WO2023082786A1 - 前列腺癌靶向磁共振造影剂及应用 - Google Patents

前列腺癌靶向磁共振造影剂及应用 Download PDF

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WO2023082786A1
WO2023082786A1 PCT/CN2022/116541 CN2022116541W WO2023082786A1 WO 2023082786 A1 WO2023082786 A1 WO 2023082786A1 CN 2022116541 W CN2022116541 W CN 2022116541W WO 2023082786 A1 WO2023082786 A1 WO 2023082786A1
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peg
gmnps
prostate cancer
psma
contrast agent
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杨志
夏雷
朱华
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北京肿瘤医院(北京大学肿瘤医院)
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00—Preparations for testing in vivo
    • A61K49/06—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/08—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by the carrier
    • A61K49/10—Organic compounds
    • A61K49/12—Macromolecular compounds
    • A61K49/126—Linear polymers, e.g. dextran, inulin, PEG
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00—Preparations for testing in vivo
    • A61K49/06—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/08—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by the carrier
    • A61K49/085—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by the carrier conjugated systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00—Preparations for testing in vivo
    • A61K49/06—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/08—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by the carrier
    • A61K49/10—Organic compounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00—Preparations for testing in vivo
    • A61K49/06—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/18—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes
    • A61K49/1818—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles
    • A61K49/1821—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles
    • A61K49/1824—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles
    • A61K49/1827—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle
    • A61K49/1851—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle having a (super)(para)magnetic core coated or functionalised with an organic macromolecular compound, i.e. oligomeric, polymeric, dendrimeric organic molecule
    • A61K49/1857—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle having a (super)(para)magnetic core coated or functionalised with an organic macromolecular compound, i.e. oligomeric, polymeric, dendrimeric organic molecule the organic macromolecular compound being obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. PLGA
    • A61K49/186—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle having a (super)(para)magnetic core coated or functionalised with an organic macromolecular compound, i.e. oligomeric, polymeric, dendrimeric organic molecule the organic macromolecular compound being obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. PLGA the organic macromolecular compound being polyethyleneglycol [PEG]
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B82—NANOTECHNOLOGY
    • B82Y—SPECIFIC USES OR APPLICATIONS OF NANOSTRUCTURES; MEASUREMENT OR ANALYSIS OF NANOSTRUCTURES; MANUFACTURE OR TREATMENT OF NANOSTRUCTURES
    • B82Y15/00—Nanotechnology for interacting, sensing or actuating, e.g. quantum dots as markers in protein assays or molecular motors
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B82—NANOTECHNOLOGY
    • B82Y—SPECIFIC USES OR APPLICATIONS OF NANOSTRUCTURES; MEASUREMENT OR ANALYSIS OF NANOSTRUCTURES; MANUFACTURE OR TREATMENT OF NANOSTRUCTURES
    • B82Y5/00—Nanobiotechnology or nanomedicine, e.g. protein engineering or drug delivery

Definitions

  • the invention belongs to the fields of radiation medicine, molecular imaging and nanomedicine, and in particular relates to a prostate cancer targeting magnetic resonance contrast agent, the application of the magnetic resonance contrast agent, and a prostate cancer targeting molecule whose active ingredient is a magnetic resonance contrast agent Probes, and kits comprising magnetic resonance contrast agents or molecular probes.
  • MRI contrast agents Compared with the emerging magnetic resonance imaging (MRI) technology, the update and development of MRI contrast agents is slower. This is due to the low sensitivity of traditional MRI contrast agents, and the risk of toxic effects caused by a large amount of contrast agents is relatively high.
  • Commonly used magnetic resonance contrast agents are mainly paramagnetic substances and superparamagnetic substances.
  • Gd-DTPA which is widely used in clinical practice, is considered to be prone to side effects such as renal fibrosis, and its disadvantages are gradually revealed, and Gd-DTPA does not have the target tropism, poor tumor specificity.
  • SPIONs Superparamagnetic iron oxide nanoparticles
  • SPIONs as an emerging T2-weighted negative contrast agent, have been used in MRI imaging of liver cancer and other tumors, but as metal nanoparticles, SPIONs also have safety problems such as difficult degradation, which greatly affects its clinical transformation. efficiency.
  • the research on molecular imaging mostly focuses on integrating the advantages of multiple technologies to construct molecular probes with higher imaging efficiency, better safety and wider application.
  • PSMA prostate-specific membrane antigen
  • MRI contrast agent a tumor-targeted magnetic resonance contrast agent based on melanin nanoparticles
  • prostate cancer-specific enhanced MRI imaging can be used to improve the application range and diagnostic accuracy of MRI contrast.
  • the combination of tumor-targeted drugs and nanotechnology will be a research hotspot in the development of new diagnostic and therapeutic drugs in the future.
  • the purpose of the present invention is to provide a prostate cancer targeting magnetic resonance contrast agent and its application.
  • the contrast agent can specifically bind to the PSMA membrane antigen on the surface of prostate cancer cells, and use the T1-weighted enhanced contrast function of the nanoprobe for MRI imaging. Since a large number of gadolinium ions are confined in the nanoparticle, it promotes the recovery of protons from high-energy states to The speed of low-energy state conversion shortens the relaxation time and obviously improves the enhancement efficiency of the contrast agent.
  • the contrast agent of the present invention can be used to achieve the purpose of tumor-targeted magnetic resonance enhanced contrast.
  • the first aspect of the present invention provides a prostate cancer-targeted magnetic resonance contrast agent.
  • the preparation method of the prostate cancer-targeting magnetic resonance contrast agent includes: firstly, the bio-extracted melanin is polymerized into MNPs, and gadolinium salt, bisaminopolyethylene glycol are added during the process.
  • MNPs are organic melanin nanoparticles; the average particle size of the nanoparticles is 11-20nm;
  • the gadolinium salt is gadolinium chloride hexahydrate
  • the bisamino polyethylene glycol is NH 2 -PEG n -NH 2 , and the molecular weight of PEG n is 200-20000Da.
  • PEG-GMNPs are paramagnetic melanin nanoparticles, the average particle size of the nanoparticles is 15nm, and the molecular weight is about 40KDa.
  • the preparation method is described in the literature (Lei Xia, Xiangxi Meng, Li Wen, et al. A Highly Specific Multiple Enhancement Theranostic Nanoprobe for PET/MRI/PAI Image-Guided Radioisotope Combined Photothermal Therapy in Prostate Cancer. Small. 2021, 17(21) : e2100378) on the basis of improvement, one-step method to obtain paramagnetic nanoparticles.
  • the paramagnetic nanoparticles PEG-GMNPs with amino groups on the surface are obtained in one step, which specifically includes the following steps:
  • using the cross-linking agent Sulfo-SMCC to modify the amino groups on the surface of PEG-GMNPs and coupling SMCC-PEG-GMNPs with sulfhydrylated PSMA targeting groups PSMA-SH includes the following steps :
  • the use of PEG with different molecular weights to modify nanoparticles will slightly affect the pharmacokinetic results of the probe.
  • the bisaminopolyethylene glycol is NH 2 -PEG 5000 -NH 2 .
  • the tumor-targeted MRI contrast agent of the present invention can be used for targeted MRI contrast of PSMA receptor highly expressed prostate cancer.
  • the second aspect of the present invention provides the application of the above-mentioned prostate cancer-targeting magnetic resonance contrast agent in the preparation of prostate cancer-targeting molecular probes.
  • the third aspect of the present invention provides a prostate cancer-targeting molecular probe, the active ingredient of which is the above-mentioned prostate cancer-targeting magnetic resonance contrast agent.
  • the fourth invention of the present invention provides a kit comprising the above-mentioned prostate cancer-targeting magnetic resonance contrast agent, or the above-mentioned prostate cancer-targeting molecular probe.
  • PSMA-GMNPs can accurately locate PSMA receptor-positive prostate cancer, and after intravenous injection, it will be significantly enriched at the tumor site and stay for a long time .
  • PSMA-GMNPs can significantly enhance the T1-weighted signal intensity of PSMA receptor-positive solid tumors.
  • the present invention uses melanin nanoparticles (MNPs) with excellent biological properties as a carrier, fuses highly paramagnetic metal gadolinium ions in one step, and modifies PEG on the surface of the nanoparticles to construct magnetic nanoparticles PEG-GMNPs, which can target prostate cancer
  • MNPs melanin nanoparticles
  • a small molecule inhibitor of PSMA was coupled with nanoparticles to obtain a novel prostate cancer-targeted MRI contrast agent PSMA-GMNPs, which has a high relaxation rate and can specifically bind to the surface-specific membrane antigen PSMA of prostate cancer , through MRI-enhanced contrast imaging to accurately locate PSMA high-expression tumor tissue and metastases, to achieve the purpose of targeted molecular imaging diagnosis of prostate cancer, so as to achieve the goals of early detection, early diagnosis and early treatment of tumors.
  • Fig. 1 is a schematic diagram of the synthesis process of the prostate cancer-targeted MRI contrast agent of the present invention.
  • Fig. 2 is a pharmacokinetic experiment of a prostate cancer-targeted MRI contrast agent in Test Example 1 of the present invention.
  • Fig. 3 is a high-resolution transmission electron microscope scanning image of PEG-GMNPs in Example 1 of the present invention.
  • Figure 4 is the cell uptake and competition experiment in Test Example 2 of the present invention
  • the left side is the comparison of the uptake experiment of the prostate cancer targeting MRI contrast agent of the present invention in the positive cell LNCaP and the negative cell PC-3
  • the right side is the prostate cancer target Competitive inhibition experiments of LNCaP in positive cells to MRI contrast agents.
  • Fig. 5 is an in vitro MRI-enhanced imaging of prostate cancer-targeted MRI contrast agents in Test Example 3 of the present invention after binding different metals.
  • Fig. 6 is the in vitro MRI-enhanced relaxation rate detection of prostate cancer-targeted MRI contrast agents in Test Example 3 of the present invention after binding different metals.
  • Fig. 7 is a schematic diagram of enhanced MRI imaging of prostate cancer-targeting MRI contrast agent PSMA-GMNPs in PSMA-positive model LNCaP tumor-bearing mice in Test Example 4 of the present invention, and the white circle outlines the tumor outline.
  • Fig. 8 is a curve diagram of the MRI signal change curve of the tumor site in the imaging of PSMA-positive model LNCaP tumor-bearing mice with the prostate cancer-targeted MRI contrast agent PSMA-GMNPs in Test Example 4 of the present invention.
  • the preparation of prostate cancer-targeted MRI contrast agent PSMA-GMNPs includes the following steps:
  • SMCC-PEG-GMNPs 5.5 mg were mixed with thiol-modified PSMA (1.8-2.7 mg) according to the molar ratio of SMCC-PEG-GMNPs to thiol-modified PSMA targeting groups of 1:20-30, The reaction was stirred at room temperature for 12-24 hours, and after the reaction was completed, it was purified with a PD-10 column to obtain pure prostate cancer-targeting MRI contrast agent PSMA-GMNPs.
  • the preparation method is the same as in Example 1, except that the diaminopolyethylene glycol with a molecular weight of 5000Da used in step 1 is replaced with a diaminopolyethylene glycol with a molecular weight of 200-20000Da, and the rest of the reaction conditions are the same.
  • the preparation method is the same as in Example 1, only the gadolinium salt GdCl 3 6H 2 O in step 1 is replaced by iron salt FeCl 3 6H 2 O or manganese salt MnCl 2 4H 2 O, and the molar weight of the metal salt is still excessive compared with melanin , and the rest of the reaction conditions were the same.
  • the obtained PSMA-Fe-MNPs and PSMA-Mn-MNPs were synthesized.
  • mice Take 5 normal BALB/c mice (all male, 4 weeks old, 16-18g), dilute a certain amount of PSMA-GMNPs with normal saline (30 ⁇ M), inject 200 ⁇ L of contrast medium through the tail vein of each mouse, and Strictly record the injection time. After the mice were injected with the drug through the tail vein, blood was taken from the fundus vein using a capillary blood needle at 1min, 3min, 5min, 10min, 15min, 30min, 60min, 2h, 8h, 24h, and 48h, and placed in a place where citric acid was added. Sodium in a test tube.
  • the blood mass in the test tube was weighed, the Gd 3+ content of the sample was detected by ICP-MS, and 1% of the injected drug amount of each mouse was taken as a reference marker for determination.
  • the results were shown by the percentage of gadolinium ion content in unit tissue to the total injected dose (%ID/g), and the biological half-life of the drug was calculated after attenuation correction using the analysis software.
  • Fig. 2 The results showed (Fig. 2): The drug metabolism-time curve of PSMA-GMNPs conformed to the two-compartment model, and the half-lives of the distribution phase and clearance phase were 0.13h and 6.71h, respectively.
  • 3.0T MR imaging equipment was used to detect the magnetic resonance enhancement function and T1-weighted relaxation rate of prostate cancer-targeted MRI contrast agents, and compared the different concentrations of PSMA-Fe-MNPs, PSMA-Mn-MNPs and common magnetic resonance imaging described in Example 1.
  • the in vitro T1-weighted magnetic resonance imaging and relaxation efficiency of the contrast agent Gd-DTPA were compared.
  • the T1-weighted in vitro imaging results of different concentrations of MRI contrast agents in Figure 5 show that at the same concentration, the T1-weighted signal intensity of PSMA-GMNPs is the highest, followed by PSMA-Mn-MNPs, PSMA- 3+ Fe-MNPs, PSMA- 2 + Fe-MNPs, Gd-DTPA.
  • the T1-weighted relaxation efficiency line graph (Fig. 6) shows that the T1-weighted relaxation rate of PSMA-GMNPs is significantly higher than that of the commonly used magnetic resonance contrast agent Gd-DTPA, which is about 5 times that.
  • LNCaP tumor-bearing mice with a tumor diameter of 0.8-1 cm were taken, and each mouse was injected with a certain amount of PSMA-GMNPs (prepared in Example 1) physiological saline dilution (30 ⁇ M, 200 ⁇ L) through the tail vein, using a 3.0T MR imager with a small animal coil , before drug injection, 2h, 24h, 72h, and 168h after drug injection, MRI T1-weighted imaging acquisition was carried out, and the MR sequence information was: TR (repetition time): 531ms, TE (echo time): 9.1ms; flip angle ( flip angle): 30°; FOV (scanning field of view): 160 ⁇ 100mm 2 ; scanning matrix (matrix): 256 ⁇ 256; scanning layer thickness (slice thickness): 3mm, the imaging results are shown in Figure 7, the results show that PSMA-GMNPs After 2 hours of tail vein injection, the whole-body MR signals of LNCaP tumor-bearing
  • the T1-weighted MRI signal of the tumor site was significantly enhanced at 24 hours, and at 72 hours, the enhanced MRI contrast could clearly locate the tumor location, and the internal enhanced signal was obvious.
  • MRI-enhanced scanning was performed again 7 days after administration, and the tumor site still showed clear MRI-enhanced signals, which proved the strong retention function of the probe. The experiment proved that PSMA-GMNPs probe can be used for PSMA-high expression prostate cancer-specific MRI-enhanced contrast.

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Abstract

本发明属于放射医学、分子影像学以及纳米医学领域，涉及一种前列腺癌靶向磁共振造影剂及应用。所述前列腺癌靶向磁共振造影剂的制备方法包括：先将生物提取黑色素聚合成为MNPs，在此过程中添加钆盐、双氨基聚乙二醇，一步法获得表面带有氨基的顺磁性纳米粒PEG-GMNPs，然后使用交联剂Sulfo-SMCC对PEG-GMNPs表面上的氨基进行修饰，得到SMCC-PEG-GMNPs，最后将SMCC-PEG-GMNPs与巯基化的PSMA靶向基团PSMA-SH偶联，制得前列腺癌靶向磁共振造影剂PSMA-GMNPs。本发明的造影剂可用于实现肿瘤的靶向磁共振增强造影目的。

Description

前列腺癌靶向磁共振造影剂及应用 技术领域
本发明属于放射医学、分子影像学以及纳米医学领域，具体地，涉及一种前列腺癌靶向磁共振造影剂、该磁共振造影剂的应用、有效成分为磁共振造影剂的前列腺癌靶向分子探针，以及包含磁共振造影剂或分子探针的试剂盒。
背景技术
与新兴磁共振成像(MRI)技术相比，磁共振造影剂的更新发展较慢，这是由于传统磁共振造影敏感性较低，大量使用造影剂产生毒性作用的风险比较大。常用的磁共振造影剂主要以顺磁性物质和超顺磁性物质为主，其中临床广泛应用的Gd-DTPA被认为易产生肾纤维化等副作用，渐渐显露其弊端，且Gd-DTPA并不具备靶向性，肿瘤特异性较差。超顺磁性氧化铁纳米颗粒(SPIONs)作为新兴的T2加权阴性造影剂被应用于肝癌等肿瘤的MRI造影中，但是SPIONs作为金属纳米粒子也存在难以降解等安全问题，这大大影响了其临床转化效率。分子影像的研究多集中于融合多种技术的优势，构建造影效率更高、安全性更好以及应用更广泛的分子探针。在肿瘤靶向造影领域以及前列腺癌诊疗方面，以前列腺特异性膜抗原(PSMA)为靶点的特异性小分子探针在前列腺癌的诊断、分期、预后及复发监测方面取得重大突破。通过构建基于黑色素纳米粒子的肿瘤靶向磁共振造影剂(MRI造影剂)，进行前列腺癌特异性MRI增强显像，可用于提高MRI造影的应用范围和诊断准确率。肿瘤靶向药物与纳米技术的结合将是今后发展新型诊疗药物的研究热点。
发明内容
本发明的目的是提供一种前列腺癌靶向磁共振造影剂及应用。该造影剂能够与前列腺癌细胞表面的PSMA膜抗原特异性结合，利用纳米探针的T1加权增强造影功能进行MRI成像，由于大量钆离子被限制在纳米粒子内，促进了质子由高能态恢复到低能态转化的速度，缩短了弛豫时间，明显提高了该造影剂的增强效率。本发明的造影剂可用于实现肿瘤的靶向磁共振增强造影目的。
本发明的第一方面提供一种前列腺癌靶向磁共振造影剂，在生物提取黑色素聚合成为纳米粒子过程中，融合Gd 3+、表面活性剂双氨基聚乙二醇，一步法获得表面带有氨基的顺磁性纳米粒PEG-GMNPs，具体地，所述前列腺癌靶向磁共振造影剂的制备方法包括：先将生物提取黑色素聚合成为MNPs，在此过程中添加钆盐、双氨基聚乙二醇，一步法获得表面带有氨基的顺磁性纳米粒PEG-GMNPs，然后使用交联剂Sulfo-SMCC(4-(N-马来酰亚胺甲基)环己烷-1-羧酸磺酸基琥珀酰亚胺酯钠盐)对PEG-GMNPs表面上的氨基进行修饰，得到SMCC-PEG-GMNPs，最后将SMCC-PEG-GMNPs与巯基化的PSMA靶向基团PSMA-SH偶联，制得前列腺癌靶向磁共振造影剂PSMA-GMNPs；
其中，MNPs为有机黑色素纳米粒子；纳米粒子的平均粒径大小为11-20nm；
所述钆盐为六水合氯化钆；
所述双氨基聚乙二醇为NH 2-PEG n-NH 2，PEG n的分子量为200-20000Da。
本发明中，PEG-GMNPs为顺磁性黑色素纳米粒子，纳米粒子的平均粒径大小为15nm，分子量约为40KDa。制备方法在文献(Lei Xia,Xiangxi Meng,Li Wen,et al.A Highly Specific Multiple Enhancement Theranostic Nanoprobe for PET/MRI/PAI Image-Guided Radioisotope Combined Photothermal Therapy in Prostate Cancer.Small.2021, 17(21):e2100378)的基础上，进行改进，一步法获得顺磁性纳米颗粒。
根据本发明一种具体实施方式，采用从植物细胞中提取的黑色素、钆盐及PEG作为原材料，一步法获得表面带有氨基的顺磁性纳米粒PEG-GMNPs，具体包括以下步骤：
(1)取10-50mg天然黑色素，剧烈搅拌下溶于10-20mL的0.15-0.25MNaOH溶液中；在超声细胞粉碎机作用下，于0.5-1.5分钟内加入12-12.5mL的0.15-0.25M HCl溶液，调体系pH至9.0-9.5；
(2)按MNPs与NH 2-PEG 5000-NH 2摩尔比1:20-30的比例继续将两者混合，同时加入过量钆盐，室温下搅拌反应12-24h；
(3)再次通过超声破碎法加入1-1.5mL的0.15-0.25M HCl溶液，调体系pH至7.0-7.5，得到黑亮的纳米粒子分散液；使用截留分子量为30kDa的超滤离心管去除溶液中游离的Na +、Cl -、Gd 3+及未反应的NH 2-PEG 5000-NH 2，并用去离子水清洗，得到纯净的表面带有氨基的顺磁性纳米粒子PEG-GMNPs，每个PEG-GMNPs表面结合20-30个PEG。
根据本发明一种优选实施方式，使用交联剂Sulfo-SMCC对PEG-GMNPs表面上的氨基进行修饰以及将SMCC-PEG-GMNPs与巯基化的PSMA靶向基团PSMA-SH偶联包括以下步骤：
1)按PEG-GMNPs表面上的氨基与Sulfo-SMCC摩尔比1:20-30的比例，将PEG-GMNPs与Sulfo-SMCC混合，室温下搅拌反应1-3h，反应结束后用PD-10柱纯化，得到SMCC-PEG-GMNPs；
2)按SMCC-PEG-GMNPs与PSMA-SH摩尔比1:20-30的比例，将SMCC-PEG-GMNPs与PSMA-SH混合，室温下搅拌反应12-24h，反应结束后用PD-10柱纯化，每个PEG-GMNPs表面结合15-20个PSMA。
根据实验证实，使用不同分子量PEG修饰纳米粒子会轻度影响探针的药代动力学结果，优选地，所述双氨基聚乙二醇为NH 2-PEG 5000-NH 2。
本发明的所述肿瘤靶向MRI造影剂可用于PSMA受体高表达前列腺癌靶 向MRI造影。
本发明的第二方面提供上述前列腺癌靶向磁共振造影剂在制备前列腺癌靶向分子探针中的应用。
本发明的第三方面提供一种前列腺癌靶向分子探针，有效成分为上述前列腺癌靶向磁共振造影剂。
本发明的第四发明提供一种试剂盒，所述试剂盒包含上述前列腺癌靶向磁共振造影剂，或上述前列腺癌靶向分子探针。
本发明提供的前列腺癌靶向MRI造影剂PSMA-GMNPs的MRI增强造影结果表明，PSMA-GMNPs能够准确定位PSMA受体阳性前列腺癌，静脉注射后在肿瘤部位产生明显富集，并滞留较长时间。PSMA-GMNPs能够明显增强PSMA受体阳性实体瘤的T1加权信号强度。
本发明以具有优良生物学性能的黑色素纳米粒子(MNPs)作为载体，一步法融合高顺磁性金属钆离子，并在纳米粒子表面修饰PEG，构建磁性纳米粒子PEG-GMNPs，将前列腺癌靶向基团PSMA小分子抑制剂与纳米粒子偶联，获得新型的前列腺癌靶向MRI造影剂PSMA-GMNPs，该造影剂具有较高的弛豫率，能够与前列腺癌表面特异性膜抗原PSMA特异性结合，通过MRI增强造影显像精准定位PSMA高表达肿瘤组织及转移灶，实现前列腺癌的靶向分子影像诊断目的，以达到肿瘤早发现、早诊断、早治疗的目标。
本发明的其它特征和优点将在随后具体实施方式部分予以详细说明。
附图说明
通过结合附图对本发明示例性实施方式进行更详细的描述，本发明的上述以及其它目的、特征和优势将变得更加明显。
图1为本发明前列腺癌靶向MRI造影剂的合成流程示意图。
图2为本发明测试例1中前列腺癌靶向MRI造影剂的药物代谢-动力学实验。
图3为本发明实施例1中PEG-GMNPs的高分辨率透射电镜扫描图。
图4为本发明测试例2中细胞摄取和竞争实验，左侧为本发明前列腺癌靶向MRI造影剂在阳性细胞LNCaP和阴性细胞PC-3中的摄取实验对比，右侧图为前列腺癌靶向MRI造影剂在阳性细胞LNCaP的竞争抑制实验。
图5为本发明测试例3中不同金属结合后前列腺癌靶向MRI造影剂体外MRI增强造影显像。
图6为本发明测试例3中不同金属结合后前列腺癌靶向MRI造影剂体外MRI增强弛豫率检测。
图7为本发明测试例4中前列腺癌靶向MRI造影剂PSMA-GMNPs在PSMA阳性模型LNCaP荷瘤鼠中的MRI增强造影示意图，白色圆圈勾勒肿瘤轮廓。
图8为本发明测试例4中前列腺癌靶向MRI造影剂PSMA-GMNPs在PSMA阳性模型LNCaP荷瘤鼠成像中，肿瘤部位MRI信号变化曲线图。
具体实施方式
下面将更详细地描述本发明的优选实施方式。虽然以下描述了本发明的优选实施方式，然而应该理解，可以以各种形式实现本发明而不应被这里阐述的实施方式所限制。
实施例1前列腺癌靶向MRI造影剂的制备方法
前列腺癌靶向MRI造影剂PSMA-GMNPs的制备包括以下步骤：
1、PEG-GMNPs的制备
采用从植物细胞中提取的黑色素、钆盐及PEG作为原材料，一步法制备顺磁性纳米粒子PEG-GMNPs；具体地，取10-50mg天然黑色素，剧烈搅拌下溶于15mL的0.2M NaOH溶液中；在超声细胞粉碎机作用下，于1分钟内加入12-12.5mL的0.2M HCl溶液，调体系pH至9.0-9.5；按MNPs与NH 2-PEG 5000-NH 2摩尔比1:20-30的比例继续将两者混合，同时加入过量钆 盐，室温下搅拌反应12-24h；再次通过超声破碎法加入1-1.5mL的0.2M HCl溶液，调体系pH至7.0-7.5，得到黑亮的纳米粒子分散液；使用截留分子量为30kDa的超滤离心管去除溶液中游离的Na +、Cl -、Gd 3+及未反应的NH 2-PEG 5000-NH 2，并用去离子水清洗三次，得到纯净的表面带有氨基的顺磁性纳米粒子PEG-GMNPs，每个PEG-GMNPs表面结合20-30个PEG，纳米粒子的平均粒径大小为15nm。PEG-GMNPs的高分辨率透射电镜扫描图如图3所示。
2、PSMA-GMNPs的制备
1)按PEG-GMNPs表面上的氨基与Sulfo-SMCC摩尔比1:20-30的比例，将PEG-GMNPs(5mg)与Sulfo-SMCC(0.48-0.72mg)混合，室温下搅拌反应2h，反应结束后用PD-10柱纯化，得到SMCC-PEG-GMNPs；
2)按SMCC-PEG-GMNPs与巯基修饰的PSMA靶向基团摩尔比1:20-30的比例，将SMCC-PEG-GMNPs(5.5mg)与巯基修饰的PSMA(1.8-2.7mg)混合，室温下搅拌反应12-24h，反应结束后用PD-10柱纯化，得到纯净的前列腺癌靶向MRI造影剂PSMA-GMNPs。
前列腺癌靶向MRI造影剂PSMA-GMNPs的合成流程示意图见图1。
实施例2前列腺癌靶向MRI造影剂的制备方法
制备方法同实施例1，仅将步骤1中所用分子量为5000Da双氨基聚乙二醇替换为分子量200-20000Da双氨基聚乙二醇，其余反应条件相同。
结果显示，使用不同分子量PEG修饰纳米粒子会轻度影响探针的药代动力学结果，但差异性并不明显。
对比例1对比前列腺癌靶向MRI造影剂的制备方法
制备方法同实施例1，仅将步骤1中钆盐GdCl 3·6H 2O换成铁盐FeCl 3·6H 2O或锰盐MnCl 2·4H 2O，金属盐的摩尔量较黑色素仍为过量，其余 反应条件相同。合成所得PSMA-Fe-MNPs、PSMA-Mn-MNPs。
测试例1前列腺癌靶向MRI造影剂药代动力学检测
取5只正常BALB/c小鼠(均为雄性，4周龄，16-18g)，将一定量PSMA-GMNPs经生理盐水稀释(30μM)，每只小鼠经尾静脉注射200μL造影剂，并严格记录注射时间。小鼠经尾静脉注射药物后，分别于1min、3min、5min、10min、15min、30min、60min、2h、8h、24h、48h使用毛细取血针经眼底静脉取血，并分别置于添加柠檬酸钠的试管中。称量试管中血液质量，使用ICP-MS检测样品Gd 3+含量，同时取每只小鼠注射药物量的1％作为测定参考标记品。结果使用单位组织的钆离子含量占注射总剂量的百分比(％ID/g)显示，使用分析软件经衰减校正后计算药物生物半衰期。结果显示(图2)：PSMA-GMNPs的药物代谢-时间曲线符合二室模型，其分布相和清除相的半衰期分别为0.13h和6.71h。
测试例2前列腺癌靶向磁共振造影剂细胞摄取及竞争抑制实验
细胞摄取实验：将生长至对数期的人源前列腺癌LNCaP细胞和PC-3细胞分别以2×10 5个/孔均匀铺到24孔板中，向每孔加入500μL不含胎牛血清的PRIM 1640培养基，培养箱孵育24h。将一定量PSMA-GMNPs使用PBS缓冲液稀释(30μM)，每孔均匀加入10μL PSMA-GMNPs溶液，放入培养箱孵育一段时间，分别于1h、2h、4h、24h将孔板取出，使用1M NaOH裂解细胞(n＝6)并收集，ICP-MS检测Gd 3+含量。实验结果如图4左图显示，探针在PSMA高表达细胞LNCaP中的摄取量高于PSMA低表达PC-3细胞。
细胞竞争抑制实验：使用LNCaP细胞，实验步骤与细胞摄取实验大致相同，仅在加入造影剂之前30min向部分孔内(n＝6)加入1μg/孔PSMA-SH溶液，然后每孔加入10μL PSMA-GMNPs(30μM)溶液，分别于2h、4h收集裂解后的细胞溶液，ICP-MS检测Gd 3+含量。实验结果如图4右图所示， 探针在LNCaP细胞的摄取可被PSMA-SH抑制，证明其对PSMA受体特异靶向性。
测试例3前列腺癌靶向MRI造影剂体外MRI增强造影检测
使用3.0T MR成像设备检测前列腺癌靶向MRI造影剂的磁共振增强功能及T1加权弛豫率，并对对比例1所述不同浓度PSMA-Fe-MNPs、PSMA-Mn-MNPs以及常用磁共振造影剂Gd-DTPA的体外T1加权磁共振造影以及弛豫效率进行对比。图5中不同浓度MRI造影剂T1加权体外成像结果显示，相同浓度下，PSMA-GMNPs的T1加权信号强度最高，其后依次是PSMA-Mn-MNPs、PSMA- 3+Fe-MNPs、PSMA- 2+Fe-MNPs、Gd-DTPA。T1加权弛豫效率折线图(图6)显示PSMA-GMNPs的T1加权弛豫率明显高于常用磁共振造影剂Gd-DTPA，大约是其5倍。
测试例4前列腺癌靶向MRI造影剂在荷瘤鼠体内的MRI增强造影
取瘤径0.8-1cm的LNCaP荷瘤鼠，每只鼠经尾静脉注射一定量PSMA-GMNPs(实施例1制备)生理盐水稀释液(30μM，200μL)，使用3.0T MR成像仪搭配小动物线圈，分别于药物注射前、药物注射后2h、24h、72h、168h进行MRI T1加权成像采集，MR序列信息为：TR(重复时间):531ms，TE(回波时间):9.1ms；翻转角(flip angle):30°；FOV(扫描视野):160×100mm 2；扫描矩阵(matrix):256×256；扫描层厚(slice thickness):3mm，成像结果见图7，该结果显示PSMA-GMNPs经尾静脉注射2h后，LNCaP荷瘤鼠全身MR信号均有所增强，其中，肝脏、胆囊MRI信号增高最为明显，肿瘤部位未见明显MRI增强信号。结合肿瘤、非肿瘤MRI信号比曲线图(图8)，肿瘤部位的T1加权MRI信号在24h时明显增强，72h时MRI增强造影可清晰定位肿瘤位置，内部强化信号明显。最后，给药7天后再次进行MRI增强扫描，肿瘤部位仍显 示清晰的MRI增强信号，证明探针的强滞留功能。实验证明PSMA-GMNPs探针可用于PSMA高表达前列腺癌特异性MRI增强造影。
以上已经描述了本发明的各实施例，上述说明是示例性的，并非穷尽性的，并且也不限于所披露的各实施例。在不偏离所说明的各实施例的范围和精神的情况下，对于本技术领域的普通技术人员来说许多修改和变更都是显而易见的。

Claims (7)

  1. 一种前列腺癌靶向磁共振造影剂，其特征在于，所述前列腺癌靶向磁共振造影剂的制备方法包括：先将生物提取黑色素聚合成为MNPs，在此过程中添加钆盐、双氨基聚乙二醇，一步法获得表面带有氨基的顺磁性纳米粒PEG-GMNPs，然后使用交联剂Sulfo-SMCC对PEG-GMNPs表面上的氨基进行修饰，得到SMCC-PEG-GMNPs，最后将SMCC-PEG-GMNPs与巯基化的PSMA靶向基团PSMA-SH偶联，制得前列腺癌靶向磁共振造影剂PSMA-GMNPs；
    其中，MNPs为有机黑色素纳米粒子；纳米粒子的平均粒径大小为11-20nm；
    所述钆盐为六水合氯化钆；
    所述双氨基聚乙二醇为NH 2-PEG n-NH 2，PEG n的分子量为200-20000Da。
  2. 根据权利要求1所述的前列腺癌靶向磁共振造影剂，其特征在于，一步法获得表面带有氨基的顺磁性纳米粒PEG-GMNPs包括以下步骤：
    (1)取10-50mg天然黑色素，剧烈搅拌下溶于10-20mL的0.15-0.25M NaOH溶液中；在超声细胞粉碎机作用下，于0.5-1.5分钟内加入12-12.5mL的0.15-0.25M HCl溶液，调体系pH至9.0-9.5；
    (2)按MNPs与NH 2-PEG 5000-NH 2摩尔比1:20-30的比例继续将两者混合，同时加入过量钆盐，室温下搅拌反应12-24h；
    (3)再次通过超声破碎法加入1-1.5mL的0.15-0.25M HCl溶液，调体系pH至7.0-7.5，得到黑亮的纳米粒子分散液；使用截留分子量为30kDa的超滤离心管去除溶液中游离的Na +、Cl -、Gd 3+及未反应的NH 2-PEG 5000-NH 2，并用去离子水清洗，得到纯净的表面带有氨基的顺磁性纳米粒子PEG-GMNPs，每个PEG-GMNPs表面结合20-30个PEG。
  3. 根据权利要求1所述的前列腺癌靶向磁共振造影剂，其特征在于，使用交联剂Sulfo-SMCC对PEG-GMNPs表面上的氨基进行修饰以及将SMCC-PEG-GMNPs与巯基化的PSMA靶向基团PSMA-SH偶联包括以下步骤：
    1)按PEG-GMNPs表面上的氨基与Sulfo-SMCC摩尔比1:20-30的比例，将PEG-GMNPs与Sulfo-SMCC混合，室温下搅拌反应1-3h，反应结束后用PD-10柱纯化，得到SMCC-PEG-GMNPs；
    2)按SMCC-PEG-GMNPs与PSMA-SH摩尔比1:20-30的比例，将SMCC-PEG-GMNPs与PSMA-SH混合，室温下搅拌反应12-24h，反应结束后用PD-10柱纯化，每个PEG-GMNPs表面结合15-20个PSMA。
  4. 根据权利要求1-3中任意一项所述的前列腺癌靶向磁共振造影剂，其特征在于，所述双氨基聚乙二醇为NH 2-PEG 5000-NH 2。
  5. 权利要求1-4中任意一项所述的前列腺癌靶向磁共振造影剂在制备前列腺癌靶向分子探针中的应用。
  6. 一种前列腺癌靶向分子探针，其特征在于，有效成分为权利要求1-4中任意一项所述的前列腺癌靶向磁共振造影剂。
  7. 一种试剂盒，其特征在于，所述试剂盒包含权利要求1-4中任意一项所述的前列腺癌靶向磁共振造影剂，或权利要求6所述的前列腺癌靶向分子探针。
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