WO2018176699A1 - 共轭聚合物纳米探针及其制备方法和应用 - Google Patents

共轭聚合物纳米探针及其制备方法和应用 Download PDF

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WO2018176699A1
WO2018176699A1 PCT/CN2017/094222 CN2017094222W WO2018176699A1 WO 2018176699 A1 WO2018176699 A1 WO 2018176699A1 CN 2017094222 W CN2017094222 W CN 2017094222W WO 2018176699 A1 WO2018176699 A1 WO 2018176699A1
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conjugated polymer
nanoprobe
polymer nanoprobe
fluorescent
infrared
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French (fr)
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熊丽琴
操凤文
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Shanghai Jiao Tong University
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Shanghai Jiao Tong University
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Definitions

  • the present invention relates to the field of molecular imaging, and in particular to a conjugated polymer nanoprobe, and a preparation method and application thereof, especially in a lymph node metastasis tumor model, by near-infrared fluorescence imaging, photoacoustic imaging, magnetic resonance imaging, The application of targeted imaging of lymph nodes with tumor metastasis.
  • Lymph node metastasis is a common metastasis method for most primary tumors, such as breast cancer, lung cancer, stomach cancer, esophageal cancer, thyroid cancer, cervical cancer, ovarian cancer, colorectal adenocarcinoma, pancreatic cancer, and laryngeal cancer. . Lymph node staging is an important factor in determining the treatment plan and prognosis of most primary tumors. It is of great clinical significance to accurately assess the extent of preoperative lymphatic metastasis. However, currently available probes for detecting lymphatic metastasis (eg, ICG) and imaging methods (eg, PET/CT, magnetic resonance, ultrasound, etc.) are not yet effective in identifying normal lymph nodes and lymph nodes where tumor metastasis occurs.
  • lymphatic metastasis eg, ICG
  • imaging methods eg, PET/CT, magnetic resonance, ultrasound, etc.
  • Molecular imaging is the use of imaging methods to study the normal or pathological molecular processes in cells under in vivo conditions, reflecting physiological and pathological changes at the molecular or cellular level, in vivo monitoring of disease processes, gene therapy in vivo, In vivo evaluation and functional study of functional molecules in vivo provide new techniques, with non-invasive, real-time, in vivo, fine imaging, highly sensitive, highly specific and so on.
  • Molecular imaging uses a variety of imaging methods to image specific targets in the body, the core of which is the design of molecular probes.
  • Molecular imaging methods mainly include radionuclide imaging, magnetic resonance imaging, optical imaging, ultrasound imaging, and photoacoustic imaging. Each imaging modality has its advantages and limitations.
  • fluorescence imaging has high sensitivity, relatively low price, and convenient operation, but its penetration depth is limited.
  • Radionuclide imaging and magnetic resonance imaging have no limits on depth, but the sensitivity of magnetic resonance imaging is low and the spatial resolution of radionuclide imaging is low.
  • the information acquired by single modal imaging is limited and does not reflect the complexity and specificity of the organism. Therefore, the fusion of multimodal molecular imaging and the construction of multimodal molecular probes complement each other, which can provide more accurate and reliable biomedical research. Image information.
  • Fluorescent conjugated polymers act as a fluorescent probe with unique photophysical and photochemical properties.
  • Swager et al. of the Massachusetts Institute of Technology reported for the first time that fluorescent conjugated polymers have a ⁇ - ⁇ * conjugated molecular wire structure that can amplify the fluorescence response signal by a factor of 100. This finding makes fluorescent conjugated polymers widely available. It is widely used for the detection of biological macromolecules such as nucleic acids and proteins, and small molecules such as ATP and glucose.
  • Fluorescent conjugated polymers have some advantages compared with traditional small molecule fluorescent compounds due to their ⁇ - ⁇ * conjugated molecular wire structure: (1) good stability; (2) conjugated polymer electronic structure, fluorescence emission wavelength It can be adjusted by changing and modifying the chemical structure; (3) The response signal can be amplified by a hundred times without changing the binding constant, thereby improving the sensitivity of detection.
  • the fluorescent conjugated polymer does not contain any toxic metal elements and is less toxic than semiconductor quantum dots. Therefore, in recent years, the application of fluorescent conjugated polymers in the field of molecular imaging has also attracted the attention of researchers.
  • the technical problem to be solved by the present invention is to provide a conjugated polymer nanoprobe and preparation thereof. Methods and applications.
  • a first aspect of the present invention provides a conjugated polymer nanoprobe.
  • the conjugated polymer nanoprobe comprises:
  • the surface ligand is located on the surface of the conjugated polymer nanoprobe
  • the target molecule is located on the surface of the conjugated polymer nanoprobe
  • the near red fluorescent external dye is located inside the conjugated polymer nanoprobe.
  • the surface ligand function is to increase the biocompatibility of the probe, and the carboxyl group provided can be further coupled with the antibody/protein or the like.
  • the target molecule is used to bind to a receptor or the like on the tumor cell to form a binding of the probe to the tumor cell.
  • the target molecule recognizes the folate receptor.
  • the target molecule is a phospholipid modified target molecule.
  • the phospholipids are modified to be modified using liposomes.
  • the phospholipid modified target molecule is one of phosphatidylethanolamine-polyethylene glycol 5000-folic acid cross-linking, phosphatidylethanolamine-polyethylene glycol 2000-folate cross-linking and phosphatidylethanolamine-folate cross-linking.
  • phosphatidylethanolamine-polyethylene glycol 5000-folic acid cross-linking phosphatidylethanolamine-polyethylene glycol 2000-folate cross-linking
  • phosphatidylethanolamine-folate cross-linking kind or more.
  • the surface ligand is a terminal ligand modified with a terminal carboxyl group. Further, the surface ligand is selected from the group consisting of benzene Ethylene-polyethylene glycol-carboxyl (PS-PEG-COOH), polyethylene glycol-carboxyl (PEG-COOH), styrene-maleic anhydride copolymer (PSMA) or a combination thereof.
  • PS-PEG-COOH benzene Ethylene-polyethylene glycol-carboxyl
  • PEG-COOH polyethylene glycol-carboxyl
  • PSMA styrene-maleic anhydride copolymer
  • the absorption wavelength of the near-infrared fluorescent dye is between 700 and 900 nm.
  • the near infrared fluorescent dye is selected from the group consisting of NIR775, DiIC18, ICG, Cy7 or Cy7.5.
  • the fluorescent conjugated polymer is selected from the group consisting of PFBT or MEH-PPV.
  • the weight ratio of the near-infrared fluorescent dye to the fluorescent conjugated polymer is between 0.2% and 1.2%, and the weight ratio of the surface ligand to the fluorescent polymer is between 0.5 and 2, and the weight of the target molecule and the fluorescent polymer.
  • the ratio is between 0.2-1.
  • the transmission electron microscopy of the conjugated polymer nanoprobe as described above showed an average particle size distribution of 2 to 100 nm.
  • the transmission electron microscopy of the conjugated polymer nanoprobe as described above exhibits an average particle size distribution of 20 to 60 nm.
  • the conjugated polymer nanoprobe further comprises a krypton-containing magnetic resonance contrast agent.
  • the krypton-containing magnetic resonance contrast agent is located on the surface of the conjugated polymer nanoprobe.
  • the krypton-containing magnetic resonance contrast agent is a phospholipid-modified hydrazine.
  • the phospholipid-modified hydrazine is a phospholipid-modified fluorene diethylenediamine pentaacetic acid complex (DTPA) selected from the group consisting of DTPA-BSA (Gd), bis (18:0 PE)-DTPA (Gd), bis (16) :0PE)-DTPA(Gd), bis(14:0PE)-DTPA(Gd), 18:0PE-DTPA(Gd), 16:0PE-DTPA(Gd) or a combination thereof.
  • DTPA fluorene diethylenediamine pentaacetic acid complex
  • the weight ratio of the near-infrared fluorescent dye to the fluorescent conjugated polymer is between 0.2% and 1.2%, and the weight ratio of the surface ligand to the fluorescent conjugated polymer is between 0.5 and 2, and the target molecule is conjugated to the fluorescent substance.
  • the weight ratio of the polymer is between 0.2 and 1, and the weight ratio of the krypton-containing magnetic resonance contrast agent to the fluorescent polymer is between 3-5.
  • transmission electron microscopy of the above conjugated polymer nanoprobe showed an average particle size distribution of 20 to 130 nm.
  • the transmission electron microscopy of the above conjugated polymer nanoprobe shows an average particle size distribution of 30 to 60 nm.
  • a second aspect of the present invention provides a method for preparing a conjugated polymer nanoprobe.
  • the conjugated polymer nanoprobe is a krypton-free magnetic resonance contrast agent as described above.
  • Conjugated polymer nanoprobes, the method comprising:
  • the conjugated polymer nanoprobe is a conjugated polymer nanoprobe containing a krypton magnetic resonance contrast agent as described above, in the step 1) of the method as described above, in organic
  • the krypton-containing magnetic resonance contrast agent is also added to the solvent.
  • the target molecule is a phospholipid modified target molecule.
  • the krypton-containing magnetic resonance contrast agent is a phospholipid-modified hydrazine.
  • step 2) the power of the ultrasound is set to 8-12%, the ultrasound is stopped for 2-4 seconds every 4-6 seconds, and the ultrasonic time is set to 50-70 seconds.
  • the power of the ultrasound is set to 10%, the pause is 3 seconds per 5 seconds of ultrasound, and the ultrasound time is set to 1 minute.
  • the weight ratio of the krypton-containing magnetic resonance contrast agent to the fluorescent polymer is between 3-5.
  • the organic solvent in the step 1) is a tetrahydrofuran solution or chloroform.
  • the weight ratio of the near-infrared fluorescent dye to the fluorescent conjugated polymer is between 0.2 and 1.2%, and the weight ratio of the surface ligand to the fluorescent conjugated polymer is between 0.5 and 2, and the target molecule
  • the weight ratio to the fluorescent conjugated polymer is between 0.2 and 1.
  • the method further comprises: 3) volatilizing the organic solvent under heating to obtain a conjugated polymer nanoprobe.
  • the heating condition is at 45 to 55 °C. Preferably, it is 50 °C.
  • a third aspect of the invention provides the use of a conjugated polymer nanoprobe for the preparation of a molecular imaging reagent.
  • the conjugated polymer nanoprobe is a conjugated polymer nanoprobe containing no osmium magnetic resonance contrast agent as described above, and the conjugated polymer nanoprobe can perform near infrared fluorescence imaging And / or photoacoustic imaging.
  • the conjugated polymer nanoprobe is a conjugated polymer nanoprobe containing a krypton magnetic resonance contrast agent as described above, the conjugated polymer nanoprobe capable of near infrared fluorescence imaging , photoacoustic imaging and / or magnetic resonance imaging.
  • the above conjugated polymer nanoprobe can target tumor cells expressed by folate receptor at the cellular level.
  • the above conjugated polymer nanoprobe can recognize lymph nodes and normal lymph nodes where tumor metastasis occurs.
  • the above conjugated polymer nanoprobe can recognize lymph nodes and normal lymph nodes in which tumor metastasis occurs at a living level of small animals.
  • a fourth aspect of the invention provides a molecular imaging reagent.
  • the molecular imaging reagent comprises a conjugated polymer nanoprobe as described above.
  • a fifth aspect of the invention provides the use of a conjugated polymer nanoprobe for the preparation of a photodynamic therapeutic agent.
  • the conjugated polymer nanoprobe is as described above.
  • the conjugated polymer nanoprobe comprises a near-infrared fluorescent dye capable of generating active oxygen under illumination.
  • the near-infrared fluorescent dye is a near-infrared dye containing a tetrapyrrolyl structure.
  • the near infrared fluorescent dye is NIR775.
  • a sixth aspect of the invention provides a photodynamic therapeutic agent.
  • the photodynamic therapeutic agent comprises a conjugated polymer nanoprobe as described above.
  • the conjugated polymer nanoprobe comprises a near-infrared fluorescent dye capable of generating active oxygen under illumination.
  • the near-infrared fluorescent dye is a near-infrared dye containing a tetrapyrrolyl structure.
  • the near infrared fluorescent dye is NIR775.
  • the photodynamic therapeutic agent can be used for tumor photodynamic therapy.
  • the photodynamic therapeutic agent can kill tumor cells at the cellular level and at the level of small animals.
  • the tumor is a subcutaneous solid tumor.
  • the hybrid fluorescent conjugated polymer nanoprobe of the invention has multi-modal imaging and folate receptor targeting function, and can target tumor cells expressed by folate receptor at the cell level; in the lymphatic metastasis tumor model, It can effectively identify metastatic lymph nodes and normal lymph nodes, and has a long residence time in metastatic lymph nodes, which can meet the needs of long-term observation and detection.
  • the synthetic hybrid fluorescent conjugated polymer nanoprobe is prepared according to the method of the invention, and the lymph node metastasis tumor model can effectively identify the lymph node with tumor metastasis, and the specific targeted imaging effect on lymph node metastasis can reach or exceed The level of similar products is currently known.
  • the one-step synthesis is carried out by the coprecipitation method, and the synthesis process is simple and efficient. Since the target molecule and the krypton-containing magnetic resonance contrast agent are both phospholipid-modified, after cross-linking, the cross-linking property with the fluorescent conjugated polymer is good, the cross-linking is stable, and the leakage of small molecules from the nano-probe is avoided. In this case, therefore, the conjugated polymer nanoprobe can be synthesized in a one-step process. In addition, after ultrasonication, the surface ligand coats the entire nanoprobe tighter, further preventing leakage of small molecules, improving the stability of the entire nanoprobe, and contributing to the storage stability of the nanoprobe.
  • the hybrid fluorescent conjugated polymer nanoprobe of the present invention combines near-infrared fluorescence imaging, photoacoustic imaging and magnetic resonance imaging with bimodal or trimodal molecular imaging techniques to achieve targeted imaging of metastatic lymph nodes at the living level of small animals. It can be used for imaging-mediated surgical navigation, implementation of removal of metastatic lymph nodes, and improved resection rate.
  • the near-infrared fluorescently doped conjugated polymer nanoprobe of the invention can generate active oxygen under illumination, and can be used for photodynamic therapy of tumors, especially subcutaneous solid tumors. Moreover, the conjugated polymer nano-probe has good effect and low cytotoxicity, and has great application prospect in photodynamic therapy.
  • FIG. 1 is a schematic view showing the mechanism of a fluorescent conjugated polymer nanoprobe in an embodiment of the present invention.
  • FIG. 2 is a schematic view of the mechanism of a fluorescent conjugated polymer nanoprobe in another embodiment of the present invention.
  • Figure 3 is a schematic illustration of probe preparation in Example 1.
  • Figure 5 is a schematic illustration of probe preparation in Example 2.
  • Figure 6 is an electron micrograph of the probe of Example 2.
  • Figure 7 is a near infrared fluorescence spectrum of a NIR775 hybrid PFBT fluorescent conjugated polymer nanoprobe.
  • Figure 8 is a near infrared fluorescence spectrum of a NIR775 hybridized MEH-PPV fluorescent conjugated polymer nanoprobe.
  • Figure 9 is an in vitro photoacoustic imaging of a NIR775 hybrid PFBT fluorescent conjugated polymer nanoprobe.
  • Figure 10 is an in vitro magnetic resonance imaging of NIR775, Gd 3+ hybrid PFBT fluorescent conjugated polymer nanoprobe.
  • Figure 11 is a flow cytometric diagram of folate receptor expression in human glioma U87MG cells, human ovarian cancer SKOV 3 cells, human lung cancer NCI-H292 (lymph node metastasis) cells, and human cervical cancer HeLa cells.
  • Figure 12 is a NCI-H292 cytotoxicity of a hybrid fluorescent conjugated polymer nanoprobe.
  • Figure 13 is HeLa cytotoxicity of hybrid fluorescent conjugated polymer nanoprobes.
  • Figure 14 is a targeted imaging of NCI-H292 and HeLa cells of hybrid fluorescent conjugated polymer nanoprobes.
  • Figure 15 is a flow chart of NCI-H292 of a hybrid fluorescent conjugated polymer nanoprobe.
  • Figure 16 is a HeLa flow cytogram of a hybrid fluorescent conjugated polymer nanoprobe.
  • Figure 17 shows the detection of reactive oxygen species in a solution state of a PFBT near-infrared fluorescent nanoprobe having a molecular weight of 10,000 to 20,000 hybridized with NIR775.
  • Figure 18 shows the detection of reactive oxygen species in a solution state of a NIR775 hybrid PFBT near-infrared fluorescent nanoprobe having a molecular weight of 47,000.
  • Figure 19 is a comparison of the production efficiency of active oxygen in solution state of different molecular weight PFBT near-infrared fluorescent nanoprobes hybridized with NIR775.
  • Figure 20 is a diagram showing the detection of reactive oxygen species and apoptosis in NCI-H292 cells of hybrid fluorescent conjugated polymer nanoprobes.
  • Figure 21 shows the detection of reactive oxygen species and apoptosis in HeLa cells of hybrid fluorescent conjugated polymer nanoprobes.
  • Figure 22 is the photodynamic toxicity of NCI-H292 cells of hybrid fluorescent conjugated polymer nanoprobes.
  • Figure 23 is a photodynamic toxicity of HeLa cells of a hybrid fluorescent conjugated polymer nanoprobe.
  • Figure 24 is a growth curve of in vivo photodynamically treated NCI-H292 tumors of hybrid fluorescent conjugated polymer nanoprobes.
  • Figure 25 is a graph showing changes in body weight of in vivo photodynamically treated NCI-H292 tumor mice with hybrid fluorescent conjugated polymer nanoprobes.
  • Figure 26 is a photodynamic therapy of NCI-H292 tumor with hybrid fluorescent conjugated polymer nanoprobe Tissue H&E staining of NCI-H292 tumor mice.
  • Figure 27 is an H&E staining of NCI-H292 tumor tissue.
  • Figure 28 is an H&E staining of normal lymph nodes.
  • Figure 29 is an H&E staining of AX lymph nodes where NCI-H292 tumor metastasis occurs.
  • Figure 30 is an H&E staining of PO lymph nodes where NCI-H292 tumor metastasis occurs.
  • Figure 31 is an H&E staining of SC lymph nodes where NCI-H292 tumor metastasis occurs.
  • Figure 32 is an H&E staining of IN lymph nodes where NCI-H292 tumor metastasis occurs.
  • Figure 33 is a VEGF staining of AX lymph nodes where NCI-H292 tumor metastasis occurs.
  • Figure 34 is a VEGF staining of PO lymph nodes where NCI-H292 tumor metastasis occurs.
  • Figure 35 is a VEGF staining of SC lymph nodes where NCI-H292 tumor metastasis occurs.
  • Figure 36 is a VEGF staining of IN lymph nodes where NCI-H292 tumor metastasis occurs.
  • Figure 37 is an in vivo NIR fluorescence imaging (NCI-H292 tumor model) of lymph node metastasis of a hybrid fluorescent conjugated polymer nanoprobe (7.5 ⁇ g).
  • Figure 38 is an in vivo near-infrared fluorescence imaging (NCI-H292 tumor model) of lymph node metastasis of a hybrid fluorescent conjugated polymer nanoprobe (15 ⁇ g).
  • Figure 39 is an in vivo near-infrared fluorescence imaging (NCI-H292 tumor model) of lymph node metastasis of a hybrid fluorescent conjugated polymer nanoprobe (170 ⁇ g).
  • Figure 40 is a photoacoustic imaging of lymph node metastasis of a hybrid fluorescent conjugated polymer nanoprobe. Red represents the photoacoustic signal of HbO 2 and green represents the photoacoustic signal of the nanoprobe (NCI-H292 tumor model).
  • Figure 41 is a photoacoustic imaging of lymph node metastasis of a hybrid fluorescent conjugated polymer nanoprobe. Green represents the photoacoustic signal of the nanoprobe (NCI-H292 tumor model).
  • Figure 42 is an in vivo magnetic resonance imaging (NCI-H292 tumor model) of lymph node metastasis of a hybrid fluorescent conjugated polymer nanoprobe.
  • Figure 43 is an isolated near-infrared fluorescence image (NCI-H292 tumor model) of lymph node metastasis of a hybrid fluorescent conjugated polymer nanoprobe.
  • Figure 44 is a magnetic resonance and in vitro near-infrared fluorescence imaging (NCI-H292 tumor model) of lymph node metastasis of hybrid fluorescent conjugated polymer nanoprobes. T represents a tumor.
  • Figure 45 is an in vivo NIR fluorescence imaging (HeLa tumor model) of lymph node metastasis of a hybrid fluorescent conjugated polymer nanoprobe.
  • DSPE-PEG (5000) Folate phosphatidylethanolamine-polyethylene glycol 5000-folic acid cross-linking
  • PE-Folate phosphatidylethanolamine-folate cross-linking
  • PS-PEG-COOH styrene-polyethylene glycol-carboxyl
  • PEG-COOH polyethylene glycol-carboxyl
  • PSMA a styrene-maleic anhydride copolymer
  • MEH-PPV poly[2-methoxy-5-(2'-ethylhexyloxy)-1,4 phenylvinylene]
  • ADMA 9,10-fluorenyl-bis(methylene)dimalonic acid
  • DCFH-DA 2',7'-dichlorofluorescein diacetate
  • AX axillary lymph nodes
  • PO axillary lymph node
  • SC hip lymph nodes
  • the raw materials used in this article can be purchased directly without special instructions.
  • the near-infrared fluorescent dyes NIR775, DiIC18, ICG, Cy7 or Cy7.5 are commercially available and can be purchased directly.
  • One aspect of the invention provides a fluorescent conjugated polymer nanoprobe having a structure as shown in Figure 1 or Figure 2.
  • the fluorescent conjugated polymer nanoprobe as shown in FIG. 1 includes a fluorescent conjugated polymer; a surface ligand; a target molecule; a near-infrared fluorescent dye.
  • the fluorescent conjugated polymer nanoprobe as shown in FIG. 2 includes a fluorescent conjugated polymer; a surface ligand; a target molecule; a near-infrared fluorescent dye, and a krypton-containing magnetic resonance contrast agent.
  • the fluorescent conjugated polymer may be PFBT and MEH-PPV of different molecular weights
  • Target molecules include DSPE-PEG (5000) Folate, DSPE-PEG (2000) Folate, PE-Folate or a combination thereof;
  • Surface ligands include PS-PEG-COOH, PEG-COOH, PSMA or a combination thereof;
  • Gd 3+ magnetic resonance contrast agent containing strontium
  • Gd 3+ magnetic resonance contrast agent containing strontium
  • DTPA-BSA DTPA-BSA
  • Gd bis (18:0PE)-DTPA
  • Gd bis (16:0PE)-DTPA
  • Gd bis (14:0PE)- DTPA
  • Gd 18:0PE-DTPA
  • Gd 16:0 PE-DTPA
  • Gd magnetic resonance contrast agent containing strontium
  • the molecular weight of PFBT ranges from 10,000 to 52,000.
  • the monomer structure of MEH-PPV is:
  • MEH-PPV has a molecular weight ranging from 10,000 to 200,000.
  • NIR775 The structural formula of NIR775 is:
  • the molecular weight of the PS moiety is 6500 to 21700 Da; and the molecular weight of the PEG moiety is 1200 to 4600 Da.
  • the molecular weight of PEG ranges from 2,000 to 5,000.
  • Another aspect of the invention provides a method of preparing a conjugated polymer nanoprobe. It is prepared by coprecipitation method, which comprises fluorescent conjugated polymer, near-infrared fluorescent dye, target molecule and surface ligand, or fluorescent conjugated polymer, near-infrared fluorescent dye, target molecule, surface ligand and strontium-containing magnetic
  • a mixed solution of a resonance contrast agent in an organic solvent such as tetrahydrofuran is rapidly added to water to form a conjugated polymer nanoprobe under ultrasonic conditions.
  • a further aspect of the invention provides the use of a conjugated polymer nanoprobe as described above.
  • the conjugated polymer nanoprobe shown in Figure 1 can perform near-infrared fluorescence imaging and/or photoacoustic imaging.
  • the conjugated polymer nanoprobe shown in Figure 2 can perform near-infrared fluorescence imaging, photoacoustic imaging, and / or magnetic resonance imaging.
  • the above two conjugated polymer nanoprobes can target tumor cells expressed by folate receptor at the cell level, and can recognize metastatic lymph nodes and normal lymph nodes, especially lymph nodes and normal lymph nodes that recognize tumor metastasis at the level of small animals. .
  • Yet another aspect of the invention provides a molecular imaging reagent comprising a conjugated polymer nanoprobe as described above.
  • Photodynamic therapy refers to the introduction of photosensitizer into the human body. After a certain period of time, the lesion is irradiated with light of a specific wavelength. Through a series of photochemical and photobiological reactions, singlet oxygen and/or free radicals are generated with the participation of molecular oxygen. Oxidation destroys various biological macromolecules in tissues and cells, causing irreversible damage to cells that are abnormally proliferating and active, and eventually killing the cells for therapeutic purposes.
  • Yet another aspect of the invention provides a photodynamic therapeutic agent comprising a conjugated polymer nanoprobe as described above.
  • the photodynamic therapeutic agent comprises a near-infrared fluorescent dye that produces reactive oxygen species under illumination.
  • the conjugated polymer nanoprobe has lower toxicity or no toxicity.
  • the above reaction scheme is shown in Fig. 5.
  • the particle size distribution of the prepared NIR775 and Gd 3+ hybridized near-infrared fluorescent conjugated polymer nanoprobes is shown in Fig. 6.
  • the transmission electron microscope showed an average particle size distribution of about 50 nm.
  • the THF in the solution was volatilized by blowing nitrogen at 50 ° C for about 25 minutes to obtain a NIR775 hybrid fluorescent conjugated polymer nanoprobe.
  • the prepared NIR775 hybrid fluorescent conjugated polymer nanoprobe showed a mean particle size distribution of 20-30 nm by transmission electron microscopy.
  • the THF in the solution is volatilized by blowing nitrogen at 50 ° C for about 25 minutes to obtain a NIR775, Gd 3+ hybridized near-infrared fluorescent conjugated polymer nanoprobe.
  • the prepared NIR775 and Gd 3+ hybridized near-infrared fluorescent conjugated polymer nano-probes showed a mean particle size distribution of 40-50 nm by transmission electron microscopy.
  • the experimental instrument adopts Edinburgh LFS-920 fluorescence spectrometer, fluorescence excitation spectrum scanning parameter setting: receiving wavelength 776nm, excitation band 350-750nm; fluorescence emission spectrum scanning parameter setting: excitation wavelength 465nm, receiving band 500-850nm; scanning interval is set to 2nm,
  • the slit has a width of 5 nm, 5 nm, and a voltage of 400V.
  • the PFBT near-infrared fluorescent nanoprobe solution with a concentration of 31.25, 62.5, 125, 250 and 500 ⁇ g/mL of NIR775 doped with 0.6 wt% was sequentially added to a polyvinyl chloride plastic tube, and pure water was used as a control group.
  • the intensity of the photoacoustic signal and the photoacoustic imaging picture of the solution were measured under excitation at 770 nm. Photoacoustic imaging was performed using the MSOT real-time scanner (MSOT inVision 128) from iThera Medical, Germany.
  • a 20 mL sample of erbium-doped magnetic resonance contrast agent (using DTPA-BSA (Gd) as an example) was centrifuged at 4500 rpm for 3-4 minutes using a 100 K superconducting tube, and then diluted to a concentration of 1/1/ of the original concentrated sample. 2, 1/4, 1/8 and 1/16 times.
  • 1 mL of the above different concentrations of the sample were placed in a 2 mL EP tube, and the sample was placed in a medium-sized nuclear magnetic resonance analysis and imaging system with a magnetic field strength of 0.55 T to collect a sample MRI cross-sectional image to complete a T 1 -weight image.
  • the T 1 weighted imaging effect was measured by the MesoMR23-060H-I medium-sized nuclear magnetic resonance analysis and imaging system, manufactured by Shanghai Newmai Electronic Technology Co., Ltd., with a resonance frequency of 23.315 MHz, a magnet strength of 0.55 T, a coil diameter of 60 mm, and a magnet temperature of 32 °C.
  • U87MG cells in the logarithmic growth phase SKOV 3 cells, NCI-H292 cells and HeLa cells were digested with trypsin to prepare a monodisperse cell suspension, and the cells were counted using a cell counting plate, and the same number was The cells were seeded in a six-well plate (1 ⁇ 10 6 cells/well), cultured in a folate-free 1640 medium containing 1% of the double antibody and 10% serum, and incubated at 37 ° C, 5% CO 2 for 12 hours.
  • the old culture solution was removed, 2 mL of PBS buffer was added, 5 ⁇ L of Mov18 (1:400) was added to the experimental group, and the cells were incubated for 30 min at 37 ° C to allow the cells to fully bind to the antibody;
  • the cells were washed 3 times with PBS, unbound antibody was removed, 2 mL of PBS buffer was added, 10 ⁇ L of Anti-mouse IgG with FITC (1:200) was added, and the cells were incubated at 37 ° C for 20 min. Finally, the cells were washed 3 times with PBS.
  • the digested cells were dispersed in 500 ⁇ L of PBS. Cells that did not receive antibody treatment served as a control group.
  • the cells of the control group and the experimental group were detected by flow cytometry, and 1 ⁇ 10 4 cells were collected for analysis.
  • the excitation wavelength was 488 nm
  • the receiving wavelength was 515 nm
  • the bandwidth was 20 nm.
  • the collected data was analyzed using BD Accuri C6 software.
  • RESULTS Specifically, we can participate in Figure 11, which shows that human glioma U87MG cells are negative for folate receptor; human ovarian cancer SKOV 3 cells, human lung cancer NCI-H292 (lymph node metastasis) cells, and human cervical cancer HeLa cells Folate receptors are positive, and HeLa cells have high expression of folate receptors.
  • the CCK-8 kit was used to evaluate near-infrared fluorescent conjugated polymer nanoprobes (using PFBT NPs as an example) and folate-functionalized near-infrared fluorescent conjugated polymer nanoprobes (with FA-PFBT NPs as an example) and Toxicity of Gd 3+ and folate-functionalized near-infrared fluorescent conjugated polymer nanoprobes, exemplified by Gd-FA-PFBT NPs.
  • the specific experimental steps are as follows:
  • NCI-H292 cells and HeLa cells in the logarithmic growth phase were digested with trypsin to prepare a monodisperse cell suspension, and the cells were counted using a cell counting plate, and then the cell suspension was diluted to 50 000 / mL. 100 ⁇ L of the cell suspension (5 ⁇ 10 3 /well) was inoculated into a 96-well plate, and 100 ⁇ L of normal cell-free medium was added to the control group, and incubated at 37 ° C, 5% CO 2 for 12 hours.
  • each probe solution to be tested was sequentially added to each well containing the cells, and the final probe concentrations were 0, 5, 25, 50 and 100 ⁇ g/mL, respectively, and incubated at 37 ° C for 24 h.
  • the old culture medium in the 96-well plate was removed, and the cells were gently washed twice with PBS, and a pre-formulated 110 ⁇ L of a mixed solution of CCK-8 and the culture solution was added to each well, wherein CCK-8
  • the volume ratio to the culture solution was 1:10, and incubation was carried out for 2 hours at 37 ° C.
  • the OD value of the 96-well plate at 450 nm was measured with a microplate reader.
  • cell viability* (%) [A (dosing) - A (blank)] / [A (0 dosing) - A (blank)] ⁇ 100.
  • a (dosing) refers to the absorbance of a well having cells, a CCK-8 solution and a probe solution
  • a (blank) refers to the absorbance of a well having a medium and a CCK-8 solution without cells
  • a (0 plus Drug) refers to the absorbance of a well having a cell, a CCK-8 solution, and no probe solution.
  • the setting parameters of the laser confocal microscope are: BFBT excitation PFBT, receiving channel at 520-560nm; for NIR775, 458nm excitation, receiving channel at 750nm-800nm; for DAPI, 405nm excitation, signal receiving wavelength is 450nm-480nm.
  • cells were also seeded into six-well plates (1 ⁇ 10 6 cells/well) and cultured in serum-free 1640 medium at 37 ° C, 5% CO 2 . Incubate for 12 h. After the cells were attached, remove the old culture medium, add 1 mL of fresh serum-free 1640 medium, and then add 20 ⁇ g of PFBT polymer fluorescent nanoprobe and phospholipid folic acid-doped PFBT polymer fluorescent nanoprobe at 37 ° C. Incubate for 24 h at 5% CO 2 .
  • the cells were washed three times with PBS to remove the nano-probes dissolved in the solution, and the digested cells were dispersed in 500 ⁇ L of PBS, and then the cells of the control group and the experimental group were detected by flow cytometry, and 1 ⁇ was collected. 10 4 cells were analyzed.
  • the excitation wavelength was 488 nm
  • the PFBT receiving wavelength was 515 nm
  • the bandwidth was 20 nm.
  • the NIR775 receiving wavelength was 670 LP filter
  • the collected data was analyzed by BD Accuri C6 software.
  • NIR775-doped PFBT near-infrared fluorescent nanoprobe 1 mL was mixed with 25 ul of the above ADMA/PBS solution, diluted with water to 2.5 mL, and finally contained 20 ug/mL Pdots, 5 ug/mL ADMA.
  • the mixed solution was irradiated with a light source of 460 nm and 100 mW/cm 2 , and the ultraviolet absorption spectrum of the solution was characterized by an ultraviolet spectrophotometer at different times until the absorption spectrum of the solution did not change.
  • a pure solution containing no AFM (5 ug/mL) containing no near-infrared fluorescent nanoprobe was used as a reference and irradiated for the same time under the same light intensity.
  • PFBT polymer fluorescent nanoprobes with a molecular weight of 10,000-20000, irradiate once every 1 min for a total irradiation time of 12 min; for a PFBT polymer fluorescent nanoprobe with a molecular weight of 47,000, irradiate every 1 min from 0 to 10 min. From 10 to 40 minutes, every 5 minutes, the total irradiation time is 40 minutes.
  • the UV absorption intensity of PFBT near-infrared fluorescent nanoprobe with a molecular weight of 10 000-20000 at 261 nm is greater than that of PFBT with near molecular weight of 47000 at the same illumination time.
  • the change in UV absorption intensity at 261 nm is up to 10 min, and for PFBT near-infrared fluorescent nanoprobes with a molecular weight of 47,000, it takes 25 min.
  • the PFBT near-infrared fluorescent nanoprobe having a molecular weight of 10,000-20000 produces singlet oxygen and the efficiency of producing singlet oxygen is higher than that of the PFB near-infrared fluorescent nanoprobe having a molecular weight of 47,000.
  • NCI-H292 cells and HeLa cells in the same logarithmic growth phase were digested and inoculated into confocal glass dishes (4 ⁇ 10 4 cells/dish), and cultured in serum 1640 culture medium. After that, remove the old culture solution, add 1 mL of fresh serum-free 1640 medium, and add 0 or 20 ⁇ g of phospholipid folate-doped PFBT (molecular weight 10000-20000) near-infrared fluorescent nanoprobe at 37 ° C, 5 Under the condition of %CO 2 , the cells were co-cultured for 24 hours.
  • phospholipid folate-doped PFBT molecular weight 10000-20000
  • the old medium was removed, the cells were washed three times with PBS, the nanoparticles not phagocytized by the cells were removed, and 1 mL of fresh serum-free 1640 medium was added.
  • a 460 nm, 50 mW/cm 2 LED light source cells with nanoprobes were continuously irradiated for 20 minutes, cells with nano-probes but without light, and cells without photodetectors but for 20 minutes were added.
  • As a control group As a control group.
  • Intracellular singlet oxygen detection Weigh 3.5 mg of DCFH-DA, dissolve it in 721 ⁇ L of ethanol (10 mM), dilute to 1.0 mM with serum-free medium, and then dilute the 1.0 mM solution to 10 ⁇ M with serum-free medium. Just use it. The irradiated cells were stained with 10 ⁇ M DCFH-DA solution for 20 minutes in the dark, then gently washed three times with PBS, and subjected to laser confocal microscopy for cell imaging. Adopt 488nm The DCFH-DA is excited and the receiving channel is at 510-520 nm.
  • Apoptosis detection Weigh 1 mg of PI dissolved in 10 mL of PBS solution to obtain 100 ⁇ g/mL PI solution, and take 1 mL of 100 ⁇ g/mL PI solution into 50 mL of PBS to obtain 2 ⁇ g/mL PI solution, which can be used directly. .
  • the irradiated cells were stained with a 2 ⁇ g/mL PI solution for 20 minutes in the dark, then gently washed three times with PBS, and subjected to laser confocal microscopy for cell imaging. The PI was excited at 561 nm and the receiving channel was at 600-630 nm.
  • NCI-H292 cells and HeLa cells in the logarithmic growth phase were digested with trypsin to prepare a monodisperse cell suspension, and the cells were counted using a cell counting plate, and then the cell suspension was diluted to 50,000 cells/mL. 100 ⁇ L of the cell suspension (5 ⁇ 10 3 /well) was inoculated into a 96-well plate, and 100 ⁇ L of normal cells containing no cells were added to the control group, and incubated at 37 ° C, 5% CO 2 for 12 hours.
  • the serum-free 1640 medium is used instead of the old one.
  • 10 ⁇ L of each concentration of the test solution was sequentially added to each well containing the cells, and the final probe concentrations were 0, 0.5, 1, 2.5, and 5 ⁇ g/mL, respectively, and incubated at 37 ° C for 24 hours.
  • the old medium in the 96-well plate was removed, and the cells were gently washed twice with PBS to remove the nano-probes that were not phagocytosed by the cells, and then 100 ⁇ L of the new medium was added.
  • An LED light source of 460 nm and a power of 50 mW/cm 2 was used to irradiate cells for 0, 10, 20 and 30 min, respectively.
  • 10 ⁇ L of CCK-8 solution was added to each well, and the mixture was incubated at 37 ° C for 2 hours. After the solution was discolored, the OD value of the 96-well plate at 450 nm was measured with a microplate reader. The formula was used to calculate the killing effect of different concentrations of nanoprobe on NCI-H292 cells and HeLa cells under different illumination time.
  • cell viability* (%) [A (dosing) - A (blank)] / [A (0 dosing) - A (blank)] ⁇ 100.
  • a (dosing) refers to the absorbance of a well having cells, a CCK-8 solution and a probe solution
  • a (blank) refers to the absorbance of a well having a medium and a CCK-8 solution without cells
  • a (0 plus Drug) refers to the absorbance of a well having a cell, a CCK-8 solution, and no probe solution.
  • the IC50 values (semi-lethal concentration) of NCI-H292 and HeLa cells were 0.8 ⁇ g/mL and 2.43 ⁇ g/mL, respectively.
  • mice inoculated with NCI-H292 tumor underarm. After the tumor volume of the mouse reached about 100-150 mm 3 , 15 nude mice were randomly divided into three groups (5 in each group): the first group was the illumination group, that is, only the light was irradiated, and the material was not injected; the second group For the material group, the nano-probe was only injected into the tail vein, and there was no illumination; the third group was the photodynamic experiment group, that is, the nano-probe was injected into the tail vein and received light irradiation.
  • the first group was the illumination group, that is, only the light was irradiated, and the material was not injected
  • the second group For the material group, the nano-probe was only injected into the tail vein, and there was no illumination
  • the third group was the photodynamic experiment group, that is, the nano-probe was injected into the tail vein and received light irradiation.
  • mice requiring tail vein injection of nanoprobes injections were given every 7 days, 40 ⁇ g of nanoprobes per injection; for mice that required light exposure, the source used a wavelength of 460 nm and a power of 100 mW/cm 2 LED lamp, each irradiation time is 30 minutes, the irradiation site is the tumor site.
  • the mice are irradiated immediately after the injection of the material, and the photodynamic experiment group and the illumination group are irradiated every 7 days. The total treatment time is 28 days.
  • the size and body weight of the mouse tumors were measured every 7 days and recorded.
  • the volume of the tumor was calculated according to the following equation: (tumor length) x (tumor width) 2 /2; the relative volume of the tumor was calculated as V/V 0 (V 0 refers to the volume of the initial tumor).
  • V 0 refers to the volume of the initial tumor.
  • the axillary lymph node (AX) metastasis model was established: the tumor cells in the logarithmic growth phase were digested and centrifuged, dispersed in PBS, and formulated into a certain concentration of cell suspension. 200 ⁇ L of the tumor cell suspension (2 ⁇ 10 6 / each) was subcutaneously inoculated into the infraorbital site of the mouse, and the tumor grew after about 10 days.
  • PO metastatic lymph node
  • tumor tissue axillary lymph node (AX), popliteal lymph node (PO), sciatic lymph node (SC), and inguinal lymph node (inguinal lymph node) were used.
  • AX axillary lymph node
  • PO popliteal lymph node
  • SC sciatic lymph node
  • inguinal lymph node inguinal lymph node (inguinal lymph node) were used.
  • IN fixed for paraffin embedding, and hematoxylin and eosin staining, staining with Anti-VEGFA antibody (ab46154), and obtaining images of tissue sections by optical microscopy.
  • the phospholipid folic acid-doped PFBT near-infrared fluorescent nanoconjugated polymer nanoprobe was simultaneously injected into the two foot pads of the mouse to observe the nanoprobe to the lymph node.
  • Targeting situation of transfer. Mice were imaged in vivo using PerkinElmer's IVIS Lumina XRMS Series III imaging system.
  • the excitation light source is 460 nm, and the receiving channel is selected to be a 780 nm filter.
  • RESULTS Specifically, you can participate in Figure 37-39. From Figure 37, when the tumor diameter reaches 5 mm, the axillary lymph node on the tumor side is injected 2 hours after the injection of the near-infrared fluorescent polymer nanoprobe through the foot pad. The near-infrared signal of the probe was detected, and there was no probe signal on the opposite side of the PO. When the skin of the mouse was cut open and two POs were taken out, it was confirmed that the probe was detected only on the PO side of the tumor. Near infrared fluorescence signal. The results demonstrate that the nanoprobe can specifically target the PO lymph nodes where tumor metastasis occurs.
  • the near-infrared signal of the probe is detected on the axillary lymph node PO of the tumor side and the SC of the hip lymph node on the tumor side by injecting the near-infrared fluorescent polymer nanoprobe through the foot pad.
  • the contralateral PO and SC there was no probe signal.
  • the skin of the mouse was cut open and the lymph nodes were taken out, it was confirmed that the near-infrared fluorescent signal of the probe was detected only on the side of the tumor by PO and SC.
  • the results demonstrate that the nanoprobe can specifically target the PO and SC lymph nodes where tumor metastasis occurs. From Fig.
  • the axillary lymph node PO on the tumor side and the fluorescence of the hip lymph node SC can still be detected after 20 days of injection of the near-infrared fluorescent polymer nanoprobe through the foot pad. signal.
  • the nanoprobe was confirmed to remain in the lymph nodes for a long time.
  • the phospholipid folic acid-doped PFBT near-infrared fluorescent nanoconjugated polymer nanoprobe was simultaneously injected into the two foot pads of the mouse to observe the nanoprobe to the lymph node.
  • Targeting situation of transfer For small animal live photoacoustic imaging, scanning was performed using the MSOT real-time scanner (MSOT inVision 128) from iThera Medical, Germany.
  • the excitation band is from 680-800 nm, and an excitation peak is selected every 10 nm, and the scanning step is 0.2 mm.
  • the data at the optimal excitation wavelength of 770 nm is selected, and the image is reconstructed based on the back projection algorithm.
  • Figure 40-41 Specifically, you can participate in Figure 40-41. From Figure 40, after injecting near-infrared fluorescent polymer nanoprobe through the foot pad, the axillary lymph node PO, hip lymph node SC, and lymphatic vessel were detected. The photoacoustic signal of the needle. Four hours after the injection, it was concluded from Fig. 41 that photoacoustic signals of the probe were detected in the axillary lymph node PO, the hip lymph node SC, and the inguinal lymph node IN.
  • RESULTS See Figures 42 and 43 for details. It can be seen from the figure that after injecting Gd 3+ hybridized near-infrared fluorescent polymer nanoprobe through the foot pad, in the axillary lymph node PO, hip lymph node SC, groin The lymph node IN detects the magnetic resonance signal and the near-infrared fluorescence signal of the probe.
  • FIG. 44 can be taken from the figure, after the Gd 3+ hybridized near-infrared fluorescent polymer nano-probe is injected through the tail vein, the probe is detected in the tumor tissue and the two axillary lymph nodes AX. Magnetic resonance signals and near-infrared fluorescent signals.
  • the phospholipid folate-doped PFBT near-infrared fluorescent nanoconjugated polymer nanoprobe was simultaneously injected into the two foot pads of mice to observe the nanoprobe for lymph node metastasis.
  • Targeting situation Mice were imaged in vivo using PerkinElmer's IVIS Lumina XRMS Series III imaging system.
  • the excitation light source is 460 nm, and the receiving channel is selected to be a 780 nm filter.
  • RESULTS Specifically, it can be taken as shown in Fig. 45. It can be seen from the drawing that the near-infrared signal of the probe is detected in the axillary lymph node PO on the side of the tumor at different time by injecting the near-infrared fluorescent polymer nanoprobe through the foot pad. In the absence of a probe signal on the contralateral PO, when the skin of the mouse was cut and two POs were taken out, it was confirmed that the near-infrared fluorescent signal of the probe was detected only on the PO side of the tumor. The results demonstrate that the nanoprobe can specifically target the PO lymph nodes where tumor metastasis occurs.

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Abstract

一种共轭聚合物纳米探针，包括：荧光共轭聚合物；表面配体；靶分子；近红外荧光染料；还可以包括含钆磁共振造影剂。该共轭聚合物纳米探针的制备方法为：在有机溶剂中加入上述原料，超声混合获得混合液；将混合液加到超纯水中，继续超声。该共轭聚合物纳米探针融合近红外荧光成像、光声成像和磁共振成像双模态或三模态分子成像技术，可识别转移淋巴结和正常淋巴结，且在转移淋巴结的滞留时间长，满足长时间观察检测的需求。同时，该近红外荧光共轭聚合物纳米探针，其能在光照条件下产生活性氧，可以用于肿瘤光动力学治疗。

Description

[根据细则37.2由ISA制定的发明名称]　共轭聚合物纳米探针及其制备方法和应用 技术领域
本发明涉及分子影像领域，具体涉及一种共轭聚合物纳米探针，及其制备方法和应用，尤其是在淋巴结转移肿瘤模型中，通过近红外荧光成像、光声成像、磁共振成像，对发生肿瘤转移的淋巴结进行靶向成像的应用。
背景技术
淋巴结转移是大多数原发肿瘤常见的转移方式，例如：乳腺癌，肺癌，胃癌，食管癌，甲状腺癌，宫颈癌，卵巢癌，结直肠腺癌，胰腺癌，喉癌等都容易发生淋巴结转移。淋巴结的分期是决定大多数原发肿瘤治疗方案和预后的重要因素，对于患者术前淋巴转移程度的准确评估具有重要的临床意义。然而，目前临床上用于检测淋巴转移的探针(例如：ICG)和影像学方法(例如PET/CT，磁共振，超声等)尚不能有效识别正常的淋巴结与发生肿瘤转移的淋巴结。而系统淋巴结清扫术具有较大的创伤，术后后遗症的几率也上升，更为严重的是部分早期癌症患者无法确定淋巴结状态而被动地进行不必要的淋巴结清扫。如果能够在术前、术中检测淋巴结转移的状态，准确地判断肿瘤的累及范围，将极大的减少患者的痛苦，提高生活质量。
分子影像学是利用影像学手段研究在体条件下细胞内的正常或病理状态分子过程，在分子或细胞水平反映生物体生理、病理变化，为疾病过程在体监测、基因治疗在体示踪、在体疗效评测和功能分子在体活动规律研究提供新的技,具有无创、实时、在体、精细显像，高度灵敏、高度特异性等优点。分子影像采用多种成像手段，对体内特定靶点进行成像，其核心是分子探针的设计。分子影像手段主要包括放射性核素成像、磁共振成像、光学成像、超声成像、以及光声成像等。每种成像模态都具有其优势和局限。例如荧光成像灵敏度高、价格相对低廉、操作方便，但其穿透深度受限。放射性核素成像及磁共振成像对深度无限制，但磁共振成像的灵敏度很低，放射性核素成像的空间分辨率较低。此外，单一模态成像获取的信息有限且不能反映生物体的复杂及特异性，因此，融合多模态分子成像，构建多模态分子探针，彼此互补，可为生物医学研究提供更准确可靠的影像信息。
荧光共轭聚合物作为一种荧光探针，具有独特的光物理和光化学性质。1995年，麻省理工学院的Swager等首次报道了荧光共轭聚合物由于具有π-π*共轭的分子导线结构，可以使荧光响应信号放大百倍，这一发现使得荧光共轭聚合物广 泛用于核酸、蛋白质等生物大分子以及ATP、葡萄糖等小分子的检测。荧光共轭聚合物由于具有π-π*共轭的分子导线结构，与传统小分子荧光化合物相比具有一些优点：(1)稳定性好；(2)共轭聚合物电子结构、荧光发射波长能够通过对化学结构的改变和修饰进行调节；(3)在不改变结合常数的前提下，可以成百倍地放大响应信号，从而能够提高检测的灵敏度。此外，与半导体量子点相比，荧光共轭聚合物不含任何有毒金属元素，毒性低。因此，近年来，荧光共轭聚合物在分子影像领域的应用也引起了科研工作者的关注。但是已报道的荧光共轭聚合物纳米材料中，由于其发射光的波长主要在可见光的范围内，为此这类材料用于小动物活体成像的例子还比较少。此外，基于荧光共轭聚合物纳米探针的淋巴结转移的靶向成像尚未见文献报道。
因此，本领域的技术人员致力于开发一种共轭聚合物纳米探针及其制备方法，用于多模态分子成像，以更好的进行淋巴结转移的靶向成像并区分正常的淋巴结与发生肿瘤转移的淋巴结。
发明内容
有鉴于现有技术中多是单一模态成像，并且尚未有对淋巴结转移的靶向成像中的良好探针，本发明所要解决的技术问题是提供一种共轭聚合物纳米探针及其制备方法和应用。
为实现上述目的，本发明的第一个方面提供了一种共轭聚合物纳米探针。在一个具体实施方式中，该共轭聚合物纳米探针包括：
荧光共轭聚合物；
表面配体；
靶分子；
近红荧光外染料。
其中，表面配体位于共轭聚合物纳米探针的表面，靶分子位于共轭聚合物纳米探针的表面，近红荧光外染料位于共轭聚合物纳米探针的内部。表面配体作用是增加探针的生物相容性，以及提供的羧基可进一步与抗体/蛋白等偶联。靶分子用于和肿瘤细胞上的受体等结合，形成探针与肿瘤细胞的结合。
进一步地，靶分子能识别叶酸受体。
进一步地，靶分子为磷脂修饰的靶分子。
进一步地，磷脂修饰为使用脂质体修饰。
优选地，磷脂修饰的靶分子为磷脂酰乙醇胺-聚乙二醇5000-叶酸交连物、磷脂酰乙醇胺-聚乙二醇2000-叶酸交连物和磷脂酰乙醇胺-叶酸交连物中的一种或多种。
进一步地，表面配体为末端羧基修饰的表面配体。进一步地，表面配体选自苯 乙烯-聚乙二醇-羧基(PS-PEG-COOH)、聚乙二醇-羧基(PEG-COOH)、苯乙烯-顺丁烯二酸酐共聚物(PSMA)或其组合。
进一步地，近红外荧光染料的吸收波长在700～900nm之间。优选地，近红外荧光染料选自NIR775、DiIC18、ICG、Cy7或Cy7.5。
进一步地，荧光共轭聚合物选自PFBT或MEH-PPV。
进一步地，PFBT分子量在10000～52000之间，MEH-PPV分子量在Mw＝10142～200000。
优选地，PFBT分子量为Mn＝10000～20000,39000,47000,52000，MEH-PPV分子量为Mw＝10142，200000。
优选地，近红外荧光染料与荧光共轭聚合物的重量比在0.2％-1.2％之间，表面配体与荧光聚合物的重量比在0.5-2之间，靶分子与荧光聚合物的重量比在0.2-1之间。
进一步地，如上所述的共轭聚合物纳米探针的透射电镜显示其平均粒径大小分布为2～100nm。
优选地，如上所述的共轭聚合物纳米探针的透射电镜显示其平均粒径大小分布为20～60nm。
在另一优选地实施例中，该共轭聚合物纳米探针还包括含钆磁共振造影剂。
其中，含钆磁共振造影剂位于共轭聚合物纳米探针的表面。
进一步地，含钆磁共振造影剂为磷脂修饰的钆。
进一步地，磷脂修饰的钆为磷脂修饰的钆的二乙烯二胺五醋酸络合物(DTPA)，选自DTPA-BSA(Gd)、bis(18:0PE)-DTPA(Gd)、bis(16:0PE)-DTPA(Gd)、bis(14:0PE)-DTPA(Gd)、18:0PE-DTPA(Gd)、16:0PE-DTPA(Gd)或其组合物。
优选地，近红外荧光染料与荧光共轭聚合物的重量比在0.2％-1.2％之间，表面配体与荧光共轭聚合物的重量比在0.5-2之间，靶分子与荧光共轭聚合物的重量比在0.2-1之间，含钆磁共振造影剂与荧光聚合物的重量比在3-5之间。
进一步地，上述共轭聚合物纳米探针的透射电镜显示其平均粒径分布为20～130nm。
优选地，上述共轭聚合物纳米探针的透射电镜显示其平均粒径分布为30～60nm。
本发明的第二个一方面提供了一种共轭聚合物纳米探针的制备方法，在一个具体实施方式中，共轭聚合物纳米探针为如上所述的不含钆磁共振造影剂的共轭聚合物纳米探针，该方法包括：
1)在有机溶剂中加入荧光共轭聚合物、表面配体、近红外荧光染料和靶分子，超声混合获得混合液；
2)在超声条件下，将上述混合液加到超纯水中，继续超声。
在另一个具体实施方式中，共轭聚合物纳米探针为如上所述的含钆磁共振造影剂的共轭聚合物纳米探针，该方法在如上所述方法的步骤1)中，在有机溶剂中还添加了所述含钆磁共振造影剂。
进一步地，靶分子为磷脂修饰的靶分子。
进一步地，含钆磁共振造影剂为磷脂修饰的钆。
进一步地，步骤2)中，超声的功率设置为8-12％，每超声4-6秒停2-4秒，超声时间设置为50-70秒。优选地，超声的功率设置为10％，每超声5秒停3秒，超声时间设置为1分钟。优选地，含钆磁共振造影剂与所述荧光聚合物的重量比在3-5之间。
进一步地，步骤1)中有机溶剂为四氢呋喃溶液或氯仿。
优选地，步骤1)中，近红外荧光染料与荧光共轭聚合物的重量比在0.2-1.2％之间，表面配体与荧光共轭聚合物的重量比在0.5-2之间，靶分子与荧光共轭聚合物的重量比在0.2-1之间。
进一步地，上述方法在步骤2)之后，还包括：3)在加热条件下通入氮气使有机溶剂挥发，得到共轭聚合物纳米探针。
进一步地，步骤3)中，所述加热条件为在45-55℃。优选地，为50℃。
本发明的第三个方面提供了一种共轭聚合物纳米探针在制备分子影像试剂中的应用。在一个具体实施方式中，该共轭聚合物纳米探针为如上所述的不含钆磁共振造影剂的共轭聚合物纳米探针，该共轭聚合物纳米探针能进行近红外荧光成像和/或光声成像。
在另一个具体实施方式中，该共轭聚合物纳米探针为如上所述的含钆磁共振造影剂的共轭聚合物纳米探针，该共轭聚合物纳米探针能进行近红外荧光成像、光声成像和/或磁共振成像。
进一步地，上述共轭聚合物纳米探针能在细胞层次靶向成像叶酸受体表达的肿瘤细胞。
进一步地，上述共轭聚合物纳米探针能识别发生肿瘤转移的淋巴结和正常淋巴结。
进一步地，上述共轭聚合物纳米探针能在小动物活体层次识别发生肿瘤转移的淋巴结和正常淋巴结。
本发明的第四个方面提供了一种分子影像试剂。在一个优选的具体实施方式中，该分子影像试剂包括如上所述的共轭聚合物纳米探针。
本发明的第五个方面提供了一种共轭聚合物纳米探针在制备光动力治疗试剂中的应用。在一个具体实施方式中，该共轭聚合物纳米探针如上所述。
进一步地，该共轭聚合物纳米探针包括近红外荧光染料，所述近红外荧光染料在光照下能产生活性氧。
进一步地，该近红外荧光染料为含有四吡咯基结构的近红外染料。
优选地，该近红外荧光染料为NIR775。
本发明的第六个方面提供了一种光动力治疗试剂。在一个优选的具体实施方式中，该光动力治疗试剂包括如上所述的共轭聚合物纳米探针。
进一步地，该共轭聚合物纳米探针包括近红外荧光染料，该近红外荧光染料在光照下能产生活性氧。
进一步地，该近红外荧光染料为含有四吡咯基结构的近红外染料。
优选地，该近红外荧光染料为NIR775。
进一步地，该光动力治疗试剂能用于肿瘤光动力学治疗。
进一步地，该光动力治疗试剂能在细胞层次和小动物活体层次杀死肿瘤细胞。
进一步地，该肿瘤为皮下实体瘤。
本发明的杂化荧光共轭聚合物纳米探针，同时具有多模态成像及叶酸受体靶向功能，在细胞层次可靶向成像叶酸受体表达的肿瘤细胞；在淋巴转移肿瘤模型中，可有效识别转移淋巴结和正常淋巴结，且在转移淋巴结的滞留时间长，可满足长时间观察检测的需求。按照本发明的方法制备合成的杂化荧光共轭聚合物纳米探针，在淋巴结转移肿瘤模型中，可有效识别发生肿瘤转移的淋巴结，其对淋巴结转移的特异性靶向成像效果能达到或超过了目前已知同类产品的水平。
并且，采用共沉淀方法一步合成，合成工艺简易且效率高。由于靶分子和含钆磁共振造影剂都是磷脂修饰的，在超声之后，其与荧光共轭聚合物之间的交联性好、交联稳定，避免出现小分子从纳米探针中漏出的情况，因此，能造就一步法合成该共轭聚合物纳米探针。另外，在超声后，表面配体将整个纳米探针包覆的更紧，进一步防止小分子的漏出，提高了整个纳米探针的稳定性，有助于纳米探针的保存稳定性。
本发明的杂化荧光共轭聚合物纳米探针融合近红外荧光成像、光声成像和磁共振成像双模态或三模态分子成像技术，在小动物活体层次实现对转移淋巴结的靶向成像，可用于成像介导的手术导航，实施对转移淋巴结的切除，提高切除率。
本发明的近红外荧光掺杂的共轭聚合物纳米探针，其能在光照下能产生活性氧，可以用于肿瘤光动力学治疗，尤其是皮下实体瘤。并且该共轭聚合物纳米探针效果好、细胞毒性低，在光动力治疗中非常有应用前景。
以下将结合附图对本发明的构思、具体步骤及产生的技术效果作进一步说明，以充分地了解本发明的目的、特征和效果。
附图说明
图1是本发明的一个具体实施方式中荧光共轭聚合物纳米探针的机构示意图。
图2是本发明的另一个具体实施方式中荧光共轭聚合物纳米探针的机构示意图。
图3是实施例1中探针制备的示意图。
图4是实施例1中探针的电镜图。
图5是实施例2中探针制备的示意图。
图6是实施例2中探针的电镜图。
图7是NIR775杂化的PFBT荧光共轭聚合物纳米探针的近红外荧光光谱。
图8是NIR775杂化的MEH-PPV荧光共轭聚合物纳米探针的近红外荧光光谱。
图9是NIR775杂化的PFBT荧光共轭聚合物纳米探针的体外光声成像。
图10是NIR775、Gd3+杂化的PFBT荧光共轭聚合物纳米探针的体外磁共振成像。
图11是人神经胶质瘤U87MG细胞,人卵巢癌SKOV3细胞，人肺癌NCI-H292(淋巴结转移)细胞，及人宫颈癌HeLa细胞的叶酸受体表达的流式细胞图。
图12是杂化荧光共轭聚合物纳米探针的NCI-H292细胞毒性。
图13是杂化荧光共轭聚合物纳米探针的HeLa细胞毒性。
图14是杂化荧光共轭聚合物纳米探针的NCI-H292和HeLa细胞的靶向成像。
图15是杂化荧光共轭聚合物纳米探针的NCI-H292流式细胞图。
图16是杂化荧光共轭聚合物纳米探针的HeLa流式细胞图。
图17是NIR775杂化的分子量为10000-20000的PFBT近红外荧光纳米探针在溶液状态下的活性氧的检测。
图18是NIR775杂化的分子量为47000的PFBT近红外荧光纳米探针在溶液状态下的活性氧的检测。
图19是NIR775杂化的不同分子量的PFBT近红外荧光纳米探针在溶液状态下活性氧产生效率的比较。
图20是杂化荧光共轭聚合物纳米探针的NCI-H292细胞内的活性氧及细胞凋亡检测。
图21是杂化荧光共轭聚合物纳米探针的HeLa细胞内的活性氧及细胞凋亡检测。
图22是杂化荧光共轭聚合物纳米探针的NCI-H292细胞的光动力学毒性。
图23是杂化荧光共轭聚合物纳米探针的HeLa细胞的光动力学毒性。
图24是杂化荧光共轭聚合物纳米探针的在体光动力学治疗的NCI-H292肿瘤的生长曲线。
图25是杂化荧光共轭聚合物纳米探针的在体光动力学治疗的NCI-H292肿瘤小鼠的体重变化。
图26是杂化荧光共轭聚合物纳米探针的NCI-H292肿瘤的在体光动力学治疗 的NCI-H292肿瘤小鼠的组织H&E染色。
图27是NCI-H292肿瘤组织的H&E染色。
图28是正常淋巴结的H&E染色。
图29是发生NCI-H292肿瘤转移的AX淋巴结的H&E染色。
图30是发生NCI-H292肿瘤转移的PO淋巴结的H&E染色。
图31是发生NCI-H292肿瘤转移的SC淋巴结的H&E染色。
图32是发生NCI-H292肿瘤转移的IN淋巴结的H&E染色。
图33是发生NCI-H292肿瘤转移的AX淋巴结的VEGF染色。
图34是发生NCI-H292肿瘤转移的PO淋巴结的VEGF染色。
图35是发生NCI-H292肿瘤转移的SC淋巴结的VEGF染色。
图36是发生NCI-H292肿瘤转移的IN淋巴结的VEGF染色。
图37是杂化荧光共轭聚合物纳米探针(7.5μg)的淋巴结转移的在体近红外荧光成像(NCI-H292肿瘤模型)。
图38是杂化荧光共轭聚合物纳米探针(15μg)的淋巴结转移的在体近红外荧光成像(NCI-H292肿瘤模型)。
图39是杂化荧光共轭聚合物纳米探针(170μg)的淋巴结转移的在体近红外荧光成像(NCI-H292肿瘤模型)。
图40是杂化荧光共轭聚合物纳米探针的淋巴结转移的在体光声成像。红色代表HbO2的光声信号，绿色代表纳米探针的光声信号(NCI-H292肿瘤模型)。
图41是杂化荧光共轭聚合物纳米探针的淋巴结转移的在体光声成像。绿色代表纳米探针的光声信号(NCI-H292肿瘤模型)。
图42是杂化荧光共轭聚合物纳米探针的淋巴结转移的在体磁共振成像(NCI-H292肿瘤模型)。
图43是杂化荧光共轭聚合物纳米探针的淋巴结转移的离体近红外荧光成像(NCI-H292肿瘤模型)。
图44是杂化荧光共轭聚合物纳米探针的淋巴结转移的在体磁共振和离体的近红外荧光成像(NCI-H292肿瘤模型)。T表示肿瘤。
图45是杂化荧光共轭聚合物纳米探针的淋巴结转移的在体近红外荧光成像(HeLa肿瘤模型)。
具体实施方式
除非另外定义，本文中所使用的技术和属于都具有本发明所述领域普通技术人员通常所理解的同样含义。
除非说明书和权利要求书中明确说明，术语“包括”、“包含”等应被认为是包括性含义，而不是排他性或穷举性含义，也就是说，其含义是“包括但不限于”。
本文中，化合物的缩写或中英文对应如下：
DSPE-PEG(5000)Folate：磷脂酰乙醇胺-聚乙二醇5000-叶酸交连物；
DSPE-PEG(2000)Folate：磷脂酰乙醇胺-聚乙二醇2000-叶酸交连物；
PE-Folate：磷脂酰乙醇胺-叶酸交连物；
PS-PEG-COOH：苯乙烯-聚乙二醇-羧基；
PEG-COOH：聚乙二醇-羧基；
PSMA：苯乙烯-顺丁烯二酸酐共聚物；
PFBT：9,9-二辛基聚芴-苯并噻二唑交替共聚物；
MEH-PPV：聚[2-甲氧基-5-(2'-乙基己氧基)-1,4苯撑乙烯撑]；
ADMA：9,10-蒽基-双(亚甲基)二丙二酸；
DCFH-DA：2',7'-二氯荧光素二乙酸酯；
DCF：二氯荧光素；
PI：碘化丙啶；
AX：腋下淋巴结；
PO：腘窝淋巴结；
SC：髋部淋巴结；
IN：腹股沟淋巴结；
THF：四氢呋喃。
本文中使用的原料，若没有特殊说明，均可直接购买获得。如近红外荧光染料NIR775、DiIC18、ICG、Cy7或Cy7.5均为市售产品，可以直接购买获得。
本发明的一方面提供了一种荧光共轭聚合物纳米探针，所述探针具有如图1或图2所示的结构。
如图1所示的荧光共轭聚合物纳米探针，包括荧光共轭聚合物；表面配体；靶分子；近红外荧光染料。
如图2所示的荧光共轭聚合物纳米探针，包括荧光共轭聚合物；表面配体；靶分子；近红外荧光染料，还包括含钆磁共振造影剂。
其中，荧光共轭聚合物可以为不同分子量的PFBT和MEH-PPV；
靶分子包括DSPE-PEG(5000)Folate、DSPE-PEG(2000)Folate、PE-Folate或其组合；
表面配体包括PS-PEG-COOH，PEG-COOH，PSMA或其组合；
Gd3+(含钆磁共振造影剂)包括DTPA-BSA(Gd)，bis(18:0PE)-DTPA(Gd)，bis(16:0PE)-DTPA(Gd)，bis(14:0PE)-DTPA(Gd)，18:0PE-DTPA(Gd)，16:0PE-DTPA(Gd)或其组合。
具体地：
PFBT的单体结构式为:
Figure PCTCN2017094222-appb-000001
其中，PFBT分子量范围为10000～52000。
MEH-PPV的单体结构式为：
Figure PCTCN2017094222-appb-000002
其中，MEH-PPV分子量范围为10000～200000。
DSPE-PEG(5000)Folate的结构式为：
Figure PCTCN2017094222-appb-000003
DSPE-PEG(2000)Folate的结构式为:
Figure PCTCN2017094222-appb-000004
PE-Folate的结构式为:
Figure PCTCN2017094222-appb-000005
NIR775的结构式为:
Figure PCTCN2017094222-appb-000006
R＝O-Si((CH2)5CH3)3
DiIC18的结构式为:
Figure PCTCN2017094222-appb-000007
Cy7的结构式为:
Figure PCTCN2017094222-appb-000008
或其他疏水链修饰)
Cy7.5的结构式为:
Figure PCTCN2017094222-appb-000009
或其他疏水链修饰)
DTPA-BSA(Gd)的结构式为:
Figure PCTCN2017094222-appb-000010
bis(18:0PE)-DTPA(Gd)的结构式为:
Figure PCTCN2017094222-appb-000011
bis(16:0PE)-DTPA(Gd)的结构式为:
Figure PCTCN2017094222-appb-000012
bis(14:0PE)-DTPA(Gd)的结构式为:
Figure PCTCN2017094222-appb-000013
18:0PE-DTPA(Gd)的结构式为:
Figure PCTCN2017094222-appb-000014
16:0PE-DTPA(Gd)的结构式为:
Figure PCTCN2017094222-appb-000015
PS-PEG-COOH的结构式为:
Figure PCTCN2017094222-appb-000016
其中，PS部分的分子量为 6500～21700Da；PEG部分的分子量为1200～4600Da。
PEG-COOH的结构式为:
Figure PCTCN2017094222-appb-000017
其中，PEG的分子量范围2000～5000。
本发明的另一方面提供了一种共轭聚合物纳米探针的制备方法。其采用共沉淀方法制备合成，将荧光共轭聚合物、近红外荧光染料、靶分子和表面配体，或者将荧光共轭聚合物、近红外荧光染料、靶分子、表面配体和含钆磁共振造影剂的有机溶剂(如四氢呋喃)混合溶液快速加入到水中，在超声条件下形成共轭聚合物纳米探针。
本发明的再一方面提供了一种上述共轭聚合物纳米探针的应用。如图1所示的共轭聚合物纳米探针能进行近红外荧光成像和/或光声成像，如图2所示的共轭聚合物纳米探针能进行近红外荧光成像、光声成像和/或磁共振成像。
上述两种共轭聚合物纳米探针能在细胞层次靶向成像叶酸受体表达的肿瘤细胞，并能识别转移淋巴结和正常淋巴结，尤其是在小动物活体层次识别发生肿瘤转移的淋巴结和正常淋巴结。
本发明的又一方面提供了一种分子影像试剂，其包括如上所述的共轭聚合物纳米探针。
本发明的又一方面提供了上述共轭聚合物纳米探针在制备光动力治疗试剂中的应用。光动力治疗是指将光敏剂输入人体，在一定时间后，以特定波长的光照射病变部位，通过一系列光化学和光生物学反应，在分子氧的参与下，产生单态氧和/或自由基，氧化破坏组织和细胞中的各种生物大分子，使异常增生活跃的细胞发生不可逆的损伤，最终使细胞死亡，达到治疗目的。
本发明的又一方面提供了一种光动力治疗试剂，其包括如上所述的共轭聚合物纳米探针。在一个优选的实施方式中，该光动力治疗试剂包括近红外荧光染料，该近红外荧光染料在光照下能产生活性氧。并且该共轭聚合物纳米探针具有较低的毒性或无毒性。
下面将通过具体实施例的方式进行进一步地说明。
实施例1:
NIR775杂化的PFBT荧光共轭聚合物纳米探针的制备
在EP管中加入1450μL过滤后的四氢呋喃溶液，再依次加入1mg/mL PFBT及1mg/mL PS-PEG-COOH溶液各250μL，3μL NIR775溶液(1mg/mL)，50μL磷脂叶酸溶液(1mg/mL)，超声混合3分钟。在超声条件下，将该混合液快速加入到 10mL的超纯水中，超声功率设置为10％，每超声5秒停3秒，总的超声时间设置为1分钟。超声完成后，在50℃下，通入氮气约25分钟使溶液中的THF挥发干净，即可得到NIR775杂化的荧光共轭聚合物纳米探针。
上述反应示意图如图3所示。制备的NIR775杂化的荧光共轭聚合物纳米探针的粒径分布如图4所示，透射电镜显示其平均粒径大小分布为约30nm。
实施例2:
NIR775、Gd3+杂化的PFBT荧光共轭聚合物纳米探针的制备
在EP管中加入650μL过滤后的四氢呋喃溶液，再依次加入1mg/mL PFBT及1mg/mL表面配体PS-PEG-COOH溶液各250μL，3μL NIR775溶液(1mg/mL)，50μL磷脂叶酸溶液(1mg/mL)，800μL钆磁共振造影剂DTPA-BSA(Gd)溶液(1.25mg/mL)，超声混合3分钟。在超声条件下，将该混合液快速加入到10mL的超纯水中，超声功率设置为10％，每超声5秒停3秒，总的超声时间设置为1分钟。超声完成后，在50℃下，通入氮气约25分钟使溶液中的THF挥发干净，即可得到NIR775、Gd3+杂化的近红外荧光共轭聚合物纳米探针。
上述反应示意图如图5所示。制备的NIR775、Gd3+杂化的近红外荧光共轭聚合物纳米探针的粒径分布如图6所示，透射电镜显示其平均粒径大小分布为约50nm。
实施例3:
NIR775杂化的MEH-PPV荧光共轭聚合物纳米探针的制备
在EP管中加入1450μL过滤后的四氢呋喃溶液，再依次加入1mg/mL MEH-PPV及1mg/mL表面配体PS-PEG-COOH溶液各250μL，3μL NIR775溶液(1mg/mL)，50μL磷脂叶酸溶液(1mg/mL)，超声混合3分钟。在超声条件下，将该混合液快速加入到10mL的超纯水中，超声功率设置为10％，每超声5秒停3秒，总的超声时间设置为1分钟。超声完成后，在50℃下，通入氮气约25分钟使溶液中的THF挥发干净，即可得到NIR775杂化的荧光共轭聚合物纳米探针。制备的NIR775杂化的荧光共轭聚合物纳米探针，透射电镜显示其平均粒径大小分布为20～30nm。
实施例4:
NIR775、Gd3+杂化的MEH-PPV荧光共轭聚合物纳米探针的制备
在EP管中加入650μL过滤后的四氢呋喃溶液，再依次加入1mg/mL MEH-PPV及1mg/mL表面配体PS-PEG-COOH溶液各250μL，3μL NIR775溶液(1mg/mL)，50μL磷脂叶酸溶液(1mg/mL)，800μL钆磁共振造影剂DTPA-BSA(Gd)溶液(1.25mg/mL)，超声混合3分钟。在超声条件下，将该混合液快速加入到10mL 的超纯水中，超声功率设置为10％，每超声5秒停3秒，总的超声时间设置为1分钟。超声完成后，在50℃下，通入氮气约25分钟使溶液中的THF挥发干净，即可得到NIR775、Gd3+杂化的近红外荧光共轭聚合物纳米探针。制备的NIR775、Gd3+杂化的近红外荧光共轭聚合物纳米探针，透射电镜显示其平均粒径大小分布为40～50nm。
实施例5:
纳米探针的荧光光谱研究
取1mL的探针溶液加入到石英皿中，测试样品的荧光激发与荧光发射光谱。实验仪器采用爱丁堡LFS-920荧光光谱仪，荧光激发光谱扫描参数设置：接收波长776nm，激发波段350-750nm；荧光发射光谱扫描参数设置：激发波长465nm，接收波段500-850nm；扫描间隔设置为2nm，狭缝宽5nm，5nm，电压400V。
结果：具体参见图7-8，从附图7中得出NIR775杂化的PFBT荧光共轭聚合物纳米探针在500-650nm有较弱PFBT的荧光发射，在750-800nm有强的NIR775的荧光发射峰。从图8中得出NIR775杂化的MEH-PPV荧光共轭聚合物纳米探针在550-700nm有较弱MEH-PPV的荧光发射，在750-800nm有强的NIR775的荧光发射峰。结果说明PFBT和MEH-PPV都能够和NIR775发生荧光共振能量转移，使探针的发射峰在近红外区，减少背景荧光的干扰，有利于活体成像检测。
实施例6:
纳米探针的体外光声成像研究
将浓度分别为31.25，62.5，125，250和500μg/mL的NIR775掺杂量为0.6wt％的PFBT近红外荧光纳米探针溶液依次加入到聚氯乙烯塑料管中，以纯水作对照组，测量770nm激发下，光声信号的强度以及溶液光声成像图片。光声成像采用德国iThera Medical公司的MSOT实时扫描仪(MSOT inVision 128)。
结果：具体可以参加图9，从附图中得出，在0-500μg/mL范围内，随着浓度的增加，光声信号强度依次增强，在浓度达到500μg/mL时，探针溶液与纯水(浓度为0μg/mL)的光声成像图片具有明显的对比效果，将光声信号强度与浓度作图，在0-500μg/mL范围内，样品的浓度与光声信号强度成线性关系，R2＝0.9992。结果表明NIR775杂化的荧光共轭聚合物纳米探针可用于活体光声成像。
实施例7:
纳米探针的体外T1加权磁共振成像研究
将20mL掺钆磁共振造影剂(以DTPA-BSA(Gd)为例)的样品采用100K的超虑管以4500rpm/min离心3-4分钟，后梯度稀释成原浓缩样品浓度的1，1/2，1/4， 1/8及1/16倍。取1mL上述不同浓度的样品放入2mL EP管中，将样品放入磁场强度为0.55T的中尺寸核磁共振分析与成像系统中检测，采集样品MRI横截面图像，完成T1加权像。T1加权成像效果采用MesoMR23-060H-I中尺寸核磁共振分析与成像系统，上海纽迈电子科技有限公司生产，共振频率23.315MHz，磁体强度0.55T，线圈直径为60mm，磁体温度为32℃。参数设置为：采用MSE序列,SFO1(MHz)＝23.315,FOVRead(mm)＝80,FOVPhase(mm)＝80,TR(ms)＝240,TE(ms)＝18.2,Slice width(mm)＝5,Slices＝1,Average＝8。
结果：具体可以参加图10，从图中得出，随着Gd3+浓度的上升，其信号强度逐渐增强，T1加权体外成像结果规律明显，并且当Gd3+浓度为0.608mM时，其造影效果与水的造影效果对比明显，结果说明Gd3+杂化的荧光聚合物纳米探针作为T1造影剂用于磁共振成像。
实施例8:
肿瘤细胞叶酸受体表达量的检测
用胰酶将处于对数生长期的U87MG细胞，SKOV3细胞，NCI-H292细胞及HeLa细胞进行消化，制作成单分散的细胞悬液，采用细胞计数板对细胞进行计数，后将相同数目的细胞接种到六孔板(1×106个/孔)中，采用含1％双抗，10％血清的无叶酸1640培养液进行培养，37℃，5％CO2下孵育12h。细胞贴壁后，移去旧的培养液，加入2mLPBS缓冲液，向实验组中加入5μL Mov18(1:400)，37℃下，共孵育30min，使得细胞与抗体充分结合；到达时间点后，用PBS清洗细胞3次，除去未结合的抗体，再加入2mLPBS缓冲液，后加入10μL带有FITC的Anti-mouse IgG(1:200)，37℃共孵育20min；最后用PBS清洗细胞3次，消化后的细胞用500μL PBS分散。没有接受抗体处理的细胞当作对照组。最后，采用流式细胞仪对对照组及实验组细胞进行检测，收集1×104个细胞进行分析。实验中，激发波长为488nm，接收波长为515nm，带宽为20nm，收集的数据采用BD Accuri C6软件进行分析。
结果：具体可以参加图11，从附图中得出人神经胶质瘤U87MG细胞叶酸受体阴性；人卵巢癌SKOV3细胞，人肺癌NCI-H292(淋巴结转移)细胞，及人宫颈癌HeLa细胞叶酸受体阳性，其中HeLa细胞高表达叶酸受体。
实施例9:
纳米探针的细胞毒性研究
采用CCK-8试剂盒来评估近红外荧光共轭聚合物纳米探针(以PFBT NPs为例)、叶酸功能化的近红外荧光共轭聚合物纳米探针(以FA-PFBT NPs为例)及Gd3+和叶酸功能化的近红外荧光共轭聚合物纳米探针(以Gd-FA-PFBT NPs为例)的毒性。具体实验步骤如下：
用胰酶将处于对数生长期的NCI-H292细胞和HeLa细胞进行消化，制作成单分散的细胞悬液，采用细胞计数板对细胞进行计数，后将细胞悬液稀释成50 000个/mL，取100μL的细胞悬液(5×103个/孔)接种到96孔板中，对照组中加入100μL不含细胞的正常培养液，在37℃，5％CO2下孵育12h。
细胞贴壁后，向含有细胞的各孔中依次加入10μL各浓度的待测探针溶液，最终探针浓度分别0，5，25，50和100μg/mL，37℃下共孵育24h。到达时间点后，移去96孔板中旧的培养液，并用PBS轻轻清洗细胞两次，向各孔中加入预先配制好的110μL的CCK-8与培养液的混合溶液，其中CCK-8与培养液的体积比为1：10，37℃下孵育2小时，待溶液变色后，用酶标仪测定96孔板在450nm处的OD值。
细胞存活率的计算：细胞存活率*(％)＝[A(加药)-A(空白)]/[A(0加药)-A(空白)]×100。其中A(加药)是指具有细胞、CCK-8溶液和探针溶液的孔的吸光度，A(空白)是指具有培养基和CCK-8溶液而没有细胞的孔的吸光度，A(0加药)是指具有细胞、CCK-8溶液而没有探针溶液的孔的吸光度。
结果：具体可以参加图12-13，从附图中得出，对于未功能化的PFBT近红外聚合物荧光纳米探针，浓度在5-100μg/mL范围内，NCI-H292和HeLa细胞的存活力分别大于99％和87％，当纳米探针浓度高于50μg/mL时，HeLa细胞的存活率呈现下降趋势，并且差异具有显著性(p<0.05)；对于叶酸功能化的近红外荧光共轭聚合物纳米探针，NCI-H292细胞和HeLa细胞的存活率分别超过91％和85％，在100μg/mL的浓度下，两种细胞的活力均存在着显著性差异(p<0.05)。对于Gd3+和叶酸功能化的近红外荧光共轭聚合物纳米探针，即使在浓度高达100μg/mL时，两种细胞的活力降低值也均小于6％，在不存在或存在Gd3+和叶酸功能化的近红外荧光共轭聚合物纳米探针的情况下，浓度为5-100μg/ml范围内，37℃下共孵育24h时，两种细胞的细胞活力均不存在显著性差异(p>0.05)。这些结果显示这类近红外荧光共轭聚合物纳米探针在5-100μg/mL浓度范围内，表现出无毒性或低细胞毒性。
实施例10:
纳米探针的细胞靶向成像研究
对于NCI-H292细胞及HeLa细胞的细胞成像实验，我们将处于对数生长期的数量相同的NCI-H292细胞及HeLa细胞消化后分别接种到共聚焦玻璃皿(2×104个/皿)中，细胞贴壁后立即开始实验。移去旧的培养液，加入1mL无血清的1640培养液，同时加入20μg的PFBT NPs或FA-PFBT NPs。在37℃，5％CO2条件下，共培养24h。后用PBS清洗细胞两次，去除未被细胞吞噬的纳米颗粒，再加入1mL4％的多聚甲醛溶液，固定20分钟后，用PBS清洗两次，加入300nmol/L的DAPI 溶液覆盖细胞，在避光条件下染色30分钟。PBS清洗之后，在激光共聚焦显微镜下进行细胞成像。
激光共聚焦显微镜的设置参数：采用458nm激发PFBT，接收通道在520-560nm；对于NIR775，采用458nm激发，接收通道在750nm-800nm；对于DAPI，采用405nm激发，信号接收波长为450nm-480nm。
结果：具体可以参加图14，从附图中得出，未掺杂磷脂叶酸的纳米探针，细胞内荧光信号较弱；掺杂磷脂叶酸后，细胞内荧光强度增强，并且PFBT的黄色信号与NIR775的红色信号基本重叠，信号主要集中在核周或细胞质内的早期溶酶体中。结果说明磷脂叶酸掺杂的纳米探针对NCI-H292细胞及HeLa细胞具有靶向性。
实施例11:
纳米探针的流式定量检测
对于NCI-H292细胞及HeLa细胞的流式定量检测，同样将细胞接种到六孔板(1×106个/孔)中，采用无血清的1640培养液进行培养，37℃，5％CO2下孵育12h。细胞贴壁后，移去旧的培养液，加入1mL新鲜的无血清1640培养液，后分别加入20μg PFBT聚合物荧光纳米探针及磷脂叶酸掺杂的PFBT聚合物荧光纳米探针，在37℃，5％CO2下，共孵育24h。到达时间点后，用PBS清洗细胞3次，除去游离在溶液中的纳米探针，消化后的细胞用500μL PBS分散，后用流式细胞仪对对照组及实验组细胞进行检测，收集1×104个细胞进行分析。实验中，激发波长为488nm，PFBT接收波长为515nm，带宽为20nm；NIR775接收波长采用670LP滤光片，收集的数据采用BD Accuri C6软件进行分析。
结果：具体可以参加图15-16，从附图中得出，掺杂磷脂叶酸后，NCI-H292细胞及HeLa细胞内对应的荧光信号均增强，该结果与共聚焦细胞成像结果一致，说明磷脂叶酸对NCI-H292细胞及HeLa细胞的靶向性。
实施例12:
纳米探针溶液状态下活性氧的检测
称取1.25mg的ADMA粉末加入到2.5mL PBS(PH＝7.4)中，超声10min，粉末完全溶解，溶液呈紫色。
将1mL NIR775掺杂的PFBT近红外荧光纳米探针与25ul上述ADMA/PBS溶液混合，加水稀释至2.5mL，溶液中最终含20ug/mL Pdots，5ug/mL ADMA。
采用460nm，100mW/cm2的光源照射上述混合溶液，隔不同时间用紫外分光光度计表征溶液的紫外吸收光谱，直至溶液的吸收光谱不再变化。不含有近红外荧光纳米探针只含有ADMA(5ug/mL)的纯溶液当做参比物，在同样的光照强度下，照射同样的时间。
对于分子量为10000-20000的PFBT聚合物荧光纳米探针，每隔1min照射一次，总共照射时间为12min；对于分子量为47000的PFBT聚合物荧光纳米探针，从0到10min，每隔1min照射一次，从10到40min，每隔5min照射一次，照射总时间为40min。
结果：具体可以参加图17-19，从附图17中得出，对于NIR775掺杂的分子量为10000-20000的PFBT聚合物荧光纳米探针与ADMA的混合液，在460nm，100mW/cm2光照下，261nm、400nm及772nm附近的紫外吸收强度均随着光照时间的延长而逐渐减低，并且光照10分钟之后，变化逐渐减慢。
从附图18中得出，对于NIR775掺杂的分子量为47000的PFBT聚合物荧光纳米探针与ADMA的混合液，在460nm，100mW/cm2光照下，261nm、400nm及772nm附近的紫外吸收强度也均随着光照时间的延长而逐渐减低，光照25分钟之后，变化逐渐减慢。
从附图19中得出，在相同的光照时间下，分子量为10 000-20000的PFBT近红外荧光纳米探针在261nm处的紫外吸收强度的变化值大于分子量为47000的PFBT近红外荧光纳米探针，并且对于分子量为10000-20000的PFBT近红外荧光纳米探针，261nm处的紫外吸收强度的变化值达到最大只需10min，而对于分子量为47000的PFBT近红外荧光纳米探针，则需25min，说明分子量为10000-20000的PFBT近红外荧光纳米探针产生单线态氧的量以及产生单线态氧的效率高于分子量为47000的PFB近红外荧光纳米探针。
实施例13:
纳米探针细胞内单线态氧的检测及细胞凋亡检测
将处于对数生长期的数量相同的NCI-H292细胞及HeLa细胞消化后分别接种到共聚焦玻璃皿(4×104个/皿)中，采用有血清的1640培养液进行培养，细胞贴壁后，移去旧的培养液，加入1mL新鲜的无血清的1640培养液，同时加入0或20μg磷脂叶酸掺杂的PFBT(分子量为10000-20000)近红外荧光纳米探针，在37℃，5％CO2条件下，共培养24h。后移去旧的培养液，用PBS清洗细胞三次，去除未被细胞吞噬的纳米颗粒，再加入1mL新鲜的无血清的1640培养液。采用460nm，功率为50mW/cm2的LED光源，连续照射加入了纳米探针的细胞20分钟，加入了纳米探针但却没有被光照的细胞以及没有加入纳米探针但却光照20分钟的细胞作为对照组。
细胞内单线态氧检测：称取3.5mg DCFH-DA，溶于721μL乙醇中(10mM)，用无血清培养液稀释成1.0mM，再将该1.0mM的溶液用无血清培养液稀释成10μM，直接使用即可。用10μM DCFH-DA溶液将上述光照后的细胞在避光条件下染色20分钟，后用PBS轻轻清洗3次，置于激光共聚焦显微镜下进行细胞成像。采用488nm 激发DCFH-DA，接收通道在510-520nm。
细胞凋亡检测：称取1mg PI溶于10mL PBS溶液中，得到100μg/mL的PI溶液，取1mL 100μg/mL的PI溶液加入到50mL PBS中，得到2μg/mL的PI溶液，直接使用即可。用2μg/mL的PI溶液将上述光照后的细胞在避光条件下染色20分钟，后用PBS轻轻清洗3次，置于激光共聚焦显微镜下进行细胞成像。采用561nm激发PI，接收通道在600-630nm。
结果：具体可以参加图20-21。DCFH-DA被细胞摄取后，转化为非荧光的DCFH，如果细胞内存在着单线态氧，则被氧化成高度荧光的DCF，通过检测DCF的信号，就可知道细胞内是否存在单线态氧；PI染料可以进入细胞膜并染色受损细胞的细胞核，而活细胞的细胞核则无法染色。因此采用DCFH-DA来检测细胞内的单线态氧，采用PI染料来检测细胞凋亡情况。从附图中得出，无纳米探针共孵育只光照20min或有纳米探针共孵育而无光照的NCI-H292细胞和HeLa细胞内均没有检测到DCF的信号以及PI的信号，而对于既有纳米探针共孵育又光照20min的NCI-H292细胞和HeLa细胞，均检测到明显的DCF绿色荧光信号和红色的PI信号。这说明在光照条件下，与纳米探针共孵育的细胞内产生了单线态氧，单线态氧对细胞造成损伤，导致了细胞的凋亡。此外，在有纳米探针共孵育的细胞内均观察到了纳米探针对应的PFBT及NIR775的信号，同样验证了纳米探针的靶向效果。
实施例14:
纳米探针细胞内光动力学毒性检测
采用CCK-8试剂盒探究纳米探针在460nm光照下对NCI-H292细胞和HeLa细胞的杀伤效果，实验步骤如下：
用胰酶将处于对数生长期的NCI-H292细胞和HeLa细胞进行消化，制作成单分散的细胞悬液，采用细胞计数板对细胞进行计数，后将细胞悬液稀释成50000个/mL，取100μL的细胞悬液(5×103个/孔)接种到96孔板中，对照组中加入100μL不含细胞的正常培养液，在37℃，5％CO2下孵育12h。
细胞贴壁后，为了促进细胞对磷脂叶酸掺杂的PFBT(分子量为10000-20000)近红外荧光纳米探针的吞噬量，从而增强光动力学效果，用无血清的1640培养液来代替旧的培养液，后向含有细胞的各孔中依次加入10μL各浓度的待测溶液，最终探针浓度分别为0、0.5、1、2.5和5μg/mL，37℃下共孵育24h。到达时间点后，移去96孔板中旧的培养液，并用PBS轻轻清洗细胞两次，以去除没有被细胞吞噬的纳米探针，后加入100μL新的培养液。采用460nm，功率为50mW/cm2的LED光源，分别照射细胞0、10、20和30min。照射结束后，向各孔中加入10μL的CCK-8溶液，37℃下孵育2小时，待溶液变色后，用酶标仪测定96孔板在450nm处的OD值。采用公式计算不同浓度的纳米探针在不同光照时间下对NCI-H292细胞和 HeLa细胞的杀伤作用。
细胞存活率的计算：细胞存活率*(％)＝[A(加药)-A(空白)]/[A(0加药)-A(空白)]×100。其中A(加药)是指具有细胞、CCK-8溶液和探针溶液的孔的吸光度，A(空白)是指具有培养基和CCK-8溶液而没有细胞的孔的吸光度，A(0加药)是指具有细胞、CCK-8溶液而没有探针溶液的孔的吸光度。
结果：具体可以参加图22-23，从附图中得出，在相同的照射剂量下，随着浓度从0增加到5μg/mL，两种细胞的细胞存活率逐渐降低，而没有被光照射的细胞显示出可忽略的细胞毒性；对于相同浓度的纳米探针，细胞存活率随着光照时间的延长而降低。当浓度和光剂量达到一定值时，两种细胞的细胞存活率存在着显著性下降(p<0.05)。当浓度低至2.5μg/mL，光照剂量为60J/cm2时，超过90％的NCI-H292细胞被杀死。此外，当光照剂量为90J/cm2时，NCI-H292和HeLa细胞的IC50值(半致死率浓度)分别为0.8μg/mL和2.43μg/mL。
实施例15:
纳米探针对皮下瘤的光动力学治疗检测
为了探究磷脂叶酸掺杂的PFBT(分子量为10000-20000)近红外荧光纳米探针对小鼠皮下瘤的光动力学治疗效果，我们选取腋下接种有NCI-H292肿瘤的小鼠进行治疗。在小鼠的肿瘤体积达到约100-150mm3后，将15只裸鼠随机分成三组(每组5只)：第一组为光照组，即仅用光照射，不注射材料；第二组为材料组，即仅接受尾静脉注射纳米探针，无光照；第三组为光动力实验组，即既接受尾静脉注射纳米探针，又接受光照射。对于需要尾静脉注射纳米探针的小鼠，每隔7天注射一次，每次注射40μg的纳米探针；对于需要接受光照射的小鼠，光源采用波长为460nm，功率为100mW/cm2的LED灯，每次照射时间为30分钟，照射部位为肿瘤部位，对于光动力实验组，在注射完材料后立即对小鼠进行照射，光动力实验组和光照组均每隔7天照射一次，总的治疗时间为28天。
每隔7天测量一次小鼠肿瘤的大小和体重，并记录。肿瘤的体积根据以下等式计算：(肿瘤长度)×(肿瘤宽度)2/2；肿瘤相对体积的计算为V/V0(V0是指初始肿瘤的体积)。在第28天治疗结束后，将所有实验小鼠安乐死，取下肿瘤及心、肝、脾、肺和肾，保存在4％多聚甲醛中，后进行HE染色，观察肿瘤部位是否有损伤及材料是否对各组织存在毒性。
结果：具体可以参加图24-26，从附图24中得出，与光照组和材料组相比，治疗后，光动力实验组中小鼠的肿瘤生长出现抑制。这些结果表明NIR775掺杂的PFBT聚合物荧光纳米探针在光照下有明显的肿瘤抑制效果。从附图25中得出，采用不同方法治疗的过程中，小鼠的体重均在正常范围内波动，无明显的异常，说明纳米探针和实验中使用的光剂量对小鼠没有明显的毒性。从附图26中得出，与 光照组和材料组相比，光动力实验组中对应的大部分肿瘤细胞呈圆形，胞核染色加深，胞质浓缩，染色质成团块状，这说明光动力实验组中更多的肿瘤细胞发生凋亡和坏死，说明光动力学疗法确实能抑制肿瘤的生长。此外在所有治疗组中，小鼠的心脏、肝脏、脾脏、肺和肾中均没有观察到明显的组织学和形态学的变化，这说明聚合物荧光纳米探针对小鼠具有较低的毒性或无毒性。
实施例16:
裸鼠淋巴转移肿瘤模型研究
腋下淋巴结(axillary lymph node，AX)转移模型的建立：将处于对数生长期的肿瘤细胞，消化离心后，分散在PBS中，配制成一定浓度的细胞悬液。将200μL肿瘤细胞悬液(2×106个/只)皮下接种到小鼠的腋下部位，约10天后长出肿瘤。
腘窝淋巴结(popliteal lymph node，PO)转移模型的建立：将处于对数生长期的肿瘤细胞，消化离心后，分散在PBS中，配制成一定浓度的细胞悬液。将40μL肿瘤细胞悬液(2×106个/只)皮下接种到小鼠后腿的肉垫，约10天后长出肿瘤。
为了验证淋巴结转移模型，将肿瘤组织，腋下淋巴结(axillary lymph node，AX)，腘窝淋巴结(popliteal lymph node，PO)，髋部淋巴结(sciatic lymph node，SC)，腹股沟淋巴结(inguinal lymph node，IN)，固定进行石蜡包埋，以及苏木精和伊红染色，Anti-VEGFA抗体(ab46154)染色，并通过光学显微镜获取组织切片的图像。
结果：具体可以参加图27-36，从附图中得出，对于腋下接种的NCI-H292肿瘤，其前哨淋巴结腋下淋巴结AX可检测出转移的肿瘤细胞；对于脚肉垫接种的NCI-H292肿瘤，其前哨淋巴结腘窝淋巴结PO，二级淋巴结髋部淋巴结SC，以及腹股沟淋巴结IN检测出转移的肿瘤细胞。结果证实淋巴转移肿瘤模型的建立。
实施例17:
纳米探针的荧光成像研究
当NCI-H292脚垫肿瘤直径达到5-8mm时，将磷脂叶酸掺杂的PFBT近红外荧光纳米共轭聚合物纳米探针同时注射到小鼠的两只脚肉垫，观察纳米探针对淋巴结转移的靶向情况。采用PerkinElmer公司的IVIS Lumina XRMS Series III成像系统对小鼠进行活体成像。激发光源采用460nm，接收通道选择780nm的滤光片。
结果：具体可以参加图37-39，从附图37中得出，肿瘤直径达到5mm时，经脚肉垫注射近红外荧光聚合物纳米探针2小时后，在肿瘤一侧的腘窝淋巴结PO检测到探针的近红外信号，而在对侧PO没有探针的信号，当把小鼠的皮肤切开，以及把两个PO取出来，证实只在肿瘤一侧的PO检测出探针的近红外荧光信号。结果证实该纳米探针可特异性靶向成像发生肿瘤转移的PO淋巴结。从附图38中得 出，肿瘤直径达到～8mm时，经脚肉垫注射近红外荧光聚合物纳米探针不同时间，在肿瘤一侧的腘窝淋巴结PO以及髋部淋巴结SC均检测到探针的近红外信号，而在对侧PO及SC均没有探针的信号，当把小鼠的皮肤切开，以及把淋巴结取出来，证实只在肿瘤一侧的PO和SC检测出探针的近红外荧光信号。结果证实该纳米探针可特异性靶向成像发生肿瘤转移的PO和SC淋巴结。从附图39中得出，肿瘤直径达到～8mm时，经脚肉垫注射近红外荧光聚合物纳米探针20天后，仍然可以检测出肿瘤一侧的腘窝淋巴结PO以及髋部淋巴结SC的荧光信号。证实该纳米探针在淋巴结长时间的滞留。
实施例18:
纳米探针的光声成像研究
当NCI-H292脚垫肿瘤直径达到5-8mm时，将磷脂叶酸掺杂的PFBT近红外荧光纳米共轭聚合物纳米探针同时注射到小鼠的两只脚肉垫，观察纳米探针对淋巴结转移的靶向情况。对于小动物活体光声成像，采用德国iThera Medical公司的MSOT实时扫描仪(MSOT inVision 128)进行扫描。激发波段从680-800nm，每隔10nm选取一个激发峰，扫描步径为0.2mm。选取最佳激发波长770nm处的数据，基于反投影算法重建图像。
结果：具体可以参加图40-41，从附图40中得出，经脚肉垫注射近红外荧光聚合物纳米探针后，在腘窝淋巴结PO，髋部淋巴结SC，以及淋巴管检测到探针的光声信号。在注射4小时后，从附图41中得出，在腘窝淋巴结PO，髋部淋巴结SC，以及腹股沟淋巴结IN检测到探针的光声信号。
实施例19:
纳米探针的磁共振成像、近红外荧光成像研究
采用7.05T MRI系统(Biospec System70/20，Brucker，Ettlingen，Germany)进行扫描，线圈直径为40mm，扫描模式为T1加权成像。对于带有脚肉垫NCI-H292肿瘤模型的小鼠，脚肉垫注射同时掺钆磁共振造影剂DTPA-BSA(Gd)和磷脂叶酸的近红外荧光共轭聚合物纳米探针，分别扫描注射探针前后的磁共振信号，扫描参数设置为：TE＝6ms，TR＝1500ms，Flip Angle＝90deg，Slice Thickness＝1mm，Field＝7.05T，DFOV＝25mm。通过ImageJ软件导出MRI图片并进行数据分析。MRI实验结束后，实验小鼠进一步用荧光成像系统扫描，验证探针的信号分布。荧光成像采用PerkinElmer公司的IVIS Lumina XRMS Series III成像系统。激发光源采用460nm，接收通道选择780nm的滤光片。
结果：具体可以参见图42、43，从附图中得出，经脚肉垫注射Gd3+杂化的近红外荧光聚合物纳米探针后，在腘窝淋巴结PO，髋部淋巴结SC，腹股沟淋巴结 IN检测出探针的磁共振信号和近红外荧光信号。
实施例20:
纳米探针的磁共振、近红外荧光成像研究
采用7.05T MRI系统(Biospec System70/20，Brucker，Ettlingen，Germany)进行扫描，线圈直径为40mm，扫描模式为T1加权成像。对于带有腋下NCI-H292肿瘤模型的小鼠，尾静脉注射同时掺钆磁共振造影剂DTPA-BSA(Gd)和磷脂叶酸的近红外荧光共轭聚合物纳米探针，分别扫描注射探针前后的磁共振信号，扫描参数设置为：TE＝6ms，TR＝1500ms，Flip Angle＝90deg，Slice Thickness＝1mm，Field＝7.05T，DFOV＝25mm。通过ImageJ软件导出MRI图片并进行数据分析。MRI实验结束后，实验小鼠进一步用荧光成像系统扫描，验证探针的信号分布。荧光成像采用PerkinElmer公司的IVIS Lumina XRMS Series III成像系统。激发光源采用460nm，接收通道选择780nm的滤光片。
结果：具体可以参加图44，从附图中得出，经尾静脉注射Gd3+杂化的近红外荧光聚合物纳米探针后，在肿瘤组织及两个腋下淋巴结AX检测出探针的磁共振信号和近红外荧光信号。
实施例21:
纳米探针的荧光成像研究
当HeLa脚垫肿瘤直径达到5-8mm时，将磷脂叶酸掺杂的PFBT近红外荧光纳米共轭聚合物纳米探针同时注射到小鼠的两只脚肉垫，观察纳米探针对淋巴结转移的靶向情况。采用PerkinElmer公司的IVIS Lumina XRMS Series III成像系统对小鼠进行活体成像。激发光源采用460nm，接收通道选择780nm的滤光片。
结果：具体可以参加图45，从附图中得出，经脚肉垫注射近红外荧光聚合物纳米探针不同时间，在肿瘤一侧的腘窝淋巴结PO检测到探针的近红外信号，而在对侧PO没有探针的信号，当把小鼠的皮肤切开，以及把两个PO取出来，证实只在肿瘤一侧的PO检测出探针的近红外荧光信号。结果证实该纳米探针可特异性靶向成像发生肿瘤转移的PO淋巴结。
以上详细描述了本发明的较佳具体实施例。应当理解，本领域的普通技术无需创造性劳动就可以根据本发明的构思作出诸多修改和变化。因此，凡本技术领域中技术人员依本发明的构思在现有技术的基础上通过逻辑分析、推理或者有限的实验可以得到的技术方案，皆应在由权利要求书所确定的保护范围内。

Claims (48)

  1. 一种共轭聚合物纳米探针，其特征在于，包括：
    荧光共轭聚合物；
    表面配体；
    靶分子；
    近红外荧光染料。
  2. 如权利要求1所述的共轭聚合物纳米探针，其特征在于，所述靶分子能识别叶酸受体。
  3. 如权利要求2所述的共轭聚合物纳米探针，其特征在于，所述靶分子为磷脂修饰的靶分子。
  4. 如权利要求3所述的共轭聚合物纳米探针，其特征在于，所述磷脂修饰为使用脂质体修饰。
  5. 如权利要求4所述的共轭聚合物纳米探针，其特征在于，所述磷脂修饰的靶分子为磷脂酰乙醇胺-聚乙二醇5000-叶酸交连物、磷脂酰乙醇胺-聚乙二醇2000-叶酸交连物和磷脂酰乙醇胺-叶酸交连物中的一种或多种。
  6. 如权利要求1所述的共轭聚合物纳米探针，其特征在于，所述表面配体为末端羧基修饰的表面配体。
  7. 如权利要求6所述共轭聚合物纳米探针，其特征在于，所述表面配体选自苯乙烯-聚乙二醇-羧基、聚乙二醇-羧基、苯乙烯-顺丁烯二酸酐共聚物或其组合。
  8. 如权利要求1所述共轭聚合物纳米探针，其特征在于，所述近红外荧光染料的吸收波长在700～900nm之间。
  9. 如权利要求8所述共轭聚合物纳米探针，其特征在于，所述近红外荧光染料选自NIR775、DiIC18、ICG、Cy7或Cy7.5。
  10. 如权利要求1所述的共轭聚合物纳米探针，其特征在于，所述荧光共轭聚合物选自PFBT或MEH-PPV。
  11. 如权利要求10所述的共轭聚合物纳米探针，其特征在于，所述PFBT分子量在10000～52000之间，所述MEH-PPV分子量在Mw＝10142～200000。
  12. 如权利要求1-11中任一项所述的共轭聚合物纳米探针，其特征在于，所述近红外荧光染料与所述荧光共轭聚合物的重量比在0.2％-1.2％之间，所述表面配体与所述荧光共轭聚合物的重量比在0.5-2之间，所述靶分子与所述荧光共轭聚合物的重量比在0.2-1之间。
  13. 如权利要求1-11中任一项所述的共轭聚合物纳米探针，其特征在于，透射电镜显示其平均粒径大小分布为2～100nm。
  14. 如权利要求13所述的共轭聚合物纳米探针，其特征在于，透射电镜显示其平 均粒径大小分布为20～60nm之间。
  15. 如权利要求1-11中任一项所述的共轭聚合物纳米探针，其特征在于，还包括含钆磁共振造影剂。
  16. 如权利要求15所述的共轭聚合物纳米探针，其特征在于，所述含钆磁共振造影剂为磷脂修饰的钆。
  17. 如权利要求16所述的共轭聚合物纳米探针，其特征在于，所述磷脂修饰的钆为磷脂修饰的钆的二乙烯二胺五醋酸络合物。
  18. 如权利要求17所述的共轭聚合物纳米探针，其特征在于，所述磷脂修饰的钆的二乙烯二胺五醋酸络合物选自DTPA-BSA(Gd)、bis(18:0 PE)-DTPA(Gd)、bis(16:0 PE)-DTPA(Gd)、bis(14:0 PE)-DTPA(Gd)、18:0 PE-DTPA(Gd)、16:0 PE-DTPA(Gd)或其组合物。
  19. 如权利要求15所述的共轭聚合物纳米探针，其特征在于，所述近红外荧光染料与所述荧光共轭聚合物的重量比在0.2％-1.2％之间，所述表面配体与所述荧光共轭聚合物的重量比在0.5-2之间，所述靶分子与所述荧光共轭聚合物的重量比在0.2-1之间，所述含钆磁共振造影剂与所述荧光聚合物的重量比在3-5之间。
  20. 如权利要求15所述的共轭聚合物纳米探针，其特征在于，透射电镜显示其平均粒径分布为20～130nm。
  21. 如权利要求20所述的共轭聚合物纳米探针，其特征在于，透射电镜显示其平均粒径分布为30～60nm之间。
  22. 一种共轭聚合物纳米探针的制备方法，其特征在于，所述共轭聚合物纳米探针如权利要求1-14中任一项所述，所述方法包括：
    1)在有机溶剂中加入所述荧光共轭聚合物、所述表面配体、所述近红外荧光染料和所述靶分子，超声混合获得混合液；
    2)在超声条件下，将上述混合液加到超纯水中，继续超声。
  23. 如权利要求22所述的共轭聚合物纳米探针的制备方法，其特征在于，所述共轭聚合物纳米探针如权利要求15-21中任一项所述，所述方法还包括，在步骤1)中，在有机溶剂中还添加了所述含钆磁共振造影剂。
  24. 如权利要求22所述的共轭聚合物纳米探针的制备方法，其特征在于，所述靶分子为磷脂修饰的靶分子。
  25. 如权利要求23所述的共轭聚合物纳米探针的制备方法，其特征在于，所述含钆磁共振造影剂为为磷脂修饰的钆。
  26. 如权利要求22或23所述的共轭聚合物纳米探针的制备方法，其特征在于，步骤2)中，所述超声的功率设置为8-12％，每超声4-6秒停2-4秒，超声时间设置为50-70秒。
  27. 如权利要求23所述的共轭聚合物纳米探针的制备方法，其特征在于，所述含 钆磁共振造影剂与所述荧光聚合物的重量比在3-5之间。
  28. 如权利要求22或23所述的共轭聚合物纳米探针的制备方法，其特征在于，步骤1)中所述有机溶剂为四氢呋喃溶液或氯仿。
  29. 如权利要求22或23所述的共轭聚合物纳米探针的制备方法，其特征在于，步骤1)中，所述近红外荧光染料与所述荧光共轭聚合物的重量比在0.2-1.2％之间，所述表面配体与所述荧光共轭聚合物的重量比在0.5-2之间，所述靶分子与所述荧光共轭聚合物的重量比在0.2-1之间。
  30. 如权利要求22或23所述的共轭聚合物纳米探针的制备方法，其特征在于，所述方法在步骤2)之后，还包括：3)在加热条件下通入氮气使有机溶剂挥发，得到所述共轭聚合物纳米探针。
  31. 如权利要求30所述的共轭聚合物纳米探针的制备方法，其特征在于，步骤3)中，所述加热条件为在45-55℃。
  32. 一种共轭聚合物纳米探针在制备分子影像试剂中的应用，其特征在于，所述共轭聚合物纳米探针如权利要求1-14中任一项所述，所述共轭聚合物纳米探针能进行近红外荧光成像和/或光声成像。
  33. 如权利要求32所述的共轭聚合物纳米探针在制备分子影像试剂中的应用，其特征在于，所述共轭聚合物纳米探针如权利要求15-21中任一项所述，所述共轭聚合物纳米探针能进行近红外荧光成像、光声成像和/或磁共振成像。
  34. 如权利要求32或33所述的共轭聚合物纳米探针在制备分子影像试剂中的应用，其特征在于，所述共轭聚合物纳米探针能在细胞层次靶向成像叶酸受体表达的肿瘤细胞。
  35. 如权利要求32或33所述的共轭聚合物纳米探针在制备分子影像试剂中的应用，其特征在于，所述共轭聚合物纳米探针能识别发生肿瘤转移的淋巴结和正常淋巴结。
  36. 如权利要求35所述的共轭聚合物纳米探针在制备分子影像试剂中的应用，其特征在于，所述共轭聚合物纳米探针能在小动物活体层次识别发生肿瘤转移的淋巴结和正常淋巴结。
  37. 一种分子影像试剂，其特征在于，所述分子影像试剂包括如权利要求1-14中任一项所述的共轭聚合物纳米探针，或包括如15-21中任一项所述共轭聚合物纳米探针。
  38. 一种共轭聚合物纳米探针在制备光动力治疗试剂中的应用，其特征在于，所述共轭聚合物纳米探针如权利要求1-14中任一项所述，或如权利要求15-21中任一项所述。
  39. 如权利要求38所述的共轭聚合物纳米探针在制备光动力治疗试剂中的应用，其特征在于，所述共轭聚合物纳米探针包括近红外荧光染料，所述近红外荧光染料 在光照下能产生活性氧。
  40. 如权利要求39所述的共轭聚合物纳米探针在制备光动力治疗试剂中的应用，其特征在于，所述近红外荧光染料为含有四吡咯基结构的近红外染料。
  41. 如权利要求39所述的共轭聚合物纳米探针在制备光动力治疗试剂中的应用，其特征在于，所述近红外荧光染料为NIR775。
  42. 一种光动力治疗试剂，其特征在于，所述光动力治疗试剂包括如权利要求1-14中任一项所述的共轭聚合物纳米探针，或包括如15-21中任一项所述共轭聚合物纳米探针。
  43. 如权利要求42所述的光动力治疗试剂，其特征在于，所述共轭聚合物纳米探针包括近红外荧光染料，所述近红外荧光染料在光照下能产生活性氧。
  44. 如权利要求43所述的光动力治疗试剂，其特征在于，所述近红外荧光染料为含有四吡咯基结构的近红外染料。
  45. 如权利要求44所述的光动力治疗试剂，其特征在于，所述近红外荧光染料为NIR775。
  46. 如权利要求42所述的光动力治疗试剂，其特征在于，所述光动力治疗试剂能用于肿瘤的光动力学治疗。
  47. 如权利要求42所述的光动力治疗试剂，其特征在于，所述光动力治疗试剂能在细胞层次和小动物活体层次杀死肿瘤细胞。
  48. 如权利要求46所述的光动力治疗试剂，其特征在于，所述肿瘤为皮下实体瘤。
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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3883612A4 (en) * 2018-11-21 2021-09-29 The University Of Georgia Research Foundation, Inc. BIMODAL NANOPARTICLE CONJUGATES FOR NON-INVASIVE TISSUE IMAGING OF THE CENTRAL NERVOUS SYSTEM
WO2022257855A1 (zh) * 2021-06-07 2022-12-15 青岛科技大学 一种可实现靶向光热和化学协同治疗的h-BN/MoS2纳米探针及其制备方法和应用

Families Citing this family (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN109529059A (zh) * 2018-12-26 2019-03-29 中南大学 一种荧光-磁共振双模态量子点及其制备和应用方法
CN109943319A (zh) * 2019-02-28 2019-06-28 南京邮电大学 一种近红外二区荧光材料及可用于多模态诊疗的纳米颗粒与磁性纳米颗粒
CN110283327B (zh) * 2019-06-28 2021-07-09 齐鲁工业大学 一种共轭聚合物纳米粒子荧光探针及其应用
CN112007173B (zh) * 2020-08-21 2021-07-30 上海交通大学 一种荧光共轭聚合物纳米探针在周围神经成像中的应用
CN113713123B (zh) * 2021-08-26 2022-09-23 上海交通大学 用于脑部淋巴系统和血管成像的荧光共轭聚合物纳米探针
CN114231276B (zh) * 2021-12-29 2023-06-20 北京建工环境修复股份有限公司 一种荧光共轭聚合物量子点探针和全氟化合物检测方法
CN114410293B (zh) * 2022-01-11 2024-03-19 苏州大学 一种高灵敏度硫化氢响应型纳米探针及其制备方法和应用
CN114350755B (zh) * 2022-01-17 2024-04-09 吉林大学 基于半导体聚合物点的高灵敏度microRNA荧光原位杂交定量标记探针及其制备方法
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CN115025249B (zh) * 2022-05-12 2024-02-20 深圳市第二人民医院(深圳市转化医学研究院) 靶向探针及其制备方法和应用
CN115093548B (zh) * 2022-06-29 2024-05-10 南京邮电大学 一种自降解共轭聚合物、纳米粒子及其制备方法和应用
CN115737811B (zh) * 2022-11-30 2024-11-22 重庆医科大学附属口腔医院 一种鳞癌细胞膜包覆纳米粒及其制备方法和应用
CN116173208B (zh) * 2023-03-06 2024-10-01 河北工业大学 阳离子共轭聚电解质pfbt在光动力选择性抗菌方面的应用
CN117538537B (zh) * 2023-11-10 2025-10-10 中国医学科学院阜外医院深圳医院(深圳市孙逸仙心血管医院) 检测趋化因子配体9的试剂在制备心肌炎早期检测产品中的应用
CN118852634A (zh) * 2024-08-02 2024-10-29 广东云曌医疗科技有限公司 一种生物兼容性有机半导体共轭聚合物点材料仿生材料及其制备方法

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013154736A1 (en) * 2012-04-12 2013-10-17 The Board Of Trustees Of The Leland Ret2ir conjugates, ret2ir conjugate systems and methods of use thereof
CN106474492A (zh) * 2015-09-02 2017-03-08 华东理工大学 腺苷5′-单磷酸介导的靶向肿瘤的纳米传递系统的构建与应用

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106519588B (zh) * 2009-11-09 2019-08-20 华盛顿大学商业化中心 官能化发色聚合物点及其生物共轭体
JP2014129317A (ja) * 2012-02-23 2014-07-10 Canon Inc 光音響造影剤用色素含有ナノ粒子
CN105012970B (zh) * 2015-07-21 2018-05-29 福州市传染病医院 用于肿瘤早期诊断与光学治疗的多功能纳米胶束及其应用

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013154736A1 (en) * 2012-04-12 2013-10-17 The Board Of Trustees Of The Leland Ret2ir conjugates, ret2ir conjugate systems and methods of use thereof
CN106474492A (zh) * 2015-09-02 2017-03-08 华东理工大学 腺苷5′-单磷酸介导的靶向肿瘤的纳米传递系统的构建与应用

Non-Patent Citations (3)

* Cited by examiner, † Cited by third party
Title
CAO FENGWEN ET AL.: "Folic acid functionalized PFBTfluorescent polymer dots for tumor imaging", CHIN. J. CHEM., vol. 34, no. 6, 3 February 2016 (2016-02-03), pages 570 - 575, XP055540149 *
XIONG LIQIN ET AL.: "Long-term-stable near-infrared polymer dots with ultrasmall size and narrow-band emission for imaging tumor vasculature in vivo", BIOCONJUGATE CHEMISTRY, vol. 26, no. 5, 20 May 2015 (2015-05-20), pages 817 - 821, XP055540150 *
XIONG, LIQIN ET AL.: "Self-luminescing BRET-FRET near-infrared dots for in vivo lymph-node mapping and tumour imaging", NATURE COMMUNICATIONS, vol. 3, 13 November 2012 (2012-11-13), pages 1 - 9 *

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3883612A4 (en) * 2018-11-21 2021-09-29 The University Of Georgia Research Foundation, Inc. BIMODAL NANOPARTICLE CONJUGATES FOR NON-INVASIVE TISSUE IMAGING OF THE CENTRAL NERVOUS SYSTEM
WO2022257855A1 (zh) * 2021-06-07 2022-12-15 青岛科技大学 一种可实现靶向光热和化学协同治疗的h-BN/MoS2纳米探针及其制备方法和应用

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