Transmitting light path of percutaneous jaundice instrument and percutaneous jaundice instrument

Abstract

The utility model provides a transmitting light path of a percutaneous jaundice instrument and the percutaneous jaundice instrument, and belongs to the technical field of medical instruments. The transmitting light path of the percutaneous jaundice instrument comprises an LED filament lamp used for transmitting light; the reflecting cover is arranged on one side of the LED filament lamp and used for receiving light rays emitted by the LED filament lamp and reflecting and concentrating the light rays; the conduction optical fiber bundle is arranged on the side, away from the reflecting cover, of the LED filament lamp and used for receiving and conducting the light rays reflected by the reflecting cover. According to the utility model, the service life of the percutaneous jaundice instrument is prolonged, and the cost of the percutaneous jaundice instrument is reduced.

Description

Technical Field

[0001] The utility model relates to the technical field of medical devices, in particular to a light emitting path of a transcutaneous jaundice meter and a transcutaneous jaundice meter. Background Art

[0002] Jaundice is a common clinical symptom in newborns, mainly caused by an increase in bilirubin levels. Bilirubin is a byproduct of the breakdown of red blood cells and is usually processed by the liver and excreted through bile. Newborns, due to immature liver function and weak bilirubin metabolism ability, are prone to accumulate bilirubin and form jaundice. If not treated in time, hyperbilirubinemia may lead to serious health problems, such as kernicterus, which affects the neurological development of newborns.

[0003] Traditional jaundice detection methods mainly rely on blood tests, that is, by collecting blood samples from newborns and measuring the bilirubin levels in the serum. However, this invasive detection method not only causes pain and discomfort to newborns, but also may increase the risk of infection, and frequent blood sampling places a burden on the physical health of newborns.

[0004] To reduce the harm to newborns, the medical community has developed transcutaneous jaundice meters, which are a non-invasive detection method. Existing transcutaneous jaundice meters use halogen lamps or xenon lamps as light sources, and estimate bilirubin concentration by measuring the absorption of light with a specific wavelength by the skin. However, these light sources have some limitations. For example, halogen lamps have a short lifespan and low luminous efficiency, while xenon lamps, although having a high luminous flux, have a discontinuous spectrum and high maintenance costs. Summary of the Utility Model

[0005] To overcome the problems existing in the related art, this specification provides a light emitting path of a transcutaneous jaundice meter and a transcutaneous jaundice meter, which helps to improve the service life of the transcutaneous jaundice meter and reduce the cost of the transcutaneous jaundice meter.

[0006] According to a first aspect of the present utility model, there is provided a light emitting path of a transcutaneous jaundice meter, comprising:

[0007] An LED filament lamp for emitting light;

[0008] A reflector disposed on one side of the LED filament lamp for receiving the light emitted by the LED filament lamp and reflecting and concentrating it;

[0009] A conductive optical fiber bundle disposed on the side of the LED filament lamp away from the reflector for receiving the light reflected by the reflector and conducting it.

[0010] In some exemplary embodiments of the present utility model, the LED filament lamp includes an LED filament, the LED filament is a slender columnar structure, and the side surface of the columnar structure is the light emitting surface of the LED filament.

[0011] In some exemplary embodiments of the present utility model, the reflective surface of the reflector is a curved surface.

[0012] In some exemplary embodiments of the present utility model, the conductive optical fiber bundle includes a plurality of conductive optical fibers, and the incident angle of the light reflected by the reflector entering the conductive optical fiber satisfies the following relational expression:

[0013] β ≤ α, where β represents the incident angle of the light reflected by the reflector cup entering the conductive optical fiber, and α represents the maximum value of the angle between the light that can enter the conductive optical fiber and the optical fiber axis of the conductive optical fiber.

[0014] In some exemplary embodiments of the present utility model,

[0015] NA = n × sinα, where NA represents the numerical aperture of the conductive optical fiber, and n represents the refractive index of the conductive optical fiber material.

[0016] In some exemplary embodiments of the present utility model, the conductive optical fiber bundle is further configured to receive the light emitted by the LED filament lamp and conduct it.

[0017] In some exemplary embodiments of the present utility model, at least half of the light-emitting surface of the LED filament lamp is wrapped in the space enclosed by the reflective surface of the reflector.

[0018] In some exemplary embodiments of the present utility model, the shape and size of the cross-section of the conductive optical fiber bundle match the shape and size of the light beam reflected by the reflector.

[0019] In some exemplary embodiments of the present utility model, the cross-section of the conductive optical fiber bundle is rectangular.

[0020] According to a second aspect of the present utility model, there is provided a transcutaneous jaundice meter, comprising:

[0021] The transcutaneous jaundice meter emission optical path as described in the first aspect;

[0022] A receiving optical path for receiving the light emitted by the transcutaneous jaundice meter emission optical path and conducting it;

[0023] A detection device for detecting the light conducted by the receiving optical path and detecting it.

[0024] The technical solution provided by the present utility model may include the following beneficial effects:

[0025] The emission optical path of the transcutaneous jaundice meter provided by the present utility model uses a high-efficiency LED filament lamp as the light source. Compared with traditional halogen lamps or xenon lamps, the light efficiency is significantly improved. At the same time, the long service life characteristic of the LED filament lamp reduces the light source replacement frequency, lowers the maintenance cost, and enhances the reliability of the device. In addition, the miniaturization characteristic of the LED filament lamp makes it easy to integrate this emission optical path with other components of the jaundice meter, contributing to a more compact device design.

[0026] Secondly, the cooperation of the LED filament lamp and the reflector hood in the present utility model eliminates the multi-lens system, making the jaundice meter more portable and easy to operate. Among them, the design of the reflector hood optimizes the light focusing, reflects and focuses the Lambertian light emitted by the LED filament lamp into a light spot of a certain shape, improves the light concentration, and helps to improve the accuracy of jaundice detection.

[0027] The transcutaneous jaundice meter provided by the present utility model has significant advantages in terms of performance, cost, safety, and operation convenience, meeting the requirements of medical devices for high efficiency, high accuracy, and low maintenance cost.

[0028] It should be understood that the above general description and the following detailed description are only exemplary and explanatory, and cannot limit this specification. Description of the Drawings

[0029] The drawings here are incorporated into the specification and constitute a part of this specification, showing the embodiments in line with this specification, and are used together with the specification to explain the principles of this specification.

[0030] Figure 1 It is a schematic structural diagram of the emission optical path of the transcutaneous jaundice meter in an exemplary embodiment of the present utility model;

[0031] Figure 2 It is a schematic diagram of the light path direction of the emission optical path of the transcutaneous jaundice meter in an exemplary embodiment of the present utility model;

[0032] Figure 3 It is a schematic cross-sectional diagram of the conductive optical fiber bundle in an exemplary embodiment of the present utility model.

[0033] Description of the Reference Numerals

[0034] 100 - LED filament lamp; 200 - reflector hood; 300 - conductive optical fiber bundle; 310 - conductive optical fiber. Detailed Embodiments

[0035] Example embodiments will now be described more fully with reference to the accompanying drawings. However, the example embodiments can be implemented in various forms and should not be construed as limited to the embodiments set forth herein; rather, these embodiments are provided so that this utility model will be thorough and complete, and will fully convey the concept of the example embodiments to those skilled in the art. Like reference numerals in the figures denote like or similar structures, and thus their detailed description will be omitted. In addition, the drawings are only schematic illustrations of the present utility model and are not necessarily drawn to scale.

[0036] Although relative terms such as "upper" and "lower" are used in this specification to describe the relative relationship of one component of an icon to another component, these terms are used in this specification only for convenience, for example, according to the directions of the examples described in the accompanying drawings. It can be understood that if the device of the icon is turned upside down, the component described as "upper" will become the component "lower". When a structure is "on" another structure, it may mean that a structure is integrally formed on another structure, or that a structure is "directly" disposed on another structure, or that a structure is "indirectly" disposed on another structure through another structure.

[0037] The terms "a", "an", "the", "said" and "at least one" are used to indicate the existence of one or more elements / components / etc.; the terms "comprising" and "having" are used to mean an open inclusion and mean that there may be additional elements / components / etc. in addition to the listed elements / components / etc.; the terms "first", "second", "third", etc. are used only as labels and are not a limitation on the quantity of their objects.

[0038] In the present utility model, terms such as "vertical" and "equal" refer to vertical and equal within the process error range, not vertical and equal in an absolute sense. The process error can be within ±10% or within ±5%. For example, if the first direction and the second direction are perpendicular, it can be understood that the included angle between the first direction and the second direction can be 90° ± 5°.

[0039] In the related art, a transcutaneous jaundice meter uses a halogen lamp or a xenon lamp as a light source, and its lifespan is generally too short. The halogen lamp itself has a low luminous flux. In addition, light distribution and coupling need to be performed through a lens, and the utilization of light efficiency will become very low during these processes. To solve the problem of low light efficiency, a higher-power halogen lamp is usually selected for replacement. However, a high-power light source will generate a higher temperature, which is also a huge test for the heat dissipation of the device itself; compared with the halogen lamp, the xenon lamp has a higher luminous flux and can better solve the problem of device heat dissipation. However, due to its unique light-emitting method (ionizing gas by high-voltage arc to generate arc light), its wavelength is not continuous, and the requirements for the hardware and software of sensing detection are relatively high, and repeated debugging is required.

[0040] Based on this, as Figures 1 to 3 shown, an emission optical path of a transcutaneous jaundice meter according to an embodiment of the present invention includes an LED (Light Emitting Diode) filament lamp 100, a reflector 200, and a conductive optical fiber bundle 300. Among them, the LED filament lamp 100 is used to emit light; the reflector 200 is disposed on one side of the LED filament lamp 100 for receiving the light emitted by the LED filament lamp 100 and reflecting and concentrating it; the conductive optical fiber 310 is disposed on the side of the LED filament lamp 100 away from the reflector 200 for receiving the light reflected by the reflector 200 and conducting it.

[0041] The emission optical path of the transcutaneous jaundice meter provided by the present invention uses a highly efficient LED filament lamp 100 as a light source. Compared with traditional halogen lamps or xenon lamps, the light efficiency is significantly improved. At the same time, the long-life characteristic of the LED filament lamp 100 reduces the light source replacement frequency, lowers the maintenance cost, and enhances the reliability of the device. In addition, the miniaturization characteristic of the LED filament lamp 100 makes the emission optical path easy to integrate with other components of the jaundice meter, contributing to a more compact device design.

[0042] Secondly, the cooperation between the LED filament lamp 100 and the reflector 200 in the present invention eliminates the multi-lens system, making the jaundice meter more portable and easy to operate. Among them, the design of the reflector 200 optimizes the light focusing, reflects and focuses the Lambertian light emitted by the LED filament lamp 100 into a light spot of a certain shape, improves the light concentration, and helps to improve the accuracy of jaundice detection.

[0043] The transcutaneous jaundice meter provided by the present invention has significant advantages in terms of performance, cost, safety, and operation convenience, meeting the requirements of medical devices for high efficiency, high accuracy, and low maintenance cost.

[0044] Next, each part of the emission optical path of the transcutaneous jaundice meter provided by the embodiments of the present invention will be described in detail with reference to the accompanying drawings:

[0045] As Figures 1 to 3 shown, for the emission optical path of the transcutaneous jaundice meter provided by the present invention, after a newborn is born, the emission optical path can be used for rapid and non-invasive jaundice detection, evaluating the bilirubin level, and completing the timely diagnosis and treatment of the newborn. The emission optical path of the transcutaneous jaundice meter includes an LED filament lamp 100, a reflector 200, and a conductive optical fiber bundle 300.

[0046] The LED filament lamp 100 serves as a light source for emitting light for detection. The LED filament lamp 100 includes an LED filament, which is a slender columnar structure. The side surface of this columnar structure is the light-emitting surface of the LED filament, and the two end faces do not emit light. One of the end faces is an electrode. The shape of the LED filament is similar to that of a traditional tungsten filament and can be bent into various shapes to meet different light-emitting requirements. An LED filament lamp 100 can contain multiple LED filaments and can form different shapes with these filaments. For example, the LED filament lamp 100 can be cylindrical, or spiral, an "X" shape formed by the intersection of two filaments, a pagoda shape formed by multiple filaments, etc. Among them, the spiral design can increase the light-emitting area to provide a more uniform light distribution; the "X" shape design can be used to form a light output in a specific direction and angle; the pagoda shape design can output light in multiple directions and can form a complex light path design. The present utility model does not make special limitations on the shape of the LED filament lamp 100, and can be specifically set according to the requirements of the actual transcutaneous jaundice meter.

[0047] The LED filament lamp 100 operates based on the principle of electroluminescence. When an electric current passes through a semiconductor material, the recombination of electrons and holes generates photons, thereby emitting light. The present utility model uses the LED filament lamp 100 as a light source, which has higher energy efficiency and a service life of up to tens of thousands of hours compared with traditional halogen lamps or xenon lamps. Among them, the high luminous efficiency characteristic of the LED filament lamp 100 enables it to consume less electric energy while providing sufficient brightness. Its spectrum is usually blue light exciting yellow fluorescent powder to generate light with a continuous spectrum. In particular, the blue light part around 470 nm has strong energy, which matches the absorption peak of bilirubin, and this is particularly important for the detection of jaundice. In addition, since the heat generated by the LED filament lamp 100 is relatively low, the heat dissipation design of the jaundice meter can be simplified, which helps to improve the stability and reliability of the device.

[0048] In addition, the present utility model uses the LED filament lamp 100 as a light source. Compared with using an LED light-emitting chip, the LED filament lamp 100 has better heat conduction performance, its heat dissipation design is relatively simpler, and the manufacturing cost is lower.

[0049] The reflector 200 is disposed on one side of the LED filament lamp 100 and is used to receive the light emitted by the LED filament lamp 100 and reflect and concentrate it. Specifically, when the light emitted by the LED filament lamp 100 shines on the reflector 200, these lights will be captured by the reflective surface of the reflector 200 and then reflected and concentrated along a specific direction. In this way, the reflector 200 not only collects the light emitted by the LED filament lamp 100, but also focuses the light into a light spot with a specific shape through the reflection of its reflective surface to meet the requirements of the jaundice meter. Compared with using an LED light-emitting chip as the light source, the present utility model uses the LED filament lamp 100 without the need to use a lens for light distribution, and only the reflector 200 is needed. This light distribution method is simpler and has a lower cost.

[0050] In some embodiments of the present utility model, the reflective surface of the reflector 200 is a curved surface. The specific shape of the curved surface can be set according to the shape of the light spot required after being reflected by the reflector 200. In a specific embodiment, the reflective surface of the reflector 200 is a parabolic surface. When the light emitted by the LED filament lamp 100 shines on the reflector 200, these lights will be captured by the reflection characteristics of the parabolic surface and then reflected and concentrated along the axis of symmetry of the parabola. In this way, the reflector 200 not only collects the light emitted by the LED filament lamp 100, but also focuses the light into an elliptical light spot through the reflection of its inner surface. In addition, the reflective surface of the reflector 200 can also be a hyperbolic surface or a free-form surface, and the present utility model does not make special limitations specifically.

[0051] Furthermore, to ensure the reflection effect of the reflector 200 on the LED filament lamp 100, at least half of the light-emitting surface of the LED filament lamp 100 is wrapped in the space surrounded by the reflective surface of the reflector 200. For example, the LED filament lamp 100 is cylindrical, and its side surface is the light-emitting surface. To ensure the reflection effect of the reflector 200 on it, at least half of the side surface of the LED filament lamp 100 should be wrapped in the space surrounded by the reflective surface of the reflector 200. In this way, it can be ensured that most of the light emitted by the LED filament lamp 100 is received and reflected by the reflector 200.

[0052] The conductive optical fiber bundle 300 is disposed on the side of the LED filament lamp 100 away from the reflector 200 and is used to receive the light reflected by the reflector 200 and conduct it. Specifically, the conductive optical fiber bundle 300 can accurately receive the light concentrated and reflected by the reflector 200 and effectively conduct it to the skin surface. Further, the conductive optical fiber bundle 300 is arranged on one side of the LED filament lamp 100, opposite to the reflector 200, to ensure that the incident surface of the conductive optical fiber bundle 300 can receive the light reflected by the reflector 200 to the greatest extent.

[0053] In some embodiments of the present utility model, the conductive optical fiber bundle 300 includes a plurality of conductive optical fibers 310. The shape and size of the cross-section of the conductive optical fiber bundle 300 match the shape and size of the cross-section of the light beam reflected by the reflector 200. For example, the cross-section of the conductive optical fiber bundle 300 is designed to be rectangular, which helps to maximize the reception of the light focused by the reflector 200. At the same time, the arrangement density of the optical fibers in the conductive optical fiber bundle 300 and the splicing process are also considered to ensure the uniformity and optical performance of the optical fiber bundle. It should be noted here that the present utility model does not make special limitations on the specific shape of the cross-section of the conductive optical fiber bundle 300, as long as it can match the shape and size of the cross-section of the light beam reflected by the reflector 200, and it can be oval, circular, square or other geometric shapes, etc.

[0054] Further, the incident angle of the light reflected by the reflector 200 entering the conductive optical fiber 310 satisfies the following relationship:

[0055] β ≤ α, where β represents the incident angle of the light reflected by the reflector cup entering the conductive optical fiber 310, and α represents the maximum value of the angle between the light that can enter the conductive optical fiber 310 and the optical fiber axis of the conductive optical fiber 310. That is, the incident angle β of all the light entering the optical fiber will not be greater than the critical angle α of the optical fiber. This ensures that the light can be effectively coupled into the interior of the conductive optical fiber 310 and thus transmitted to the other end of the conductive optical fiber 310 to improve the accuracy and efficiency of detection.

[0056] Further, NA = n × sinα, where NA represents the numerical aperture of the conductive optical fiber 310, and n represents the refractive index of the material of the conductive optical fiber 310. Specifically, by selecting the NA value of the conductive optical fiber 310, the reflective surface of the reflector 200 can be optimized designed so that more light reflected by the reflector 200 satisfies β ≤ α.

[0057] In practical applications, the material of the conductive optical fiber 310 needs to have good optical transparency and fracture resistance to ensure stable light transmission during use. The outer coating material of the conductive optical fiber 310 also needs to have certain heat resistance and chemical stability to adapt to various environmental conditions that the medical device may face.

[0058] In addition, the conductive optical fiber bundle 300 is also used to receive and conduct the light emitted by the LED filament lamp 100. Specifically, for the light emitted by the LED filament lamp 100, a part of the light is reflected towards the reflector 200. After reaching the reflector 200, it is transmitted to the conductive optical fiber bundle 300 after being reflected by the reflector 200. Another part of the light can be directly emitted towards the conductive optical fiber bundle 300 and directly enter the conductive optical fiber bundle 300, so as to ensure that the light emitted by the LED filament lamp 100 can enter the conductive optical fiber bundle 300 to the greatest extent, improving the light utilization rate and detection accuracy.

[0059] The present utility model also provides a transcutaneous jaundice meter, which includes the transcutaneous jaundice meter emission optical path, reception optical path and detection device in any of the above embodiments. Among them, the reception optical path is used to receive and conduct the light emitted by the transcutaneous jaundice meter emission optical path; the detection device is used to detect the light conducted by the reception optical path and perform detection on it. Specifically, the light emitted by the transcutaneous jaundice meter emission optical path can irradiate the skin surface, and after being reflected, scattered and refracted by the subcutaneous tissue, it is conducted to the reception optical path. The reception optical path may include conductive light, and the light is output to the detection device after being conducted by the conductive optical fiber. The detection device may include a microprocessor MCU that can analyze the blue light value to calculate the jaundice value content (currently, processors with eight or more bits on the market all have this data processing function, such as STC8H1K28, etc.). The microprocessor can analyze the blue light value, calculate the jaundice value content, and output the jaundice value data externally through the communication interface on the circuit board.

[0060] The transcutaneous jaundice meter provided by the present utility model realizes highly efficient and accurate jaundice detection through the design of the emission optical path. The LED filament lamp in the emission optical path serves as the light source. Due to its long lifespan and high luminous efficiency characteristics, it provides a stable and lasting light output for the jaundice meter. The design of the reflector cup enables the Lambertian light emitted by the LED filament lamp to be reflected and focused to form a light spot with a specific shape, which not only improves the light concentration but also optimizes the optical path structure and enhances the detection accuracy.

[0061] The reception optical path is responsible for receiving the light reflected back from the skin and conducting it to the detection device. This step is crucial for ensuring the quality and intensity of the detection signal. Through a suitable reception optical path, useful optical information can be captured maximally while reducing the influence of interference factors such as ambient light.

[0062] As the core part of the transcutaneous jaundice meter, the detection device is responsible for precisely detecting the light conducted by the reception optical path. It can convert the optical signal into an electrical signal and perform further analysis and processing. The high sensitivity and accuracy of the detection device are crucial for the performance of the transcutaneous jaundice meter. It can accurately measure the bilirubin level and provide a reliable diagnostic basis for doctors.

[0063] Other embodiments of the present utility model will be readily conceived by those skilled in the art upon consideration of the specification and practice of the utility model disclosed herein. This application is intended to cover any variations, uses, or adaptations of the present utility model, which follow the general principles of the present utility model and include known common general knowledge or conventional technical means in the technical field not disclosed by the present utility model. The specification and examples are only regarded as exemplary, and the true scope and spirit of the present utility model are pointed out by the appended claims.

Claims

1. A transcutaneous jaundice instrument emission light path, characterized in that: include: LED filament lamp, used to emit light; A reflector, disposed on one side of the LED filament lamp, for receiving the light emitted by the LED filament lamp and reflecting and concentrating it; The conducting optical fiber bundle is arranged on a side of the LED filament lamp away from the reflector, and is used for receiving and conducting the light reflected by the reflector.

2. The transmitting optical path of the transcutaneous jaundice instrument according to claim 1, characterized in that: The LED filament lamp comprises an LED filament, and the LED filament is an elongated columnar structure, and the side surface of the columnar structure is the light-emitting surface of the LED filament.

3. The transmitting optical path of the transcutaneous jaundice instrument according to claim 1, characterized in that: The reflective surface of the reflector is a curved surface.

4. The transmitting optical path of the transcutaneous jaundice instrument according to claim 1, characterized in that: The transmission optical fiber bundle includes a plurality of transmission optical fibers, and the incident angle of the light reflected by the reflector entering the transmission optical fiber satisfies the following relationship: β≤α, ​​wherein β represents the incident angle of the light reflected by the reflective cup entering the conductive optical fiber, and α represents the maximum value of the angle between the light and the optical fiber axis of the conductive optical fiber when the light can enter the conductive optical fiber.

5. The transmitting optical path of the transcutaneous jaundice instrument according to claim 4, characterized in that: NA=n×sinα, wherein NA represents the numerical aperture of the transmission optical fiber, and n represents the refractive index of the transmission optical fiber material.

6. The transmitting optical path of the transcutaneous jaundice instrument according to claim 1, characterized in that: The transmission optical fiber bundle is also used to receive and transmit the light emitted by the LED filament lamp.

7. The transmitting optical path of the transcutaneous jaundice instrument according to claim 1, characterized in that: At least half of the light-emitting surface of the LED filament lamp is enclosed in the space surrounded by the reflective surface of the reflector.

8. The emitting optical path of the transcutaneous jaundice instrument according to any one of claims 1 to 7, characterized in that: The shape and size of the cross section of the transmission optical fiber bundle matches the shape and size of the cross section of the light beam reflected by the reflector.

9. The transmitting optical path of the transcutaneous jaundice instrument according to claim 8, characterized in that: The cross section of the transmission optical fiber bundle is rectangular.

10. A transcutaneous jaundice instrument, characterized in that: include: The transmitting optical path of the transcutaneous jaundice instrument according to any one of claims 1 to 9; A receiving optical path, used for receiving and transmitting the light emitted by the transmitting optical path of the transcutaneous jaundice instrument; The detection device is used to detect the light transmitted by the receiving light path and perform detection on it.

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