Near-infrared multiple imaging instrument for breast cancer tumor blood vessels and preparation method of near-infrared multiple imaging instrument

Abstract

The invention relates to a breast cancer tumor blood vessel near-infrared multiple imaging instrument and a preparation method, and the imaging instrument comprises an excitation imaging cooperation system which comprises a light source module, an optical imaging assembly and a detector, and the light source module and the detector are in state matching with a spectrum pair of an excitation wavelength and a receiving wavelength through a closed-loop feedback mechanism; the three-dimensional electric objective table is used for controlling the space positioning and visual field range of a detection area and is linked with the optical imaging assembly to dynamically adjust an imaging focal plane so as to be matched with the blood vessel depth; the map generation module is used for carrying out time-space domain decoupling processing on the time sequence fluorescence signals and respectively extracting blood vessel form distribution, hemodynamic parameters and molecular typing characteristics so as to generate a multi-imaging superposition map; and the surgical navigation interface is used for displaying the superposition map in real time and generating an intraoperative mark track and a boundary resection path based on the superposition map. The imaging instrument disclosed by the invention has high sensitivity, deep penetrability and multi-parameter synchronous analysis capability, and shows remarkable clinical advantages.

Description

Technical Field

[0001] The present invention relates to the technical field of medical imaging devices, and particularly to a near-infrared multi-modal imaging device for breast cancer tumor blood vessels and a preparation method thereof. Background Art

[0002] In the field of breast cancer diagnosis and treatment, traditional imaging techniques such as contrast-enhanced ultrasound, CT, and MRI have been widely used in blood vessel imaging, but there are still significant limitations. Due to insufficient resolution, contrast-enhanced ultrasound is difficult to clearly present the structure of tiny tumor blood vessels; although CT technology has a certain imaging speed, its radiation risk poses a potential hazard to patients, and its ability to distinguish soft tissues is weak, easily resulting in missed diagnosis of tiny blood vessels and occult lesions; although MRI has high soft tissue contrast, the imaging time is long, and patients need to remain stationary for a long time, which is prone to motion artifacts and affects the diagnostic accuracy. In addition, the above techniques rely highly on the experience of operators, and the diagnostic results are easily interfered by subjective factors, making it difficult to meet the needs of precise diagnosis and treatment.

[0003] In recent years, near-infrared fluorescence imaging technology has gradually been applied to surgical navigation due to advantages such as less light scattering and high signal-to-noise ratio. Among them, the near-infrared second window (NIR-II, 900 - 1700 nm) is considered to have significant potential in the field of tumor blood vessel imaging due to characteristics such as large penetration depth, high signal-background ratio, and weak biological autofluorescence. However, currently, the commonly used clinical systems are still based on the near-infrared first window (NIR-I, 760 - 900 nm). Its penetration ability and resolution are limited by the short wavelength, making it difficult to fully meet the needs of deep tissue imaging. Although NIR-II theoretically has better optical performance, due to technical bottlenecks such as optical system design, detector sensitivity, and fluorescent probe development, there is currently no clinically approved NIR-II imaging system. This situation leads to insufficient accuracy in breast cancer tiny blood vessel imaging, especially in detecting sub-millimeter metastases, real-time displaying hemodynamic changes, and the fine structure of the lymphatic system, with significant technical gaps.

[0004] In addition, the rapid discrimination of breast cancer molecular subtypes and the dynamic monitoring of blood vessels after treatment are crucial for personalized treatment. The existing immunohistochemical typing method is time-consuming and relies on pathological experience, while traditional imaging techniques are difficult to reflect the differences in tumor blood vessel characteristics in real time. At the same time, as a common postoperative complication, the precise assessment of lymphedema depends on high-resolution imaging to locate the blocked lymphatic vessels, but the existing techniques such as ultrasound have limited ability to image micron-scale lymphatic vessels.

[0005] Therefore, the development of a new imaging device that can integrate high sensitivity, deep penetration, and multi-modal imaging functions has become a key technical requirement for improving the level of breast cancer diagnosis and treatment. Summary of the Invention

[0006] (1) Technical Problems to be Solved

[0007] In view of the above-mentioned shortcomings and deficiencies of the prior art, the present invention provides a near-infrared multiplex imager for breast cancer tumor blood vessels and a preparation method, which solves the technical problems of the existing breast cancer vascular imaging technology, such as insufficient resolution, high radiation risk, long imaging time, dependence on operator experience, and difficulty in meeting the needs of precise diagnosis and treatment.

[0008] (II) Technical solution

[0009] In order to achieve the above object, the main technical solutions adopted by the present invention include:

[0010] In a first aspect, an embodiment of the present invention provides a near-infrared multiplex imaging device for breast cancer tumor blood vessels, comprising:

[0011] The excitation imaging collaborative system includes a wavelength tunable light source module, an optical imaging component and a detector. The wavelength tunable light source module and the detector dynamically match the spectral pair of the excitation wavelength and the receiving wavelength through a closed-loop feedback mechanism;

[0012] A three-dimensional electric stage is used to control the spatial positioning and field of view of the detection area through three-dimensional spatial displacement, and to dynamically adjust the imaging focal plane to match the depth of the blood vessel by linking the optical imaging component;

[0013] The atlas generation module is used to perform spatiotemporal decoupling processing on the time-series fluorescence signals transmitted by the detector, and to extract the vascular morphology distribution, hemodynamic parameters and molecular typing characteristics through parallel independent calculation channels to generate a superimposed atlas of multiple imaging;

[0014] The surgical navigation interface is used to display the superimposed atlas in real time and generate intraoperative marking trajectories and boundary resection paths based on the dynamic changes of vascular features in the superimposed atlas.

[0015] Optionally, the wavelength tunable light source module includes:

[0016] A light emitting element for emitting laser light in the near-infrared region II;

[0017] The optical fiber coupling component includes an optical adjustment frame and a collimator. The light-emitting element is coupled and aligned with the transmission optical fiber through the optical adjustment frame. The collimating lens converts the excitation light into a collimated light beam and then transmits it to the optical imaging component in a direction;

[0018] A temperature control unit, thermally coupled to the light-emitting element, suppresses wavelength drift and optical power fluctuations through active temperature control;

[0019] A current modulation unit, comprising a microcontroller and a current source circuit, for dynamically adjusting a driving current of the current source circuit through a closed-loop feedback mechanism;

[0020] Among them, the current modulation unit and the temperature control unit cooperate and control through sharing feedback signals, so that the spectra of the laser wavelength and the detector receiving wavelength are adaptively matched in real time.

[0021] Optionally, the optical imaging assembly includes:

[0022] A barrel lens group, arranged axially along the optical path, for converging the fluorescence signals in the second near-infrared region;

[0023] A dichroic mirror group, arranged on the outgoing optical path of the barrel lens group at a preset inclination angle, for separating the excitation light and the fluorescence signals;

[0024] A filter group, forming a multi-stage background light suppression channel with the dichroic mirror group, and including a narrow-band filter matching the excitation light wavelength;

[0025] A sealed housing, covering the barrel lens group, the dichroic mirror group and the filter group. The inner wall of the sealed housing is provided with an anti-reflection coating and the joints are encapsulated with an optical-grade sealant.

[0026] Optionally, the detector includes:

[0027] An area array detector group, coaxially arranged with the filter group of the optical imaging assembly, configured to receive and convert the fluorescence signals;

[0028] A signal conditioning module, including a shielded cable, a filtering unit and a signal amplifier, constituting an anti-interference transmission link from photoelectric conversion to an image acquisition system;

[0029] Among them, the area array detector group and the signal conditioning module adopt a modular packaging structure, and realize the time-sequence fidelity conversion of the fluorescence signals through a synchronous triggering mechanism.

[0030] Optionally, the three-dimensional electric stage includes:

[0031] A multi-axial displacement platform, composed of XYZ-axis slide rails distributed orthogonally, for carrying the sample to be detected;

[0032] A driving component, including a stepping motor and a reduction gear set, adjusting the displacement of each axis through closed-loop feedback control to achieve three-dimensional spatial positioning;

[0033] A grating scale positioning module, embedded in the base of the displacement platform, and real-time feedback the position information to the optical imaging assembly;

[0034] Among them, the displacement platform and the optical imaging assembly form a closed-loop control through a mechanical linkage mechanism. The driving component responds to the blood vessel depth parameter to dynamically adjust the displacement amount, and realizes the synchronous matching of the spatial positioning of the detection area and the imaging focal plane.

[0035] Optionally, the surgical navigation interface includes:

[0036] An anti-glare display screen for real-time display of intraoperative fluorescence images with superimposed vascular feature maps;

[0037] A graphical interaction panel configured with hierarchical operation interfaces for light source power adjustment, image acquisition parameter control, and image processing parameter regulation;

[0038] A dynamic navigation layer, communicating with a three-dimensional electric stage and an optical imaging component, for superimposing real-time positioning marks based on vascular depth information, spatially registering the fluorescence image with a preset vascular distribution model, and generating navigation guidance;

[0039] Among them, the graphical interaction panel realizes dynamic parameter adjustment through touch or external input devices, and the dynamic navigation layer is synchronously updated with the change of the imaging focal plane of the optical imaging component, forming a closed-loop feedback of spatial positioning and image display.

[0040] In a second aspect, an embodiment of the present invention provides a preparation method for a near-infrared multi-modal imaging instrument for breast cancer tumor blood vessels, including:

[0041] S1. In a preset clean environment, couple and align a light-emitting element with a transmission optical fiber through an optical adjustment bracket to form an excitation light transmission link, and synchronously integrate a temperature control unit and a current modulation unit to form a wavelength-tunable light source module;

[0042] S2. Coaxially assemble a lens barrel lens group, a dichroic mirror group, and a filter group into a modular optical path through a positioning fixture, and encapsulate it in a sealed housing to form an optical imaging component with multiple-stage background light suppression channels;

[0043] S3. Perform micron-level spatial matching between the area array detector group and the imaging focal plane of the optical imaging component, and configure an anti-interference transmission link to form a detector;

[0044] S4. Construct a multi-axial displacement platform and integrate a drive component and a grating scale positioning module to obtain a three-dimensional electric stage, and establish a mechanical linkage with the optical imaging component to dynamically adjust the imaging focal plane;

[0045] S5. Fix the anti-glare display screen and the graphical interaction interface to an adjustable bracket, and deploy operation software to realize the coordinated control of the laser parameters of the wavelength-tunable light source module, the imaging focal plane of the optical imaging component, the displacement of the three-dimensional electric stage, and the access parameters of the detector, and establish a synchronous update mechanism between the dynamic navigation layer and the imaging focal plane.

[0046] Optionally, step S1 includes:

[0047] Couple and align the light-emitting element with the transmission optical fiber through the optical adjustment bracket;

[0048] Thermally couple a temperature control unit to the light-emitting element to suppress wavelength drift, and integrate a current modulation unit to dynamically adjust the driving current through a microcontroller;

[0049] Cooperatively control the temperature control unit and the current modulation unit by sharing a feedback signal to make the excitation light wavelength and the detector receiving wavelength match in real time.

[0050] Optionally, step S2 includes:

[0051] Arrange the lens barrel lens group, dichroic mirror group and filter group coaxially at a preset inclination angle to form a multi-stage background light suppression channel;

[0052] Use a sealed housing with an anti-reflection coating to cover the lens barrel lens group, dichroic mirror group and filter group, inject dry gas to maintain a constant pressure environment and use an optical-grade sealant to seal the seams;

[0053] After encapsulation, use an interferometer to calibrate the optical resolution to not less than a preset threshold.

[0054] Optionally, step S4 includes:

[0055] Embed a grating scale positioning module in the base of the multi-axial displacement platform and form a closed-loop feedback control with the stepper motor of the driving component;

[0056] Connect the multi-axial displacement platform and the optical imaging component through a mechanical linkage mechanism, and dynamically adjust the XYZ axial displacement amount in response to the obtained blood vessel depth parameter to achieve synchronous matching of the spatial positioning of the detection area and the imaging focal plane.

[0057] (III) Advantageous Effects

[0058] The advantageous effects of the present invention are: The near-infrared multi-modal imaging instrument for breast cancer tumor blood vessels provided by the present invention significantly improves the accuracy and efficiency of breast cancer diagnosis and treatment through the following technologies:

[0059] First, the excitation imaging cooperation system adopts a closed-loop feedback mechanism of a wavelength-tunable light source module and a detector to dynamically match the spectral pair of the excitation wavelength and the receiving wavelength, solving the problems of insufficient penetration depth and signal interference caused by fixed wavelengths in traditional imaging technologies. Thus, while ensuring high-resolution imaging (able to clearly display sub-millimeter blood vessel morphology) under non-ionizing radiation conditions, it significantly reduces the dependence on the operator's experience.

[0060] Secondly, based on the synchronous regulation of the spatial displacement of the stage and the focal plane of the optical imaging component, multi-depth blood vessel tomography imaging and large-field rapid scanning are realized, shortening the single imaging time and solving the problem of low scanning efficiency in the prior art.

[0061] Furthermore, through spatio-temporal decoupling processing and parallel computing channels, the atlas generation module can independently extract the vascular morphological distribution, hemodynamic parameters, and molecular typing characteristics from the temporal fluorescence signals, and generate a multi-imaging superposition atlas. This shortens the molecular typing discrimination time from several hours to real-time during the operation, meeting the need for synchronous analysis of multi-dimensional information in precise diagnosis and treatment.

[0062] In addition, based on the dynamic changes of blood vessels in the superposition atlas, the surgical navigation interface generates intraoperative marking trajectories and boundary resection paths, enabling doctors to visually identify the tumor invasion range and abnormal lymphatic drainage areas. Combining the collaborative control of the probe injection and imaging parameters by the fluorescence probe management module, the system avoids the problem of image quality attenuation caused by probe metabolism fluctuations in traditional technologies during intraoperative real-time navigation, significantly improving the accuracy of surgical resection and the reliability of lymphedema assessment.

[0063] Finally, the integrated design of the above functional modules enables the imaging device to have high sensitivity, deep penetration, and multi-parameter synchronous analysis capabilities, showing significant clinical advantages in scenarios such as screening for small breast cancer metastases, formulating personalized treatment plans, and monitoring postoperative complications. Description of the Drawings

[0064] Figure 1 It is a schematic structural diagram of a near-infrared multi-imaging device for breast cancer tumor blood vessels provided by an embodiment of the present invention;

[0065] Figure 2 It is a schematic flow diagram of a preparation method of a near-infrared multi-imaging device for breast cancer tumor blood vessels provided by an embodiment of the present invention;

[0066] Figure 3 It is a specific schematic flow diagram of step S1 of the preparation method of a near-infrared multi-imaging device for breast cancer tumor blood vessels provided by an embodiment of the present invention;

[0067] Figure 4 It is a specific schematic flow diagram of step S2 of the preparation method of a near-infrared multi-imaging device for breast cancer tumor blood vessels provided by an embodiment of the present invention;

[0068] Figure 5 It is the near-infrared second-region fluorescence imaging result of the blood vessels on the back of a healthy nude mouse provided by an embodiment of the present invention;

[0069] Figure 6 It is a specific schematic flow diagram of step S4 of the preparation method of a near-infrared multi-imaging device for breast cancer tumor blood vessels provided by an embodiment of the present invention;

[0070] Figure 7 It is the near-infrared second-region fluorescence imaging result of a breast cancer tumor in a nude mouse provided by an embodiment of the present invention.

[0071]

Explanation of the Reference Numerals

[0072] 1: sample to be detected; 2: first light source module; 3: second light source module; 4: barrel lens group; 5: dichroic mirror group; 6: first filter; 7: second filter; 8: first detector; 9: second detector. DETAILED DESCRIPTION

[0073] In order to better explain the present invention and facilitate understanding, the present invention is described in detail below through specific implementation modes in conjunction with the accompanying drawings.

[0074] like Figure 1 As shown, a breast cancer tumor blood vessel near-infrared multiple imager proposed in an embodiment of the present invention includes: an excitation imaging collaborative system, including a wavelength-tunable light source module, an optical imaging component and a detector, wherein the wavelength-tunable light source module and the detector dynamically match the spectral pair of the excitation wavelength and the receiving wavelength through a closed-loop feedback mechanism; a three-dimensional electric stage, used to control the spatial positioning and field of view of the detection area through three-dimensional spatial displacement, and dynamically adjust the imaging focal plane to match the blood vessel depth by linking the optical imaging component; a spectrum generation module, used to perform spatiotemporal decoupling processing on the time-series fluorescence signal transmitted from the detector, and respectively extract the blood vessel morphological distribution, hemodynamic parameters and molecular typing characteristics through parallel independent calculation channels to generate a superimposed spectrum of multiple imaging; a surgical navigation interface, used to display the superimposed spectrum in real time, and generate an intraoperative marking trajectory and a boundary resection path based on the dynamic changes of the blood vessel characteristics in the superimposed spectrum.

[0075] The breast cancer tumor vascular near-infrared multiplex imaging device provided by the present invention significantly improves the accuracy and efficiency of breast cancer diagnosis and treatment through the collaboration of the following technologies:

[0076] First, the excitation imaging collaborative system adopts a wavelength-tunable light source module and a closed-loop feedback mechanism of the detector to dynamically match the spectral pair of excitation wavelength and receiving wavelength, solving the problems of insufficient penetration depth and signal interference caused by fixed wavelength in traditional imaging technology. It ensures high-resolution imaging (clearly displaying submillimeter vascular morphology) under non-ionizing radiation conditions while significantly reducing dependence on operator experience.

[0077] Secondly, based on the synchronous control of the spatial displacement of the stage and the focal plane of the optical imaging component, multi-depth vascular tomography and large-field rapid scanning are achieved, which shortens the single imaging time and solves the problem of low scanning efficiency of existing technologies.

[0078] Furthermore, the atlas generation module can independently extract the vascular morphological distribution, hemodynamic parameters, and molecular typing features from the temporal fluorescence signals through spatio-temporal decoupling processing and parallel computing channels, and generate a multi-imaging superposition atlas. This shortens the molecular typing discrimination time from several hours to real-time during the operation, meeting the requirements of precise diagnosis and treatment for synchronous analysis of multi-dimensional information.

[0079] In addition, based on the dynamic changes of blood vessels in the superposition atlas, the surgical navigation interface generates intraoperative marking trajectories and boundary resection paths, enabling doctors to visually identify the tumor invasion range and abnormal lymphatic drainage areas. Combined with the collaborative control of the probe injection and imaging parameters by the fluorescence probe management module, the system avoids the image quality attenuation problem caused by probe metabolism fluctuations in traditional technologies during intraoperative real-time navigation, significantly improving the accuracy of surgical resection and the reliability of lymphedema assessment.

[0080] Finally, the integrated design of the above functional modules enables the imaging device to have high sensitivity, deep penetration, and multi-parameter synchronous analysis capabilities, showing significant clinical advantages in scenarios such as screening for small breast cancer metastases, formulating personalized treatment plans, and monitoring postoperative complications.

[0081] To better understand the above technical solution, the exemplary embodiments of the present invention will be described in more detail below with reference to the accompanying drawings. Although the exemplary embodiments of the present invention are shown in the drawings, it should be understood that the present invention can be implemented in various forms and should not be limited by the embodiments set forth herein. On the contrary, these embodiments are provided to enable a more clear and thorough understanding of the present invention and to fully convey the scope of the present invention to those skilled in the art.

[0082] Among them, the wavelength-tunable light source module includes a light-emitting element, an optical fiber coupling component, a temperature control unit, and a current modulation unit.

[0083] In one embodiment, a quantum cascade laser is used as the light-emitting element to emit excitation light in the second near-infrared region (900 - 1700 nm); the optical fiber coupling component includes an optical adjustment bracket and a collimator. The light-emitting element is coupled and aligned with the transmission optical fiber through the optical adjustment bracket, and the collimating lens converts the excitation light into a collimated beam and then transmits it directionally to the optical imaging component. Preferably, the optical fiber is a homogenized liquid-core optical fiber; the temperature control unit is thermally coupled to the light-emitting element and adjusts the element temperature by active heat dissipation or heating to suppress wavelength drift and optical power fluctuations caused by temperature changes; the current modulation unit includes a microcontroller and a current source circuit, and is used to dynamically adjust the driving current of the current source circuit through a closed-loop feedback mechanism to meet the excitation requirements of different fluorescence probes.

[0084] It should be clear that the temperature sensor and the optical power detector share the feedback signal to the microcontroller to synchronously optimize the temperature control and current modulation parameters. When the wavelength shift is detected, the refrigeration power and the drive current are jointly adjusted to make the spectral pair matching error between the laser wavelength and the detector receiving wavelength less than the set value, ensuring that the excitation-reception spectrum is adapted in real time. Thus, through the temperature-current double closed-loop collaborative control, without introducing additional data, a highly stable output of the excitation light source is achieved, providing excitation light conditions with precise wavelength and adjustable power for the multi-modal imaging of tumor blood vessels. Refer to Figure 1 , the first light source module 2 and the second light source module 3 can be set to be placed at 90° with the same working distance to ensure the same imaging field of view.

[0085] Secondly, the optical imaging component includes: a lens barrel lens group 4 arranged axially along the optical path for converging the near-infrared second-region fluorescence signal to enable clear imaging of even tiny tumor blood vessels; a dichroic mirror group 5 disposed on the outgoing optical path of the lens barrel lens group 4 at a preset inclination angle for separating the excitation light and the fluorescence signal. The incident angle of the dichroic mirror is 45°, the transmission band is 685 - 1600 nm, and the reflection band is 400 - 633 nm; a filter group that forms a multi-stage background light suppression channel with the dichroic mirror group 5, including a narrow-band filter matching the excitation light wavelength. The center wavelength of the filter is precisely matched with the excitation light wavelength, and the bandwidth does not exceed 50 nm, effectively blocking the background light and other interference signals and improving the signal-to-noise ratio of the fluorescence image; and a sealed housing that covers the lens barrel lens group 4, the dichroic mirror group 5, and the filter group. The inner wall of the sealed housing is provided with an anti-reflection coating and the joints are sealed with an optical-grade sealant. The housing of the optical imaging component is made of a material with low scattering and high light transmittance, such as special optical plastic or quartz glass. The internal optical elements are calibrated and sealed with high precision to prevent dust and moisture from entering and ensure the stability of the optical performance.

[0086] Then, the detector includes: an area array detector group coaxially arranged with the filter group of the optical imaging component and configured to receive and convert the fluorescence signal; a signal conditioning module including a shielded cable, a filtering unit, and a signal amplifier, constituting an anti-interference transmission link from the photoelectric conversion to the image acquisition system; wherein, the area array detector group and the signal conditioning module adopt a modular packaging structure. The pixel unit density of the area array detector group matches the spatial frequency of the microvascular structure, and the response speed of the signal conditioning module is adapted to the fluorescence decay time constant, realizing the time-sequence fidelity conversion of the fluorescence signal through a synchronous triggering mechanism. Refer to Figure 1 , the first filter 6 and the second filter 7 can be set.

[0087] In this embodiment, a detector suitable for the second near-infrared region band is selected, with a quantum efficiency of not less than 85% and a pixel resolution of not less than 640x512. The high quantum efficiency ensures that the detector can efficiently capture weak second near-infrared fluorescence signals, and the high pixel resolution guarantees the clarity of imaging and can capture the fine structure of tumor blood vessels.

[0088] Optionally, two sets of area array detector groups are installed at the rear end of the optical imaging component, and their working distances are adjusted to a unified set value through a precision mechanical bracket to ensure the consistency of the field of view space for dual-view imaging; the photosensitive surface of the detector is strictly coaxially aligned with the filter group. The detector and the signal conditioning module are integrated in an electromagnetic shielding cavity and connected by a double-layer shielded coaxial cable, with the outer layer of the cable grounded to suppress common-mode interference; a synchronous trigger pulse is generated by the FPGA to control the exposure time deviation of the two detectors ≤1 μs and maintain strict phase locking with the excitation light source modulation signal to achieve spatio-temporal consistency acquisition and fidelity of weak fluorescence signals for dual-channel fluorescence signals. In this way, a dual-detection path composed of the first detector 8 and the second detector 9 is formed.

[0089] In addition, the three-dimensional electric stage includes: a multi-axial displacement platform composed of XYZ-axis slide rails distributed orthogonally for carrying the sample to be detected 1; a driving component including a stepper motor and a reduction gear set, which adjusts the displacement of each axis through closed-loop feedback control to achieve three-dimensional spatial positioning; a grating scale positioning module embedded in the base of the displacement platform to real-time feedback position information to the optical imaging component; among them, the displacement platform and the optical imaging component form a closed-loop control through a mechanical linkage mechanism, and the driving component dynamically adjusts the displacement according to the blood vessel depth parameter to achieve synchronous matching of the spatial positioning of the detection area and the imaging focal plane.

[0090] Subsequently, the spectral generation module first establishes a hybrid wavelet-Fourier transform model for the time-series fluorescence signal to separate the dynamic time-domain characteristics related to blood vessel pulsation and blood flow velocity: where the transformation model is:

[0091]

[0092] In the formula, S(t) is the mixed feature containing blood vessel pulsation and blood flow velocity, F -1 is the inverse Fourier transform operator, is the Fourier spectrum of the kth frequency band, is the Morlet wavelet basis function, is the Gaussian window function, is based on the Morlet wavelet basis function, σ k and a k are the frequency band attenuation coefficient and the scale factor respectively, to achieve the separation and extraction of the characteristics of blood vessel pulsation (0.1 - 2 Hz) and blood flow velocity (10 - 100 Hz).

[0093] After that, a spatial point spread function compensation model is constructed by a three-dimensional deconvolution algorithm to eliminate optical scattering noise:

[0094]

[0095] where I rec is the reconstructed three-dimensional vascular topological image, I raw is the original blurred three-dimensional fluorescence image, PSF(x, y, z) is the measured point spread function tensor of the optical system, is the three-dimensional convolution operation, is the square of the L2 norm, λ is the regularization weight coefficient, TV(I) is the total variation regularization term, which is iteratively solved by the alternating direction method of multipliers (ADMM) to reconstruct the vascular spatial topological structure and improve the vascular topological reconstruction resolution to ≤20 μm, and the following feature extraction channels are executed in parallel:

[0096] (1) Vascular morphology channel: The morphological skeletonization algorithm is used to extract the vascular branch density, diameter distribution and curvature parameters, and generate a binary morphological distribution map, specifically:

[0097]

[0098] where λ1, λ2 are the eigenvalues of the Hessian matrix, |λ1| ≤ |λ2|, which are used to describe the curvature characteristics of the local structure of the image, ε is the scale parameter of the filter, which controls the diameter range of the detected blood vessels, and β, γ are both weight adjustment factors. β controls the sensitivity to tubular structures (the smaller the value, the stronger the response to tubes), and γ suppresses background noise (the larger the value, the stronger the noise suppression). Through multi-scale Hessian analysis, the contrast between blood vessels and the background is enhanced, and non-tubular structures (such as noise or tissue boundaries) are suppressed.

[0099] (2) Hemodynamics channel: Based on the optical flow method, the blood flow velocity field (accuracy ±0.5 mm / s) is calculated, and the blood flow volume and vascular wall shear stress parameters are extracted by integrating the time-series signals, specifically:

[0100] The blood flow volume is

[0101]

[0102] where I x , I y , I tThey are the partial derivatives of the image grayscale in the spatial (x, y) and temporal (t) directions respectively, reflecting the brightness change. u and v are the components of the optical flow field to be solved (the moving speeds of pixels in the x and y directions). κ is the regularization coefficient, which balances the data fidelity term (the left term) and the velocity field smoothing term (the right term). A κ greater than the set value will make the optical flow field smoother, but may blur the motion boundary; a κ not greater than the set value will retain the motion details but is sensitive to noise.

[0103] The wall shear stress of blood vessels is:

[0104]

[0105] In the formula, P s is the dynamic viscosity of blood (Pa·s), reflecting the internal friction characteristics of the fluid. v z is the axial velocity component of blood flow (along the blood vessel length direction). r is the radial coordinate (the distance from a point in the blood vessel cross-section to the center). R is the blood vessel radius (the inner diameter of the blood vessel at the current measurement position).

[0106] (3) Molecular typing channel: Analyze the fluorescence spectrum characteristics through principal component analysis (PCA), match the preset molecular probe database, and output the heat map of tumor blood vessel-specific molecular markers. Specifically: construct the spectral feature moment {X}, and perform weighted principal component analysis to select the first 3 principal components to construct the molecular marker probability map.

[0107] After that, weights are assigned to the output data of the three channels according to the signal-to-noise ratio of each channel (such as morphology: 0.4, blood flow: 0.3, molecule: 0.3), and the α blending technology is used to generate the RGB pseudo-color overlay map. In this way, the multi-dimensional synchronous analysis of blood vessel morphology-function-molecular characteristics is realized, meeting the intraoperative real-time navigation requirements.

[0108] Furthermore, the surgical navigation interface includes: an anti-glare display screen for real-time displaying the intraoperative fluorescence image of the overlay blood vessel feature map; a graphical interaction panel configured with hierarchical operation interfaces for adjusting the light source power, controlling the image acquisition parameters, and regulating the image processing parameters; a dynamic navigation layer, communicating with the three-dimensional electric stage and the optical imaging component, for overlaying real-time positioning marks based on the blood vessel depth information, spatially registering the fluorescence image with the preset blood vessel distribution model, and generating navigation guidance; among them, the graphical interaction panel realizes dynamic parameter adjustment through touch or external input devices, and the dynamic navigation layer is updated synchronously with the change of the imaging focal plane of the optical imaging component, forming a closed-loop feedback of spatial positioning and image display.

[0109] The surgical navigation interface of this embodiment includes multiple key components. First, an anti-glare display screen is used to display the intraoperative fluorescence image with the vascular feature map superimposed in real time. This display screen effectively suppresses the reflection of ambient light through an anti-glare coating, thus ensuring the visibility of the image in the surgical scenario.

[0110] Secondly, the graphical interaction panel is another important component of this interface. This panel is configured with hierarchical operation interfaces, specifically including functions such as light source power adjustment, image acquisition parameter control, and image processing parameter regulation. The graphical interaction panel can dynamically adjust parameters through touch or external input devices.

[0111] In addition, the surgical navigation interface also includes a dynamic navigation layer. This layer communicates with the three-dimensional electric stage and the optical imaging component, and is used to superimpose real-time positioning marks based on the vascular depth information. Specifically, it performs spatial registration on the fluorescence image and the preset vascular distribution model, and generates navigation guidance. The dynamic navigation layer receives the spatial positioning data of the three-dimensional electric stage and the focal plane parameters of the optical imaging component, and dynamically superimposes positioning marks corresponding to the vascular depth, such as crosshairs, boundary contour lines, etc. At the same time, it performs spatial registration on the real-time fluorescence image and the preset vascular distribution model, and generates navigation guidance through feature point matching, such as arrow indicating the resection direction, color block marking high-risk areas. With the change of the imaging focal plane, the dynamic navigation layer is automatically updated to form a closed-loop control of stage displacement - image display - operation feedback. The dynamic navigation layer is updated synchronously with the change of the imaging focal plane of the optical imaging component, realizing the closed-loop feedback of spatial positioning and image display.

[0112] In addition, the embodiment of the present invention provides a preparation method for a near-infrared multi-modal imaging instrument for breast cancer tumor blood vessels, as Figure 2 shown, including:

[0113] S1. In a preset clean environment, couple and align the light-emitting element with the transmission optical fiber through an optical adjustment frame to form an excitation light transmission link, and synchronously integrate a temperature control unit and a current modulation unit to form a wavelength-tunable light source module.

[0114] Further, as Figure 3 shown, step S1 includes:

[0115] S11. Couple and align the light-emitting element with the transmission optical fiber through an optical adjustment frame.

[0116] S12. Thermally couple a temperature control unit to the light-emitting element to suppress wavelength drift, and integrate a current modulation unit to dynamically adjust the driving current through a microcontroller.

[0117] S13. Coordinate and control the temperature control unit and the current modulation unit through a shared feedback signal to make the excitation light wavelength match the detector receiving wavelength in real time.

[0118] In a specific embodiment, in a clean operating environment maintained by an air filtration system, temperature and humidity control, and anti-static measures, the following preparation of the light source module is performed according to Figure 1 the structure shown:

[0119] (1) Mount the fiber laser on the bottom of the instrument through a high-precision optical adjustment bracket, and control the coupling accuracy between the laser emission end and the transmission fiber within the range of ±5 μm to form an excitation light transmission link.

[0120] (2) Integrate a temperature control unit inside the laser package, directly contact the laser chip through a heat sink to suppress wavelength drift, synchronously connect a high-precision current source circuit based on an operational amplifier, and use an STM32 microcontroller to output a PWM signal to adjust the drive current.

[0121] (3) Feed the real-time wavelength data detected by the spectral analyzer back to the microcontroller, dynamically adjust the outputs of the temperature control unit and the current modulation unit, so that the excitation light wavelength matches the detector receiving band.

[0122] (4) Measure the laser output wavelength using a spectral analyzer with a resolution of 0.1 nm, and iteratively adjust the current value through the microcontroller. Calibrate the optical power density using a power meter with an accuracy of ±0.01 mW / cm 2 Verify the power linearity within the current modulation range. After multiple tests and calibrations, make the near-infrared excitation light source module meet the design requirements and ensure that it can provide excitation light meeting the standards for the entire imager.

[0123] S2. Coaxially assemble the lens barrel lens group 4, dichroic mirror group 5, and filter group through a positioning fixture into a modular optical path, and encapsulate them in a sealed housing to form an optical imaging component with multiple background light suppression channels.

[0124] Further, as Figure 4 shown, step S2 includes:

[0125] S21. Coaxially arrange the lens barrel lens group 4, dichroic mirror group 5, and filter group at a preset inclination angle to form multiple background light suppression channels.

[0126] S22. Coaxially assemble the lens barrel lens group 4, dichroic mirror group 5, and filter group with a sealed housing containing an anti-reflection coating, inject dry gas to maintain a constant pressure environment, and use an optical-grade sealant to seal the joints.

[0127] S23. After encapsulation, use an interferometer to calibrate the optical resolution to not less than a preset threshold.

[0128] In a specific embodiment, the manufacture of the optical imaging component includes the following sub-steps:

[0129] (1) Assemble the lens barrel lens group 4, dichroic mirror group 5 and filter group coaxially through a high-precision positioning fixture, ensuring that the coaxiality error of the lens group is within ±5 μm and the relative position accuracy between the filter and the lens group is within ±10 μm, so as to ensure that light can propagate along the designed optical path and form an optical path structure of a multi-stage background light suppression channel. During the assembly process, the dichroic mirror group 5 is arranged at a preset inclination angle to optimize the separation efficiency of the excitation light and fluorescence.

[0130] (2) Adopt a cycloolefin polymer (COP) material with low scattering and high light transmittance, and fabricate the sealed housing through an injection molding process, so that the internal cavity of the housing precisely matches the size of the optical element group. During encapsulation, dry gas is injected into the housing to maintain a constant pressure environment, and an optical-grade sealant is coated at the joints to prevent dust and moisture from invading, thereby ensuring Figure 5 the optical path stability and imaging quality under the sealed encapsulation process.

[0131] (3) After encapsulation, use an interferometer to calibrate the resolution of the optical imaging component. By finely adjusting the position and angle of the lens, the optical resolution is made not less than the design threshold to ensure that the optical path propagation meets the preset imaging quality requirements.

[0132] S3. Perform a micron-level spatial matching between the area array detector group and the imaging focal plane of the optical imaging component, and configure an anti-interference transmission link to form a detector.

[0133] In a specific embodiment, the installation of the detector and the construction of the signal chain include the following steps:

[0134] (1) Refer to Figure 1 the module layout, fix the area array detector group at the output end of the optical imaging unit, and adjust the conjugate relationship between the photosensitive surface of the detector and the imaging focal plane of the optical imaging unit through a three-dimensional fine adjustment frame, so that the spatial alignment error between the two is controlled at the micron level, such as within ±5 μm. To ensure that the fluorescence signal processed by the optical imaging unit can be accurately received, which is in line with Figure 1 the connection relationship between the optical imaging component and the detector in

[0135] (2) Connect the detector and the image acquisition system with a low-noise shielded coaxial cable. The cable shield layer is grounded at multiple points to eliminate electromagnetic interference, and a filter circuit and a low-noise amplifier are integrated in the signal chain to filter and amplify the weak signal output by the detector.

[0136] (3) Through the excitation-detection test of standard fluorescent reagents, verify the quantum efficiency of the detector and the signal transmission fidelity to ensure that the spatial resolution and signal-to-noise ratio of the fluorescence image meet the design requirements.

[0137] S4. Construct a multi-axial displacement platform, integrate the drive component and the grating scale positioning module to obtain a three-dimensional electric stage, and establish a mechanical linkage with the optical imaging component to dynamically adjust the imaging focal plane.

[0138] Further, as Figure 6 shown, step S4 includes:

[0139] S41. Embed the grating scale positioning module in the multi-axial displacement platform base and form a closed-loop feedback control with the stepper motor of the drive component.

[0140] S42. Connect the multi-axial displacement platform with the optical imaging component through a mechanical linkage mechanism, and dynamically adjust the XYZ axial displacement according to the obtained blood vessel depth parameters to achieve synchronous matching of the spatial positioning of the detection area and the imaging focal plane.

[0141] S5. Fix the anti-glare display screen and the graphical user interface on the adjustable bracket, and deploy the operation software to achieve coordinated control of the laser parameters of the wavelength-tunable light source module, the imaging focal plane of the optical imaging component, the displacement of the three-dimensional electric stage, and the access parameters of the detector, and establish a synchronous update mechanism for the dynamic navigation layer and the imaging focal plane.

[0142] In a specific embodiment, the method for developing the image processing algorithm and constructing the display control system in the imaging device specifically includes:

[0143] (1) Collect a near-infrared second-region fluorescence image dataset of breast cancer tumor blood vessels, manually annotate the blood vessel morphological features in the images, and perform noise reduction and contrast preprocessing on the original data using the Gaussian filtering and histogram equalization algorithms; construct a blood vessel feature recognition model based on a convolutional neural network, and train through transfer learning to enable the model to automatically segment the tumor blood vessel area and generate a highlighted display map.

[0144] (2) Embed the trained blood vessel recognition algorithm into the image acquisition driver program, and build a hardware test platform including a light source module, a three-dimensional electric stage, and an optical imaging component; collect blood vessel fluorescence images at different depths by simulating a surgical scenario, synchronously trigger the light source power adjustment, stage displacement, and detector gain parameters, collect different types of breast cancer tumor blood vessel images, process and analyze the images, and obtain Figure 5 and Figure 7 the shown diagrams, verify the blood vessel recognition accuracy and system response delay of the algorithm under dynamic imaging conditions, and iteratively optimize the noise suppression coefficient in the filtering algorithm and the weight parameters of the neural network model according to the test results to ensure the efficient and stable operation of the entire image acquisition and processing system.

[0145] (3) In the design and production of the display and control platform, first, an LED liquid crystal display with high resolution, high brightness, and anti-glare function is selected for installation. According to Figure 1 the position layout of the display and control platform in Figure 1 a special display screen bracket is used to firmly fix the display screen on the shell of the display and control platform, and the angle of the display screen is ensured to be adjustable to facilitate doctors to observe images and realize the function of

[0146] (4) In the design of the operation interface, based on the ergonomic principle, a simple and intuitive graphical user interface (GUI) is designed. This operation interface is not only beautiful and easy to use, but also convenient for experimenters to Figure 1 conveniently adjust parameters such as the excitation light source power, image acquisition parameters, and image processing parameters according to the functions of each module in

[0147] (5) In the programming of the operation software, the C language is used to develop the operation software. This software realizes the convenient adjustment function of parameters such as the excitation light source power, image acquisition parameters (such as exposure time, acquisition frequency), and image processing parameters (such as noise reduction intensity, contrast enhancement multiple). By communicating with the image acquisition and processing system, the operation instructions of doctors are accurately transmitted to the corresponding modules, and the operation results are displayed in real time. This process is closely related to the Figure 1 interaction relationship between the display and control platform and other modules in

[0148] Additionally, after step S5, it also includes: mechanically strengthening each module and performing closed-loop calibration of optical / electrical signals, optimizing the imaging resolution through phantom testing, using a vascular phantom to evaluate the resolution and signal-to-noise ratio during the imaging quality test, and monitoring the temperature change of key components and optimizing the heat dissipation structure during the stability test.

[0149] Specifically, during the overall integration, it is carried out strictly in accordance with Figure 1For the module layout and connection relationships shown, first mechanically install the wavelength-tunable light source module, optical imaging component, detector, three-dimensional motorized stage, and display and control platform. Use high-strength screws and connectors to ensure a firm and reliable connection between each module, so that there will be no loosening even in a vibrating environment. When installing the optical imaging unit, pay special attention to the optical alignment accuracy between it and the light source module and detector, and use professional optical alignment equipment for calibration to ensure the accuracy of the optical path. For electrical connections, wire strictly according to the circuit design drawings, use appropriate connectors to connect each module, ensure good electrical contact and stable signal transmission. During the wiring process, classify different types of signal lines, such as analog signal lines and digital signal lines, and perform shielding treatment separately to reduce interference between signals. At the same time, reasonably layout the power supply lines to ensure that each module can obtain a stable power supply, and avoid affecting the performance of the equipment due to power fluctuations, so as to ensure that the entire imaging system can work in coordination as expected.

[0150] Secondly, use a standard test phantom (such as a phantom containing vascular simulation structures of different sizes and contrasts) to perform an imaging quality test. Place the test phantom in a position similar to the actual surgical scenario and start the imaging system for imaging. Combining Figure 1 the overall structure, determine the resolution by measuring the size of the smallest vascular simulation structure that can be resolved. For example, if the vascular structure can be clearly resolved, it indicates that the resolution of the excitation imaging collaborative system meets the design requirements. Calculate the gray-scale difference between tumor blood vessels and surrounding tissues to evaluate the contrast. The higher the contrast, the more obvious the distinction between tumor blood vessels and surrounding tissues. Calculate the signal-to-noise ratio by the ratio of the signal intensity to the noise intensity. The higher the signal-to-noise ratio, the better the image quality. During the test, change the power of the excitation light source, image acquisition parameters, etc., observe the changes in imaging quality, and find the optimal combination of imaging parameters to ensure that the imaging system can achieve Figure 1 the functional goal of high-resolution imaging

[0151] Next, let the imaging system run continuously for 48 hours for a stability test. Record the imaging quality parameters, including resolution, contrast, signal-to-noise ratio, etc., every 2 hours, and at the same time observe the operating status of the equipment, such as whether there is a system crash, abnormal images, etc. Use a temperature sensor to monitor the temperature changes of key components inside the equipment (such as the light source module, detector, processor, etc.) to ensure that during long-term operation, the component temperature will not be too high to cause performance degradation or equipment failure. Combining Figure 1 the functions of each module, analyze the data recorded during the test. If significant fluctuations in imaging quality parameters or abnormal conditions of the equipment are found, analyze the reasons and take corresponding improvement measures, such as optimizing the heat dissipation structure, adjusting the software algorithm, etc., to ensure that the imaging system can operate stably and reliably.

[0152] Furthermore, invite medical staff to perform actual operations in a simulated surgical environment to conduct an operation convenience test. Before the test, provide simple operation training for the medical staff to familiarize them with the basic functions and operation procedures of the imaging device. During the simulated surgery, record the time for the medical staff to complete various operations (such as starting the device, adjusting imaging parameters, viewing images, etc.) and the number of operation errors. At the same time, collect the feedback from the medical staff on the operation interface, such as whether the interface is friendly and whether the operation is convenient. According to the test results, combined with Figure 1 the design and functions of the display and control platform shown in, optimize the operation interface, such as adjusting the position and size of the buttons, simplifying the operation process, etc., to improve the operation convenience and better meet the needs of doctors in actual use.

[0153] Since the system / device described in the above embodiments of the present invention is the system / device adopted for implementing the method of the above embodiments of the present invention, based on the method described in the above embodiments of the present invention, those skilled in the art can understand the specific structure and variations of the system / device, and thus will not be elaborated herein. Any system / device adopted by the method of the above embodiments of the present invention falls within the scope of protection of the present invention.

[0154] Those skilled in the art should understand that the embodiments of the present invention can be provided as a method, a system, or a computer program product. Therefore, the present invention can adopt the form of a complete hardware embodiment, a complete software embodiment, or an embodiment combining software and hardware aspects. Moreover, the present invention can adopt the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) containing computer-usable program code.

[0155] The present invention is described with reference to the flowcharts and / or block diagrams of methods, apparatuses (systems), and computer program products according to embodiments of the present invention. It should be understood that each flow and / or block in the flowcharts and / or block diagrams can be implemented by computer program instructions, and the combination of flows and / or blocks in the flowcharts and / or block diagrams can also be implemented by computer program instructions.

[0156] It should be noted that in the claims, any reference signs placed between parentheses shall not be construed as limiting the claim. The word "comprising" does not exclude the presence of components or steps not listed in the claim. The word "a" or "an" preceding a component does not exclude the presence of a plurality of such components. The present invention can be implemented by means of hardware including several different components and by means of a properly programmed computer. In a claim listing several apparatuses, several of these apparatuses can be embodied by the same hardware. The use of the words first, second, third, etc. is only for convenience of expression and does not denote any order. These words can be understood as part of the component name.

[0157] In addition, it should be noted that in the description of this specification, the descriptions of terms such as "one embodiment", "some embodiments", "embodiment", "example", "specific example", or "some examples" mean that the specific features, structures, materials, or characteristics described in connection with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic expressions of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials, or characteristics described can be combined in a suitable manner in any one or more embodiments or examples. In addition, without contradiction, those skilled in the art can combine and combine the different embodiments or examples described in this specification and the features of different embodiments or examples.

[0158] Although the preferred embodiments of the present invention have been described, those skilled in the art can make additional changes and modifications after learning the basic creative concepts. Therefore, the claims should be construed to include the preferred embodiments and all changes and modifications that fall within the scope of the present invention.

[0159] Obviously, those skilled in the art can make various modifications and variations to the present invention without departing from the spirit and scope of the present invention. Thus, if these modifications and variations of the present invention fall within the scope of the claims of the present invention and their equivalent technologies, the present invention should also include these modifications and variations.

Claims

1. A near-infrared multi-imaging instrument for breast cancer tumor blood vessels, characterized in that include: The excitation imaging collaborative system includes a wavelength tunable light source module, an optical imaging component and a detector. The wavelength tunable light source module and the detector dynamically match the spectral pair of the excitation wavelength and the receiving wavelength through a closed-loop feedback mechanism; A three-dimensional electric stage is used to control the spatial positioning and field of view of the detection area through three-dimensional spatial displacement, and to dynamically adjust the imaging focal plane to match the depth of the blood vessel by linking the optical imaging component; The atlas generation module is used to perform spatiotemporal decoupling processing on the time-series fluorescence signals transmitted by the detector, and to extract the vascular morphology distribution, hemodynamic parameters and molecular typing characteristics through parallel independent calculation channels to generate a superimposed atlas of multiple imaging; The surgical navigation interface is used to display the superimposed atlas in real time and generate intraoperative marking trajectories and boundary resection paths based on the dynamic changes of vascular features in the superimposed atlas.

2. The near-infrared multi-imaging apparatus for breast cancer tumor blood vessels according to claim 1, wherein The wavelength tunable light source module includes: A light emitting element for emitting laser light in the near-infrared region II; The optical fiber coupling component includes an optical adjustment frame and a collimator. The light-emitting element is coupled and aligned with the transmission optical fiber through the optical adjustment frame. The collimating lens converts the excitation light into a collimated light beam and then transmits it to the optical imaging component in a direction; A temperature control unit, thermally coupled to the light-emitting element, suppresses wavelength drift and optical power fluctuations through active temperature control; A current modulation unit, comprising a microcontroller and a current source circuit, for dynamically adjusting a driving current of the current source circuit through a closed-loop feedback mechanism; The current modulation unit and the temperature control unit are controlled collaboratively by sharing a feedback signal, so that the spectrum of the laser wavelength and the wavelength received by the detector can be adapted in real time.

3. The near-infrared multi-imaging device for breast cancer tumor blood vessels according to claim 1, characterized in that, Optical imaging components include: The lens group of the lens barrel is arranged along the axial direction of the optical path and is used to converge the fluorescence signal of the second near-infrared zone; A dichroic mirror group is arranged at a preset inclination angle on the outgoing light path of the lens group of the lens barrel, and is used to separate the excitation light and the fluorescence signal; A filter group, which forms a multi-level background light suppression channel with a dichroic mirror group, and includes a narrow-band filter that matches the wavelength of the excitation light; A sealed housing covers the lens group, the dichroic mirror group and the filter group. The inner wall of the sealed housing is provided with an anti-reflection coating and the joints are sealed with optical grade sealant.

4. The near-infrared multi-modal breast cancer tumor blood vessel imaging apparatus according to claim 1, wherein the detector include: An array detector group is coaxially arranged with the filter group of the optical imaging assembly and is configured to receive and convert the fluorescence signal; The signal conditioning module includes a shielded cable, a filter unit, and a signal amplifier, which constitutes an interference-resistant transmission link from the photoelectric conversion to the image acquisition system; Among them, the area array detector group and the signal conditioning module adopt a modular packaging structure, and realize the time-fidelity conversion of the fluorescence signal through a synchronous trigger mechanism.

5. The near-infrared multi-modal breast cancer tumor blood vessel imaging device according to claim 1, characterized in that, The 3D motorized stage includes: The multi-axial displacement platform is composed of orthogonally distributed XYZ axial slide rails and is used to carry the samples to be tested; The drive assembly includes a stepper motor and a reduction gear set, which adjusts the axial displacement through closed-loop feedback control to achieve three-dimensional spatial positioning; The grating ruler positioning module is embedded in the displacement platform base and provides real-time feedback of position information to the optical imaging component; Among them, the displacement platform and the optical imaging component form a closed-loop control through a mechanical linkage mechanism. The driving component dynamically adjusts the displacement in response to the blood vessel depth parameter to achieve synchronous matching of the spatial positioning of the detection area and the imaging focal plane.

6. The near-infrared multi-modal breast cancer tumor blood vessel imaging device according to any one of claims 1-5, characterized in that The surgical navigation interface includes: An anti-glare display screen for real-time displaying intraoperative fluorescence images with superimposed blood vessel feature maps; A graphical interaction panel configured with hierarchical operation interfaces for adjusting the light source power, controlling the image acquisition parameters, and regulating the image processing parameters; A dynamic navigation layer that communicates with the three-dimensional electric stage and the optical imaging component, and is used to superimpose real-time positioning marks based on the blood vessel depth information, perform spatial registration of the fluorescence image and the preset blood vessel distribution model, and generate navigation guidance; Among them, the graphical interaction panel realizes dynamic parameter adjustment through touch or an external input device, and the dynamic navigation layer is updated synchronously with the change of the imaging focal plane of the optical imaging component to form a closed-loop feedback of spatial positioning and image display.

7. A preparation method of a near-infrared multi-modal imaging device for breast cancer tumor blood vessels, characterized in that, It includes: S1. In a preset clean environment, couple and align the light-emitting element with the transmission optical fiber through an optical adjustment frame to form an excitation light transmission link, and synchronously integrate a temperature control unit and a current modulation unit to form a wavelength-tunable light source module; S2. Coaxially assemble the lens barrel lens group, dichroic mirror group, and filter group through a positioning fixture into a modular optical path, and encapsulate them in a sealed housing to form an optical imaging component with multiple-stage background light suppression channels; S3. Perform micron-level spatial matching between the area array detector group and the imaging focal plane of the optical imaging component, and configure an anti-interference transmission link to form a detector; S4. Construct a multi-axial displacement platform and integrate a driving component and a grating scale positioning module to obtain a three-dimensional electric stage, and establish a mechanical linkage with the optical imaging component to dynamically adjust the imaging focal plane; S5. Fix the anti-glare display screen and the graphical interaction interface on an adjustable bracket, and deploy operation software to realize the coordinated control of the laser parameters of the wavelength-tunable light source module, the imaging focal plane of the optical imaging component, the displacement of the three-dimensional electric stage, and the access parameters of the detector, and establish a synchronous update mechanism between the dynamic navigation layer and the imaging focal plane.

8. The preparation method of the near-infrared multi-modal imaging apparatus for breast cancer tumor blood vessels according to claim 7, wherein, Step S1 includes: Couple and align the light-emitting element with the transmission optical fiber through an optical adjustment frame; Thermally couple a temperature control unit to the light-emitting element to suppress wavelength drift, and integrate a current modulation unit to dynamically adjust the driving current through a microcontroller; Cooperatively control the temperature control unit and the current modulation unit through a shared feedback signal to make the excitation light wavelength match the detector receiving wavelength in real time.

9. The preparation method of the near-infrared multi-modal imaging device for breast cancer tumor blood vessels according to claim 7, wherein, Step S2 includes: Arrange the lens barrel lens group, dichroic mirror group, and filter group coaxially at a preset inclination angle to form multiple-stage background light suppression channels; Use a sealed housing with an anti-reflection coating to cover the lens barrel lens group, dichroic mirror group, and filter group, inject dry gas to maintain a constant pressure environment, and use optical-grade sealant to seal the joints; After encapsulation, calibrate the optical resolution with an interferometer to not be lower than a preset threshold.

10. The preparation method of the near-infrared multi-modal imaging device for breast cancer tumor blood vessels according to claim 7, characterized in that, Step S4 includes: Embed a grating scale positioning module in the base of the multi-axial displacement platform, and form a closed-loop feedback control with the stepping motor of the driving component; Connect the multi-axial displacement platform and the optical imaging component through a mechanical linkage mechanism, and dynamically adjust the XYZ axial displacement amount in response to the acquired blood vessel depth parameter to achieve synchronous matching of the spatial positioning of the detection area and the imaging focal plane.

Images