through reflected light intensity;

[0007] A detector, comprising a CMOS sensor corresponding to the first light source group and a photomultiplier tube corresponding to the second light source group;

[0008] The lens group includes a dichroic mirror and a filter. Each LED excitation light source in the first light source group is filtered by an independent filter and then refracted by the dichroic mirror and then input into a specific brain region of the experimental animal through an optical fiber. At the same time, the reflected fluorescence signal is screened by wavelength and introduced into the CMOS sensor. Each LED laser light source in the second light source group is refracted by the dichroic mirror and then input into a specific brain region of the experimental animal through an optical fiber. At the same time, the reflected fluorescence signal is screened by wavelength and then introduced into the photomultiplier tube.

[0009] A light source driving circuit electrically connected to the first light source group and the second light source group;

[0010] An acquisition card, electrically connected to the detector to interact with external analysis software data;

[0011] The control circuit is electrically connected to the acquisition card and the light source driving circuit. The control circuit uses time division multiplexing to control the on and off of multiple LED excitation light sources in the first light source group, and uses a ttl signal to control the on and off of multiple LED excitation light sources in the second light source group.

[0012] Furthermore, the central wavelengths of the LED excitation light sources in the first light source group are 405 nm, 470 nm, and 580 nm, respectively, and the central wavelengths of the LED excitation light sources in the second light source group are 660 nm and 810 nm, respectively.

[0013] Furthermore, the acquisition software model is QAXK-FPS-OST-ACQUISITION-SOFTWARE, which is used to calculate the image frame signal collected by the CMOS sensor through an algorithm to obtain the real-time change data of the fluorescence signal and display it in real time, and at the same time display the measured voltage data of the photomultiplier tube.

[0014] Furthermore, the analysis software model is QAXK-FPS-OST-ANALYSIS-SOFTWARE, which is used to normalize the real-time changing data of the fluorescence signal of the acquisition software and convert the voltage data of the photomultiplier tube into blood oxygen concentration data.

[0015] Furthermore, the light source driving circuit can receive an external square wave modulation signal to realize time-sharing output of five LED excitation light sources, among which three LED excitation light sources with central wavelengths of 405nm, 470nm, and 580nm are staggered in timing, and two LED excitation light sources with central wavelengths of 660nm and 810nm are staggered in timing.

[0016] Compared with the prior art, the beneficial effects of the utility model include:

[0017] 1. It can realize the simultaneous detection of fluorescence signals and blood oxygen concentration in a single brain area, and the changes of the two signals can be verified with each other;

[0018] 2. The blood oxygen concentration measurement accuracy of a single brain region is high. Through multi-fiber implantation, the fluorescence signal changes and blood oxygen concentration measurement of multiple brain regions can be realized;

[0019] 3. Low cost. Due to the use of advanced optical design and algorithm optimization, the production cost and maintenance cost of blood oxygen concentration can be reduced;

[0020] 4. Good real-time performance, enabling real-time imaging and rapid analysis. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] The disclosure of the present invention is described with reference to the accompanying drawings. It should be understood that the drawings are only for illustrative purposes and are not intended to limit the scope of protection of the present invention. In the accompanying drawings, the same reference numerals are used to refer to the same components. Among them:

[0022] Figure 1 A schematic diagram of implanting an optical fiber in the brain of an experimental animal according to one embodiment of the utility model is shown;

[0023] Figure 2 The schematic diagram shows the principle diagram of the optical path proposed according to one embodiment of the utility model;

[0024] Figure 3 Schematically shows a light source driving circuit diagram proposed according to an embodiment of the utility model;

[0025] Figure 4 The figure schematically shows a control circuit diagram proposed according to an embodiment of the present utility model. DETAILED DESCRIPTION

[0026] It is easy to understand that according to the technical solution of the utility model, without changing the essential spirit of the utility model, a person skilled in the art can propose a variety of interchangeable structural modes and implementation modes. Therefore, the following specific implementation modes and drawings are only exemplary descriptions of the technical solution of the utility model, and should not be regarded as the entirety of the utility model or as a limitation or restriction to the technical solution of the utility model.

[0027] According to one embodiment of the present invention, Figure 1-Figure 4 Shown.

[0028] An optical fiber recording and blood oxygen combined detection device, comprising:

[0029] A first light source group and a second light source group respectively include a plurality of LED excitation light sources with different central wavelengths, wherein the first light source group is used to excite corresponding fluorescent signals of experimental animals, and the second light source group is used to reflect changes in blood oxygen concentration through reflected light intensity;

[0030] A detector, comprising a CMOS sensor corresponding to the first light source group and a photomultiplier tube corresponding to the second light source group;

[0031] The lens group includes a dichroic mirror and a filter. Each LED excitation light source in the first light source group is filtered by an independent filter and then refracted by the dichroic mirror and then input into a specific brain region of the experimental animal through an optical fiber. At the same time, the reflected fluorescence signal is screened by wavelength and introduced into the CMOS sensor. Each LED laser light source in the second light source group is refracted by the dichroic mirror and then input into a specific brain region of the experimental animal through an optical fiber. At the same time, the reflected fluorescence signal is screened by wavelength and then introduced into the photomultiplier tube.

[0032] A light source driving circuit electrically connected to the first light source group and the second light source group;

[0033] An acquisition card, electrically connected to the detector to interact with external analysis software data;

[0034] The control circuit is electrically connected to the acquisition card and the light source driving circuit. The control circuit uses time division multiplexing to control the on and off of multiple LED excitation light sources in the first light source group, and uses a ttl signal to control the on and off of multiple LED excitation light sources in the second light source group.

[0035] Specifically, in this embodiment, if Figure 2 As shown, the central wavelengths of the LED excitation light sources in the first light source group are 405nm, 470nm, and 580nm, respectively, and the central wavelengths of the LED excitation light sources in the second light source group are 660nm and 810nm, respectively. The light source driving circuit can receive an external square wave modulation signal to achieve time-sharing output of five kinds of LED excitation light sources, wherein the three kinds of LED excitation light sources with central wavelengths of 405nm, 470nm, and 580nm are staggered in time sequence, and the two kinds of LED excitation light sources with central wavelengths of 660nm and 810nm are staggered in time sequence.

[0036] Five different wavelengths of excitation light sources are integrated into the detection device, of which 405nm / 470nm / 580nm are used to record the changes in fluorescence signals, which are used to excite green fluorescence and red fluorescence in the experimental animals to reflect the activity of neurons in the brains of the experimental animals; the 660nm and 810nm light sources are used to calculate the changes in blood oxygen in the same brain region of the experimental animals through reflected light intensity. The acquisition card can simultaneously output control signals of the 660nm and 810nm excitation lights, and use this control signal as a synchronization signal for the output of the photomultiplier tube signal, thereby obtaining the light intensity reflected by the 660nm and 810nm light sources.

[0037] Figure 2 The optical path design introduces five types of excitation lights into a specific brain area of ​​the experimental animal through an optical fiber. The optical fiber simultaneously transmits the reflected green fluorescence and red fluorescence signals to the detector of the device host to reflect the real-time changes in fluorescence. The reflected light intensity of two of the excitation lights is measured by another optical fiber implanted at 60 degrees to achieve the measurement of blood oxygen concentration based on the derived blood oxygen calculation formula.

[0038] Similarly, for the specific implementation of each circuit, the specific circuit structures of the light source driving circuit and the control circuit are as follows: Figure 3 and Figure 4 As shown, Figure 3 LED B is one of the five wavelength LED excitation light sources mentioned above. The remaining four LED laser source excitation drive circuit structures are the same and will not be repeated. For the on and off control of multiple LED excitation light sources, the connection relationship of each pin of the corresponding relay has been Figure 4 It is clearly shown in the figure and will not be repeated here.

[0039] Furthermore, the device is equipped with acquisition and analysis software that can collect and analyze fluorescence signals and blood oxygen concentration data in real time.

[0040] The acquisition software model is QAXK-FPS-OST-ACQUISITION-SOFTWARE, which is used to calculate the image frame signal collected by the CMOS sensor through an algorithm to obtain the real-time change data of the fluorescence signal and display it in real time, and at the same time display the measured voltage data of the photomultiplier tube.

[0041] The analysis software model is QAXK-FPS-OST-ANALYSIS-SOFTWARE, which is used to normalize the real-time changes in the fluorescence signal of the acquisition software and convert the voltage data of the photomultiplier tube into blood oxygen concentration data. The utility model uses three types of excitation light, 405nm / 470nm / 580nm, to record the fluorescence signal variables of specific brain areas of experimental animals. At the same time, this optical fiber also transmits two wavelength light sources of 660nm and 810nm to measure the blood oxygen saturation of specific brain areas of experimental animals through reflected light intensity. The device can prove the changes in neurons in the brain areas of experimental animals from two dimensions: fluorescence signal changes and blood oxygen changes, and realize mutual verification of data.

[0042] The technical scope of the present invention is not limited to the contents described above. Those skilled in the art can make various deformations and modifications to the above embodiments without departing from the technical concept of the present invention, and these deformations and modifications should all fall within the protection scope of the present invention.

Claims

1. An optical fiber recording and blood oxygen joint detection device, characterized in that: include: A first light source group and a second light source group respectively include a plurality of LED excitation light sources with different central wavelengths, wherein the first light source group is used to excite corresponding fluorescent signals of experimental animals, and the second light source group is used to reflect changes in blood oxygen concentration through reflected light intensity; A detector, comprising a CMOS sensor corresponding to the first light source group and a photomultiplier tube corresponding to the second light source group; The lens group includes a dichroic mirror and a filter. Each LED excitation light source in the first light source group is filtered by an independent filter and then refracted by the dichroic mirror and then input into a specific brain area of ​​the experimental animal through an optical fiber. At the same time, the reflected fluorescence signal is screened according to the wavelength and introduced into the CMOS sensor. Each LED laser light source in the second light source group is refracted by the dichroic mirror and then input into a specific brain area of ​​the experimental animal through an optical fiber. At the same time, the reflected fluorescence signal is screened according to the wavelength and then introduced into the photomultiplier tube. A light source driving circuit electrically connected to the first light source group and the second light source group; An acquisition card, electrically connected to the detector to interact with external acquisition software data; The control circuit is electrically connected to the acquisition card and the light source driving circuit. The control circuit uses time division multiplexing to control the on and off of multiple LED excitation light sources in the first light source group, and uses a ttl signal to control the on and off of multiple LED excitation light sources in the second light source group.

2. The optical fiber recording and blood oxygen combined detection device according to claim 1, characterized in that: The central wavelengths of the LED excitation light sources in the first light source group are 405 nm, 470 nm, and 580 nm, respectively; the central wavelengths of the LED excitation light sources in the second light source group are 660 nm and 810 nm, respectively.

3. The optical fiber recording and blood oxygen combined detection device according to claim 1, characterized in that: The acquisition software model is QAXK-FPS-OST-ACQUISITION-SOFTWARE, which is used to calculate the image frame signal collected by the CMOS sensor through an algorithm to obtain the real-time change data of the fluorescence signal and display it in real time, and at the same time display the measured voltage data of the photomultiplier tube.

4. The optical fiber recording and blood oxygen combined detection device according to claim 3, characterized in that: The analysis software model is QAXK-FPS-OST-ANALYSIS-SOFTWARE, which is used to normalize the real-time changing data of the fluorescence signal of the acquisition software and convert the voltage data of the photomultiplier tube into blood oxygen concentration data.

5. The optical fiber recording and blood oxygen combined detection device according to claim 2, characterized in that: The light source driving circuit can receive an external square wave modulation signal to realize time-sharing output of five LED excitation light sources, among which three LED excitation light sources with central wavelengths of 405nm, 470nm and 580nm are staggered in timing, and two LED excitation light sources with central wavelengths of 660nm and 810nm are staggered in timing.

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