Light source output apparatus and control method for laparoscopic surgery structure recognition

Abstract

The present application relates to a kind of light source output device and control method for laparoscopic surgery structure identification, it includes box;The outside of box is provided with optical fiber interface;The inside of box is provided with main optical fiber, several branch optical fibers and white light LED light-emitting diode, purple light LED light-emitting diode, blue light LED light-emitting diode and green light LED light-emitting diode;Wherein, the light-emitting side of white light LED light-emitting diode, purple light LED light-emitting diode, blue light LED light-emitting diode and green light LED light-emitting diode is respectively close to and corresponds to the light input end of each branch optical fiber;The light output end of each branch optical fiber is coupled to the light input end of main optical fiber, and the light output end of main optical fiber is connected to the optical fiber interface.The present application can be according to the need of distinguishing different tissue structures in operation, conveniently switch the illumination light of different spectral characteristics output, to solve the technical problems that existing laparoscope light source function is single, cannot assist accurate identification specific anatomical structure.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a light source output device and control method for laparoscopic surgical structure identification. Background Technology

[0002] Minimally invasive surgical techniques, especially endoscopic surgery represented by laparoscopic surgery, have become standard procedures in many fields of modern surgery. These surgeries involve making several small incisions in the abdominal wall to insert a laparoscope and specialized surgical instruments into the abdominal cavity. The surgeon then performs complex surgical procedures by observing real-time images transmitted from the laparoscopic system on a monitor. This technology effectively reduces postoperative pain, shortens the recovery period, and improves aesthetic results. In the entire laparoscopic surgical system, high-quality real-time imaging is fundamental to successful surgery, and clear images highly depend on a stable and sufficient lighting system—the laparoscopic light source. Traditional laparoscopic light source systems, whether early xenon lamps or current mainstream high-power LED light sources, are primarily designed to provide high-intensity, continuous-spectrum "white light" illumination. This white light illumination can maximally reproduce the natural colors of internal organs and tissues, providing the surgeon with a realistic surgical field environment that matches their experience in open surgery. This is necessary and fundamental for routine anatomical structure identification and surgical procedures.

[0003] However, with the advancement of laparoscopic techniques and the increasing precision of surgical procedures, simple white light illumination has begun to reveal its inherent limitations. In many critical surgical steps, surgeons need to distinguish not only different organs, but also more intricate anatomical structures, such as the thin fascia layer, tiny blood vessels hidden deep within adipose tissue, and lymph nodes that are similar in color to the surrounding tissue. Under full-spectrum white light, these structures show little difference in reflectance spectrum from the surrounding background tissue, resulting in low visual contrast, blurred boundaries, and difficulty in accurate and rapid identification. Therefore, surgeons rely heavily on their personal anatomical knowledge, tactile feedback, and accumulated surgical experience when performing layer separation, vascular manipulation, or lymph node dissection. This subjective experience-dependent approach not only increases the learning curve for young surgeons, but even for experienced specialists, there is a risk of misjudgment when faced with anatomical variations or complex pathological conditions. Entering the wrong anatomical layer can lead to unnecessary bleeding, unclear vascular identification can cause serious complications such as massive intraoperative hemorrhage, and incomplete lymph node dissection directly affects the long-term survival rate of cancer patients.

[0004] To overcome the shortcomings of white light illumination, several technological explorations have been undertaken. One common technique is fluorescence imaging, such as using indocyanine green (ICG) as a contrast agent. Under specific near-infrared light excitation, its visualization in the biliary tract, blood vessels, or lymphatic system is observed through a specialized imaging system. This technique has achieved good results in specific areas (such as liver resection and lymphatic tracing), but its drawbacks are also significant: it requires the injection of exogenous contrast agents into the patient, posing a risk of allergic reactions; it requires expensive dedicated excitation light sources and imaging systems; and its application scenarios are relatively limited, failing to meet the general identification needs of various anatomical structures during surgery. Another technique is narrow-band imaging (NBI), which filters out the red light component from white light, using blue and green light to highlight the morphology of superficial and deep mucosal vessels. It is mainly used in the field of gastrointestinal endoscopy to detect early-stage cancer. However, the spectral selection and imaging algorithms of NBI technology are mainly aimed at mucosal lesions. For the common needs in laparoscopic surgery, such as the identification of mesangial layers, deep blood vessels and lymph nodes, its optimization effect is not ideal. Moreover, it also needs to be integrated into specific high-end endoscopic systems and is difficult to use as a supplement to general light sources.

[0005] Therefore, there is an urgent clinical need for a new type of light source device that can retain all the functions of traditional white light illumination, and provide corresponding optimized wavelengths of light according to the specific needs of identifying different types of anatomical structures (such as membranous layers, blood vessels, and lymph nodes) during the surgical process, thereby solving the surgical safety and quality problems caused by insufficient tissue identification in existing technologies. Summary of the Invention

[0006] To address the problems of existing technologies as much as possible, this invention provides a light source output device and control method for laparoscopic surgical structure identification. It can conveniently switch the output of illumination light with different spectral characteristics according to the needs of identifying different tissue structures during surgery, thereby solving the technical problem that existing laparoscopic light sources have limited functions and cannot assist in the accurate identification of specific anatomical structures.

[0007] This invention discloses a light source output device for laparoscopic surgical structure identification, characterized in that it includes a housing; the outer side of the housing is provided with an optical fiber interface for external connection to the laparoscopic light source interface; the interior of the housing is provided with a main optical fiber, several branch optical fibers, and at least white LEDs, purple LEDs, blue LEDs, and green LEDs; wherein the light-emitting sides of the white LEDs, purple LEDs, blue LEDs, and green LEDs are respectively close to and correspond to the light input ends of each branch optical fiber; the light output ends of each branch optical fiber are jointly coupled to the light input end of the main optical fiber, and the light output end of the main optical fiber is connected to the optical fiber interface.

[0008] Specifically, the structural design of this invention includes a housing that serves as the overall structural foundation and carrier of internal components. To facilitate connection with external medical equipment, a standardized fiber optic interface is provided on the outside of the housing. This interface interfaces with the light source transmission fiber optic cable of the laparoscopic system, thereby transmitting the light generated inside the device to the surgical area. Inside the housing, a light source generation and transmission system is configured. This system includes various functional light sources and fiber optic components for collecting and transmitting light. Specifically, the light source section includes at least four different types of light-emitting units: white LEDs, purple LEDs, blue LEDs, and green LEDs. These together form the light source matrix of the device, capable of emitting conventional illumination and diagnostic illumination light of specific wavelengths as needed. The fiber optic components adopt a "multiple-input, one-output" converging structure, consisting of several branch fibers and a main fiber. Furthermore, the four different LEDs (white, purple, blue, green, and green) are physically arranged in close alignment with their corresponding branch fibers, with the emitting side of each LED precisely aligned with and close to the light input end of an independent branch fiber. This one-to-one configuration ensures that the light emitted from each specific LED is efficiently and without crosstalk collected into its respective fiber optic channel. Subsequently, the optical outputs of all branch fibers converge and are connected to the optical input of the main fiber via optical coupling. This structure is typically implemented using a fiber optic combiner, which combines optical signals from multiple independent channels into a single output channel. Finally, the optical output of the main fiber is connected to an external fiber optic interface. Therefore, during actual operation, the control system can selectively activate a specific LED based on the real-time needs of the surgery. For example, when a violet LED is lit, the specific wavelength of violet light emitted will be transmitted through its corresponding branch fiber, then enter the main fiber through the fiber optic combiner structure, and finally output to the laparoscope from the fiber optic interface. Similarly, the surgeon can switch to white, blue, or green light illumination as needed, while all different types of light are output through the same main fiber and the same fiber optic interface, achieving a combination of diverse light source functions and a unified output path.

[0009] As a preferred embodiment of the present invention, the purple LED has an emission wavelength of 385 nm; the blue LED has an emission wavelength of 460 nm; and the green LED has an emission wavelength of 500 nm. Specifically, the essence of this technical solution lies in the fact that instead of using a broad purple, blue, or green spectrum, it selects a narrow wavelength that has been proven in practice to produce a specific optical response with specific human tissues. The technical logic is that different types of biological tissues, such as tissue membranes, vascular structures, and lymph node structures, exhibit unique absorption, reflection, or scattering characteristics to specific wavelengths of light due to differences in their composition and microstructure. By precisely controlling the wavelength of the light source to 385 nm, 460 nm, and 500 nm, the differences in optical properties between these specific tissues and the surrounding background tissue can be maximized respectively. For example, 385nm violet light can be differentially absorbed or reflected by tissue membrane structures, thus enhancing the contours of membrane layers during imaging; 460nm blue light is strongly absorbed by hemoglobin in the blood, making blood vessels appear significantly different in contrast to surrounding tissues in the image; and 500nm green light has been shown to help highlight the boundaries and morphology of lymph nodes. Therefore, when surgeons switch to the appropriate wavelength of light source according to the needs of the surgery, the visual contrast of the target anatomical structures in the observed laparoscopic images is significantly enhanced. This makes the structural boundaries that are difficult to distinguish under white light clearly discernible, directly reducing the risk of misjudging anatomical layers, blood vessels, and lymph nodes during surgery; on the other hand, it also improves the precision of surgical procedures (such as tissue separation, vascular manipulation, and lymph node dissection), thereby ensuring surgical safety while helping to improve the thoroughness of surgeries such as radical tumor resection.

[0010] As a specific embodiment of the present invention, an optical fiber combiner is installed inside the housing; the optical output ends of each of the branch optical fibers are coupled together to the optical input end of the main optical fiber through the optical fiber combiner. Specifically, this technical solution solves the technical problem of efficiently and stably integrating optical signals from multiple independent light sources (white, violet, blue, and green LEDs) into a single output channel using a standardized optical device specifically designed for optical path combining (i.e., an optical fiber combiner). The optical fiber combiner is existing technology; its internal structure is precisely designed to accurately align and couple the cores of multiple input optical fibers to the core of the output optical fiber. Compared to simple physical bundling, this method significantly reduces coupling loss and mode mismatch during the convergence process. Thus, regardless of which LED is currently in use, its emitted light can be transmitted efficiently from the corresponding branch optical fiber to the main optical fiber and finally output through the optical fiber interface. The technical advantage of this solution is that it ensures high light energy utilization and stable output optical power for the entire light source system. Highly efficient energy transfer means that, with the same LED driving power, the surgical field can achieve greater illumination brightness, which is crucial for observing deep or complex anatomical structures. Simultaneously, stable output ensures minimal fluctuations in illumination intensity when switching between different color light sources, providing surgeons with a continuous and reliable visual environment, thereby ensuring the effective and stable implementation of wavelength-based enhanced tissue recognition.

[0011] As a preferred embodiment of the present invention, the fiber optic combiner operates in the wavelength range of 380nm-510nm to accommodate the wavelength transmission requirements of 385nm, 460nm, 500nm, and white light. Specifically, this solution ensures that the optical performance of the fiber optic combiner, as a core optical path element, can fully cover and adapt to all specific wavelength light sources used in the device. The performance parameters of optical elements, such as transmittance and coupling efficiency, are typically wavelength-dependent. If the operating wavelength range of the selected combiner does not match the wavelength of the light source, it may lead to significant light energy attenuation or performance degradation at certain specific wavelengths (e.g., 385nm violet light). This solution sets the operating wavelength range of the combiner to 380nm-510nm, which fully encompasses the main visible light components of 385nm (violet light), 460nm (blue light), 500nm (green light), and white LEDs. This means that the combiner can maintain its designed high coupling efficiency and low insertion loss at all wavelengths within this range. Therefore, the technical effect of this solution is to ensure the performance consistency and reliability of the entire light source output device under different color illumination modes. Whether using violet, blue, or green light, the light signal can pass through the combiner efficiently and without discrimination, avoiding the problem of weakened illumination effect of a specific color due to component performance mismatch. This ensures the stable operation of each special structure recognition function, enhancing the overall performance of the device and the reliability of clinical applications.

[0012] In a preferred embodiment of the present invention, the main optical fiber and each branch optical fiber are all multimode optical fibers with an operating wavelength range of 350nm to 600nm to meet the high-efficiency transmission requirements of 385nm, 460nm, 500nm, and white light. It is understood that the main optical fiber and each branch optical fiber are multimode optical fibers because multimode optical fibers have a larger core diameter, enabling efficient coupling with incoherent light sources such as LEDs, and are easy to connect and operate. Limiting the operating wavelength range to 350nm to 600nm ensures that the fiber material itself has low transmission loss (i.e., low attenuation) within this spectral range. This wavelength range also completely covers the emission wavelengths of all light sources in the device (385nm violet light, 460nm blue light, 500nm green light, and white light). This means that when light of these specific wavelengths is transmitted inside the optical fiber, the energy loss due to material absorption and scattering is very small. This ensures that the light energy coupled from the LED light source into the optical fiber can be transmitted to the end of the fiber to the maximum extent. The technical advantage of this solution lies in ensuring the efficiency of the optical transmission process by selecting high-performance optical fibers that match the wavelength of the light source. This not only complements the aforementioned fiber combiner, jointly improving the overall system's optical output efficiency and providing sufficient illumination for surgery, but also ensures that different colored light signals maintain sufficient intensity after long-distance transmission. This prevents the function of enhancing tissue contrast based on specific wavelengths from being affected by excessive attenuation of the light signal during transmission, thus guaranteeing the clarity and contrast of the final image.

[0013] In a preferred embodiment of the present invention, the core diameter of the main optical fiber and each branch optical fiber is 50μm-200μm; and the numerical aperture (NA) of the main optical fiber and each branch optical fiber is ≥0.22. It can be understood that the core diameter is one of the key parameters determining the optical fiber's ability to contain and transmit light energy. The range of 50μm to 200μm falls within the specifications of standard multimode optical fibers. This size ensures a sufficiently large light-receiving area for easy alignment and coupling with the LED light source, while also maintaining the flexibility of the optical fiber. The numerical aperture (NA) defines the maximum angle at which an optical fiber can receive light; the larger the NA value, the stronger the light-receiving capability of the fiber. NA ≥ 0.22 means that the optical fiber has a relatively large light-receiving cone angle. The light emitted by an LED has a certain divergence angle. Using an optical fiber with a larger numerical aperture can more effectively capture the divergent light emitted by the LED and guide it into the fiber core for total internal reflection transmission. Therefore, the direct purpose of combining and limiting these two parameters, core diameter and numerical aperture, is to maximize the initial coupling efficiency of light from the LED light source to the branch optical fibers. The technical objective of this solution is to improve the utilization rate of the light source. By ensuring that more photons enter the fiber optic system from the LED, the device can produce stronger light output with the same power consumption. This directly translates to brighter illumination in the surgical field, helping surgeons to observe clearer anatomical details. This provides better support for achieving high-quality imaging for identifying special tissue structures, especially in scenarios requiring precise identification of minute structures.

[0014] As a further embodiment of the present invention, a fixed bracket is fixedly provided inside the housing; the white LED, purple LED, blue LED and green LED are all mounted on the fixed bracket.

[0015] As a further aspect of the present invention, a control circuit board is provided inside the housing, and the control circuit board is electrically connected to the white LED, purple LED, blue LED, and green LED respectively; a control panel electrically connected to the control circuit board is provided on the outside of the housing, so as to control the white LED, purple LED, blue LED, and green LED through the control panel; a switching circuit module electrically connected to the control circuit board is provided inside the housing; and a power switch electrically connected to the switching circuit module is provided on the outside of the housing.

[0016] In a preferred embodiment of the present invention, a plurality of glass sleeves are fixedly disposed within the housing; each glass sleeve is respectively disposed between a white LED and a branch optical fiber, a purple LED and a branch optical fiber, a blue LED and a branch optical fiber, and a green LED and a branch optical fiber; and the optical input end of each branch optical fiber and the light-emitting side of the white, purple, blue, and green LEDs are respectively fitted into the corresponding glass sleeve port, so that the optical input end of each branch optical fiber and the light-emitting side of the white, purple, blue, and green LEDs correspond to each other within each glass sleeve. Specifically, in this embodiment, each glass sleeve is respectively fitted between the light-emitting side of an LED and the optical input end of a branch optical fiber, so that the end faces of the LED and the optical fiber are aligned with each other inside the sleeve. The inner diameter of the glass sleeve forms a tight fit with the outer diameter of the LED package and the outer diameter of the optical fiber ferrule. Once the LED and optical fiber are inserted from their respective ends into the sleeve, the inner wall of the sleeve acts as a precise guide and limiter, automatically aligning their central axes to near coincidence. Compared to positioning solely with a bracket, this mechanical constraint achieves higher precision and more stable coaxial alignment. The technical advantage of this solution lies in improving the coupling efficiency and connection reliability between the light source and the optical fiber. High-precision alignment ensures that the maximum amount of light can enter the optical fiber from the LED, further enhancing the optical output power. Simultaneously, the glass sleeve provides physical protection for the optical fiber end face, preventing damage during assembly or vibration. Furthermore, and more importantly, the glass sleeve is made of glass, preferably quartz glass, for several reasons: First, glass, as an excellent optical medium, possesses high transmittance and low absorption loss over a wide spectral range (especially covering the entire visible light band from 385nm involved in this solution). This ensures that even with minute gaps during LED-optical fiber coupling, signal loss is minimized, thus guaranteeing efficient light transmission. Secondly, the light source in this scheme includes violet light with a wavelength of 385nm, which falls within the near-ultraviolet (UV-A) spectral region. Many conventional polymer materials (such as ordinary plastics) are prone to aging, yellowing, or deterioration of physical properties after prolonged exposure to ultraviolet light, leading to reduced light transmittance and consequently affecting the performance of specific optical paths. Glass materials, especially quartz glass or specific optical glasses, possess better resistance to ultraviolet radiation and chemical stability, enabling them to maintain their optical performance and structural integrity over a long period without deterioration due to continuous exposure to 385nm violet light.Furthermore, LEDs generate heat during operation. Glass materials possess excellent thermal stability and a low coefficient of thermal expansion, ensuring that the size and shape of the sleeve remain stable despite changes in the device's operating temperature. This maintains a precise and constant alignment between the LED and the optical fiber. Therefore, choosing a glass sleeve is not only to provide a simple mechanical alignment and protective structure, but also to ensure the optical performance, long-term reliability, and tolerance to specific wavelengths (ultraviolet light) of the entire coupling interface.

[0017] This invention also discloses a light source output device and control method for laparoscopic surgical structure identification. The light source output device of this invention includes the following steps:

[0018] Step S1, User Instruction Parsing Step: The timing characteristics of user input instructions from the control panel are monitored and parsed in real time through the control circuit board; Specifically, when the timing feature is a short press operation, switching is performed between multiple preset lighting modes; when the timing feature is a long press operation, the dynamic spectral scanning step S2 is initiated. S2, Dynamic Spectral Scanning Step: During the long press operation, the control board performs the following coordinated control: (a) Control the white LED (104) to output illumination of a reference intensity; (b) Over a reference intensity of illumination, the light intensity of at least one of the said violet LED light-emitting diodes (105), blue LED light-emitting diodes (106) or green LED light-emitting diodes (107) is periodically and smoothly modulated to form a continuously varying spectral output; S3, Custom Spectrum Locking Step: The control board responds to a lock command triggered upon the end of a long press operation by performing the following actions: (c) Record the instantaneous light intensity values ​​of the white, purple, blue, and green LEDs at the moment the locking command is received; (d) Control the white, purple, blue and green LEDs to emit light in a stable and continuous manner according to the recorded instantaneous light intensity values, so as to output a user-defined mixed spectrum.

[0019] Specifically, regarding step S1 (user command parsing step), this step aims to establish a set of user interaction rules based on input timing, replacing the simple mapping of "one button, one function" in traditional devices. By monitoring the duration of a user's operation on a button on the control panel, the MCU on the control board can easily distinguish between two distinct user intentions. Short presses are parsed as regular commands that cycle through preset lighting modes, ensuring the ease of use of basic functions. Long presses, on the other hand, are parsed as special commands intended to access advanced custom functions, namely, initiating "dynamic spectral scanning," providing the user with an entry point to advanced function modes.

[0020] Secondly, regarding step S2 (dynamic spectral scanning step), this step primarily implements the human-computer interaction process, and its key lies in the collaborative and superimposed working mode of multiple LED light sources. Specifically, upon receiving a long-press command, the MCU on the control circuit board does not turn off the white LED and then turn on other colored LEDs. Instead, it first drives the white LED to provide a stable basic illumination. This basic illumination ensures that the surgical field always has basic clarity and background reference. Based on this, the MCU on the control circuit board then periodically and gradually changes the output intensity of one or more other colored LEDs (such as violet, blue, and green light) according to a preset program. This intensity change is smooth, not abrupt. As a result, what is presented on the surgical monitor is not an abrupt switching of color modes, but a continuous and gentle evolution of light hues while maintaining the basic background information.

[0021] Finally, regarding step S3 (custom spectral locking step), this step aims to achieve personalized lighting. When the user, during dynamic spectral scanning, visually determines a spectral effect that best highlights the current target anatomical structure, the immediate release of the long-press button is interpreted as a "lock" command by the MCU on the control circuit board. In response to this command, the MCU on the control circuit board immediately performs two actions: First, it samples and records the output intensity parameters of all LED channels (including white light and other colored light) at the moment the command is triggered; second, it stops the dynamic scan and switches to a static working mode, continuously and stably driving multiple LEDs to emit light simultaneously according to the previously recorded multi-channel intensity parameters. Thus, a unique mixed-spectrum lighting pattern, "tuned" by the user based on the real-time surgical field of view, is generated and stably output.

[0022] The technical advantages of the aforementioned control method are as follows: First, this method achieves personalized lighting optimization based on real-time intraoperative visual feedback through dynamic spectral scanning and instant locking mechanisms. Given the differences in tissue optical properties among individuals and under different pathological conditions, fixed preset modes are difficult to achieve universally optimal results. This method allows surgeons to intuitively select and fix a custom spectral ratio that maximizes the contrast of the target structure within a continuously changing spectral range, thereby improving the accuracy of identifying specific anatomical structures. Second, this method employs a collaborative working mode of "white light reference illumination + colored light overlay," ensuring that while enhancing target structures (such as blood vessels and fascia), the background environment information of the surgical field is preserved. This hybrid spectral output avoids the background distortion and loss of spatial positioning caused by single-color light illumination, ensuring the surgeon's operational safety in complex anatomical environments. Finally, this method integrates advanced customization functions into an intuitive and coherent "long press-observe-release" operation, optimizing the human-computer interaction process. The surgeon can make precise adjustments to the light source without taking their attention away from the surgical monitor, reducing cognitive load and operational interruptions, and improving the smoothness and efficiency of the entire surgical workflow.

[0023] The technical effects of the light source output device for laparoscopic surgical structure identification proposed in this invention are as follows: First, current laparoscopic surgery mainly relies on white light sources that provide full-spectrum illumination. While this light source can reproduce the true colors of tissues, its ability to distinguish tissue structures with similar colors and textures but completely different anatomical significance is limited. For example, the contrast between membranous tissue layers, blood vessels, and lymph nodes and surrounding fat and connective tissue is low under white light, making identification difficult and entirely dependent on the surgeon's experience. This directly leads to an increase in surgical risks and uncertainties. The technical solution of this application deploys white LEDs and three narrow-band specific wavelength light sources—violet LEDs, blue LEDs, and green LEDs—within a single device for specifically displaying membranous tissue layers, vascular structures, and lymph node structures, respectively. When fine-grained layered dissection is required during surgery, the surgeon can switch to the violet LED output mode. Utilizing the difference in reflectivity between the membranous tissue layer and surrounding tissues after illumination with this specific wavelength of light, the originally blurred anatomical gaps present higher contrast on the monitor, thus being clearly identified. Similarly, when it's necessary to identify blood vessels to avoid damage or for treatment, switching to blue LED output utilizes the absorption characteristics of hemoglobin in the blood for specific blue light wavelengths, making the vascular structure more prominent. During critical lymph node dissection in radical tumor resection, switching to green LED output helps enhance the distinction between lymph nodes and surrounding adipose tissue. All these specific light source switching is controlled by internal circuitry, with the light ultimately output through a unified main fiber and fiber optic interface. This means the surgeon can seamlessly and instantly switch between conventional white light views and various augmented reality views during surgery. Therefore, this device transforms the light source from a simple illumination tool into an active anatomical navigation tool. By enhancing the visualization of specific anatomical structures, it directly reduces the risk of misjudgment and accidental injury during surgery, improving the precision and safety of surgical procedures. Its technical effects on ensuring surgical quality and promoting thorough tumor resection are particularly significant when dealing with anatomical variations or when performed by inexperienced surgeons. Attached Figure Description

[0024] To more clearly illustrate the technical solutions in this invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of this invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0025] Figure 1 This is a perspective view of Embodiment 1 of the present invention; Figure 2 This is an internal structural diagram of Embodiment 1 of the present invention; Figure 3This is an internal structural diagram of Embodiment 1 of the present invention; Figure 4 This is an internal structural diagram of Embodiment 2 of the present invention; Figure 5 This is an internal structural diagram of Embodiment 2 of the present invention; Figure 6 These are images captured by a laparoscopic camera under white light during actual surgery. Figure 7 The laparoscopic lens used in actual surgery is enhanced with the visual image captured under purple light conditions as described in this invention. Figure 8 This is a flowchart of the control method in Embodiment 3 of the present invention.

[0026] Figure label: 100. Cabinet; 101. Fiber optic interface; 102. Main fiber optic cable; 103. Branch fiber optic cable; 104. White LED; 105. Purple LED; 106. Blue LED; 107. Green LED; 108. Fiber optic combiner; 109. Mounting bracket; 110. Control circuit board; 111. Control panel; 112. Switching circuit module; 113. Power switch; 114. Glass sleeve. Detailed Implementation

[0027] Embodiments of the present invention are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present invention, and should not be construed as limiting the present invention.

[0028] Example 1 like Figures 1 to 3 As shown, this application provides a light source output device for laparoscopic surgical structure identification. The device is encapsulated inside a box 100. The outer panel of the box 100 is provided with an optical fiber interface 101 for connecting a laparoscopic optical fiber catheter, a control panel 111 for operators to select and control functions, and a power switch 113 for starting or stopping the power supply of the entire device.

[0029] Inside the housing 100, a light source generation and transmission system is installed. This system includes at least four different types of light-emitting units: white LEDs 104, purple LEDs 105, blue LEDs 106, and green LEDs 107. To ensure the positional stability and optical path alignment accuracy of these light-emitting units during operation, each LED is uniformly mounted on an internally fixed bracket 109. This integrated mounting method not only facilitates unified calibration during production assembly but also ensures that the relative positions of each light source remain constant during long-term use or transportation, thereby ensuring the long-term reliability of the optical path system.

[0030] The optical transmission section consists of several branch optical fibers 103 and a main optical fiber 102. The optical input end of each branch optical fiber 103 is precisely aligned and close to the light-emitting side of an LED to receive its emitted light with maximum efficiency. The optical output ends of all branch optical fibers 103 are converged and coupled to the optical input end of the main optical fiber 102 via a fiber optic combiner 108. The optical output end of the main optical fiber 102 is ultimately connected to the fiber optic interface 101 outside the housing 100. The fiber optic combiner 108 efficiently combines optical signals from different branch optical fibers into a single main optical fiber, effectively reducing signal loss during the convergence process.

[0031] In this embodiment, to enhance the display of specific human tissue structures, the wavelengths of each special-color LED are specifically selected. Specifically, the center emission wavelength of the violet LED 105 is set to 385nm, a wavelength proven to specifically enhance the visual contrast of tissue membrane layers; the center emission wavelength of the blue LED 106 is set to 460nm, utilizing the strong absorption characteristics of hemoglobin in blood in this wavelength band to specifically display vascular structures; and the center emission wavelength of the green LED 107 is set to 500nm to assist in identifying structures such as lymph nodes. To ensure compatibility of the optical path components with all light sources, the operating wavelength range of the selected fiber optic combiner 108 is set to 380nm to 510nm. This range fully covers all the aforementioned specific wavelengths and the main spectral components of white light, ensuring that the optical signal passes through the combiner with consistently high efficiency when switching between any light source. Similarly, both the main fiber 102 and the branch fiber 103 are multimode fibers with an operating wavelength range of 350 nm to 600 nm, a core diameter of 50 μm to 200 μm, and a numerical aperture (NA) of not less than 0.22. These parameters are chosen to ensure that the optical fiber has efficient reception and low-loss transmission capabilities for LED light sources.

[0032] Furthermore, the control system of the device consists of a control circuit board 110 located inside the housing 100. This control circuit board 110 integrates a microcontroller unit (MCU) and provides independent, programmable constant current drive circuits for the white LED 104, purple LED 105, blue LED 106, and green LED 107. The control circuit board 110 is electrically connected to an external control panel 111 to receive user commands and drive the corresponding LEDs. The control panel 111 has buttons for switching light source modes and can be supplemented with "+" and "-" buttons for adjusting light intensity. Additionally, a switch circuit module 112 is connected between the control circuit board 110 and an external power switch 113, responsible for the power management of the entire device. When the user presses the mode switch button, the microcontroller unit can select to activate the corresponding LED drive circuit according to preset logic (e.g., white light → purple light → blue light → green light → cycle back to white light), while ensuring that other light sources are turned off to avoid interference from the mixing of different colored light. Once a specific light source mode is activated, the user can issue a dimming command via the "+" or "-" buttons. Upon receiving the command, the microcontroller unit linearly and smoothly changes the drive current by altering the duty cycle of the pulse width modulation (PWM) signal output from the corresponding constant current drive circuit, or by adjusting the reference voltage of the drive circuit. This allows for continuous fine-tuning of the light intensity. Furthermore, the control system also features parameter memory, enabling it to remember and recall commonly used brightness settings from different modes to adapt to the needs of various surgical scenarios.

[0033] Through the integrated control system described above, doctors can operate flexibly as needed during surgery. For example, ... Figure 6 As shown, under conventional white light illumination, the details and boundaries of abdominal tissues have limited contrast, making identification difficult. At this time, the user can switch to ultraviolet light mode via control panel 111. Control circuit board 110 then drives ultraviolet LED 105 to emit light, and the 385nm ultraviolet light is transmitted to the surgical area via a fiber optic system. Figure 7 As shown, under this specific wavelength of illumination, the contours and boundaries of the tissue membrane layer become exceptionally clear. Furthermore, if the surgeon believes there is still room for improvement in contrast, they can fine-tune it using the intensity adjustment button to find an optimal contrast window, maximizing the visualization of the target structure. This convenient mode switching combined with precise intensity adjustment significantly improves the accuracy and safety of surgeons performing detailed dissections, providing equally effective support for the accurate identification of other specialized structures such as blood vessels and lymph nodes.

[0034] Example 2 Based on the structure of Embodiment 1, this embodiment further optimizes the coupling structure between the LED and the branch optical fiber, such as... Figure 4 and Figure 5 As shown, in order to achieve higher precision and more stable optical path alignment, this embodiment adds a glass sleeve 114 to the connection point between each group of LEDs and the branch optical fiber on the fixed bracket 109 inside the housing 100.

[0035] Specifically, each glass sleeve 114 has openings at both ends to accommodate the light-emitting side of an LED and the light input end of a branch optical fiber 103, respectively. The inner diameter of the glass sleeve 114 is precision-machined to ensure a tight fit with the LED's package and the fiber's ferrule or end. When the LED and branch optical fiber are inserted and fixed from both ends of the sleeve, the inner wall of the sleeve provides precise mechanical guidance and positioning, ensuring that the LED's light-emitting central axis is highly aligned with the fiber's core central axis.

[0036] In this structure, glass was chosen as the material for the sleeve based on several technical considerations. First, glass has high transmittance across a wide spectral range of 350nm to 600nm, minimizing light loss through tiny gaps at the coupling interface. Second, the 385nm light emitted by the violet LED 105 in this design falls into the near-ultraviolet band. Many polymer materials will age and yellow under prolonged exposure to this band, leading to decreased light transmittance. Glass, especially quartz glass or borosilicate glass, possesses excellent resistance to ultraviolet radiation and chemical stability, ensuring stable performance of the violet channel over long-term operation. Furthermore, glass has a low coefficient of thermal expansion, exhibiting good dimensional stability when the LED generates heat and causes temperature changes, ensuring consistently high-precision alignment.

[0037] By employing the glass sleeve 114 coupling structure, this embodiment significantly improves the coupling efficiency from the light source to the optical fiber, resulting in higher light intensity and clearer images output to the surgical field of view under the same electrical power. Simultaneously, this rigid mechanical alignment structure effectively enhances the vibration resistance and long-term operational reliability of the optical path, ensuring that the device provides stable and high-quality enhanced illumination in various clinical environments.

[0038] Example 3 Based on the basic structure of Embodiment 1 above, this embodiment provides a light source output device and control method for laparoscopic surgical structure recognition. The specific implementation of this method is based on a control circuit board 110 located inside the housing (100). This control circuit board 110 integrates a microcontroller unit (MCU) and provides independent drive circuits for white LED 104, purple LED 105, blue LED 106, and green LED 107, capable of precise brightness adjustment via pulse width modulation (PWM). The core of this control method lies in the fact that the MCU, by executing a specific set of control logic, can interpret the complex operational intentions of the user on the control panel 111 and achieve coordinated control of multiple LED light sources, including simultaneously driving multiple LEDs of different colors to emit light at different brightness ratios, thereby generating user-defined mixed-spectrum illumination outside a preset range.

[0039] Specifically, the execution process of this control method is as follows: Step S1, the user instruction parsing step, specifically involves the following: First, the MCU firmware includes a user instruction parsing module. This module monitors the status and operation timing of specific buttons (e.g., the "mode switch" button) on the control panel 111 in real time using an internal timer. When the user performs a brief press operation (e.g., the button duration is less than 500 milliseconds), the module recognizes it as a "short press instruction" and executes the switching of preset lighting modes. These preset modes, in addition to the conventional white light mode that only turns on the white LED 104, may also include at least one enhancement mode. In enhancement mode, the MCU simultaneously drives the white LED 104 and a specific color LED (e.g., blue LED 106) to work together, forming a mixed spectral output that enhances the contrast of specific tissues (such as blood vessels) while retaining most of the true colors of the background environment.

[0040] Then, step S2, the dynamic spectral scanning step, is executed. Specifically, when the user continuously presses the same button (e.g., the button duration exceeds 1000 milliseconds), the instruction parsing module recognizes it as a "long press instruction." This instruction does not switch modes but serves as a trigger signal to enter the "dynamic spectral scanning" state. Once the long press instruction is recognized, the MCU immediately starts the dynamic spectral scanning program. In this program, the MCU first controls the driving circuit of the white LED (104) to output a constant, medium-intensity reference illumination. The purpose of this reference illumination is to ensure that the surgical field does not completely lose its background reference due to color changes during the entire scanning adjustment process, thereby ensuring the continuity and safety of the operation. Based on this white light reference illumination, the MCU will periodically and smoothly modulate the light intensity of other colored LEDs according to a preset program to guide the surgeon to preview different spectral enhancement effects. This modulation process is not a simple sequential change of monochromatic light but also includes a continuous evolution of multiple color superposition states. For example, when writing control program code for the MCU, the program code can be designed as follows: First, the brightness of the violet LED 105 is gradually increased. Then, while maintaining a certain violet light intensity, the brightness of the blue LED 106 is gradually increased, thereby producing an enhanced effect of violet and blue mixing. Afterward, the violet light intensity can be smoothly reduced while the brightness of the green LED 107 is increased to explore the enhanced region of blue and green mixing. The entire modulation process is continuous and includes multiple color superposition states, ensuring that the user has the opportunity to find and lock in the optimal combination they need in a mixed spectrum containing two or more enhanced colors.

[0041] Then, step S3, the custom spectral locking step, is executed. Specifically, during the continuous dynamic spectral scanning, the surgeon can observe in real time the enhancement effect of different mixed spectra on the current anatomical structure. When the surgeon observes that the mixed spectrum at a certain moment can most clearly display the target structure of interest, they only need to release the button that has been held down. This button release action is recognized by the instruction parsing module as a "lock command". Upon receiving the lock command, the MCU immediately stops the modulation program of the spectral scanning and simultaneously captures the PWM duty cycle values ​​of all LED channels (including white, violet, blue, and green light) at that moment. Subsequently, the MCU uses these multi-channel intensity values ​​as a user-defined spectral formula and continuously and stably drives each LED to emit light in synergy according to this formula. Thus, a personalized lighting mode, which is personally adjusted by the surgeon according to the real-time surgical field of view and best suited to the current identification needs, is generated and stably output.

[0042] The above method transforms the control of the light source from limited, discrete mode switching to free selection within a continuous spectral space. Surgeons can generate a more targeted lighting plan based on the specific anatomical conditions encountered during surgery, directly improving the accuracy of identifying fine structures. Simultaneously, because the entire process involves spectral superposition while preserving the white light baseline illumination, it ensures that while enhancing the target structure, a macroscopic sense of the surrounding tissue environment is not lost, thus improving surgical safety. Furthermore, this "long press-observe-release" interactive logic makes the complex personalized lighting process extremely intuitive and efficient; surgeons can complete adjustments without interrupting the surgical procedure, ensuring its smoothness.

[0043] The embodiments described above are for illustrative purposes only and are not intended to limit the scope of the invention. Various modifications and variations can be made to the above embodiments by those skilled in the art without departing from the spirit and scope of the invention, and all such modifications and variations should fall within the protection scope of the invention.

Claims

1. A light source output device for laparoscopic surgical structure identification, characterized in that, Includes the enclosure (100); The outer side of the housing (100) is provided with an optical fiber interface (101) for connecting to the laparoscopic light source interface. The housing (100) is equipped with a main optical fiber (102), several branch optical fibers (103), and at least white LED light-emitting diodes (104), purple LED light-emitting diodes (105), blue LED light-emitting diodes (106) and green LED light-emitting diodes (107). The light-emitting sides of the white LED (104), purple LED (105), blue LED (106), and green LED (107) are respectively close to and correspond to the light input ends of each of the branch optical fibers (103); The optical output ends of each of the branch optical fibers (103) are coupled to the optical input end of the main optical fiber (102), and the optical output end of the main optical fiber (102) is connected to the optical fiber interface (101). The violet LED (105) emits light at a wavelength of 385nm; The blue LED light-emitting diode (106) has an emission wavelength of 460nm; The green LED light-emitting diode (107) has an emission wavelength of 500nm.

2. The light source output device for laparoscopic surgical structure identification according to claim 1, characterized in that, The housing (100) is equipped with an optical fiber combiner (108). The optical output ends of each of the branch optical fibers (103) are coupled together to the optical input end of the main optical fiber (102) through the optical fiber combiner (108).

3. The light source output device for laparoscopic surgical structure identification according to claim 2, characterized in that, The fiber optic combiner (108) operates in the wavelength range of 380nm-510nm to accommodate wavelength transmission requirements of 385nm, 460nm, 500nm and white light.

4. The light source output device for laparoscopic surgical structure identification according to claim 1, characterized in that, The main optical fiber (102) and each branch optical fiber (103) are all multimode optical fibers with a working wavelength range of 350nm to 600nm, in order to meet the high-efficiency transmission requirements of 385nm, 460nm, 500nm and white light.

5. The light source output device for laparoscopic surgical structure identification according to claim 1, characterized in that, The core diameter of both the main optical fiber (102) and each branch optical fiber (103) is 50μm-200μm; and, The numerical aperture NA of the main optical fiber (102) and each branch optical fiber (103) is ≥0.

22.

6. The light source output device for laparoscopic surgical structure identification according to claim 1, characterized in that, A fixed bracket (109) is fixedly installed inside the housing (100); The white LED (104), purple LED (105), blue LED (106), and green LED (107) are all mounted on the fixed bracket (109).

7. The light source output device for laparoscopic surgical structure identification according to claim 1, characterized in that, The housing (100) is equipped with a control circuit board (110), which is electrically connected to the white LED (104), purple LED (105), blue LED (106) and green LED (107). The outer side of the housing (100) is provided with a control panel (111) electrically connected to the control circuit board (110) so as to control the white LED (104), purple LED (105), blue LED (106) and green LED (107) through the control panel (111). The housing (100) is provided with a switch circuit module (112) electrically connected to the control circuit board (110); the housing (100) is provided with a power switch (113) electrically connected to the switch circuit module (112) on the outside.

8. A light source output device and control method for laparoscopic surgical structure identification, applied to the light source output device as described in any one of claims 1 to 7, characterized in that, Includes the following steps: Step S1, User Instruction Parsing Step: The timing characteristics of user input instructions from the control panel are monitored and parsed in real time through the control circuit board; Specifically, when the timing feature is a short press operation, switching is performed between multiple preset lighting modes; when the timing feature is a long press operation, the dynamic spectral scanning step S2 is initiated. Step S2, Dynamic Spectral Scanning Step: During the long press operation, the control board performs the following coordinated control: (a) Control the white LED (104) to output illumination of a reference intensity; (b) Over a reference intensity of illumination, the light intensity of at least one of the said violet LED light-emitting diodes (105), blue LED light-emitting diodes (106) or green LED light-emitting diodes (107) is periodically and smoothly modulated to form a continuously varying spectral output; Step S3, Custom Spectrum Locking Step: The control board responds to a lock command triggered upon the end of a long press operation by performing the following operations: (c) Record the instantaneous light intensity values ​​of the white, purple, blue, and green LEDs at the moment the locking command is received; (d) Control the white, purple, blue and green LEDs to emit light in a stable and continuous manner according to the recorded instantaneous light intensity values, so as to output a user-defined mixed spectrum.

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