WO2024011452A1 - 一种薄膜的制备方法及其应用 - Google Patents

一种薄膜的制备方法及其应用 Download PDF

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WO2024011452A1
WO2024011452A1 PCT/CN2022/105478 CN2022105478W WO2024011452A1 WO 2024011452 A1 WO2024011452 A1 WO 2024011452A1 CN 2022105478 W CN2022105478 W CN 2022105478W WO 2024011452 A1 WO2024011452 A1 WO 2024011452A1
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film
preparing
mixture
polyvinyl alcohol
thin film
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PCT/CN2022/105478
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English (en)
French (fr)
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郑海荣
盛宗海
胡德红
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深圳先进技术研究院
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Priority to PCT/CN2022/105478 priority Critical patent/WO2024011452A1/zh
Publication of WO2024011452A1 publication Critical patent/WO2024011452A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy

Definitions

  • the invention belongs to the field of medical materials and specifically designs a preparation method and application of the film.
  • Radiotherapy is a local treatment method that uses radiation, such as alpha rays, beta rays, X-rays, gamma rays, proton rays, heavy ion rays, etc., to treat tumors.
  • Radiation therapy is divided into two categories according to the method of delivery, namely teletherapy and brachytherapy.
  • teletherapy also known as external radiation
  • brachytherapy irradiates tumors through the skin of the body.
  • Brachytherapy also known as internal irradiation, can implant the radioactive source directly into the tumor or at the edge of the target area, so that the radiation dose can accurately cover the lesion area while minimizing the radiation exposure of surrounding important tissues and organs.
  • Brachytherapy wraps radionuclides with a layer of metal and makes them into needles, tubes or particles, and places them in tissues, organs or cavities for brachytherapy.
  • intracavity irradiation can illuminate tumors through the body cavity, such as vaginal irradiation.
  • Cervical cancer intraductal irradiation irradiates the cancer through the esophagus, trachea, and bile duct
  • intertissue irradiation implants the radioactive source into the tumor tissue for irradiation, such as tongue cancer and intraoperative implantation irradiation.
  • the operations in brachytherapy are not precise.
  • the location, dose, and type of radiation source are roughly estimated, selected, and fixed based on the doctor’s experience, rather than the range, orientation, and location of the specific lesion. Determined by size, tumor cell activity, type, etc. Therefore, the risk of radiotherapy dose errors faced by patients during radiotherapy is also increasing, and dose verification is becoming more and more important as an important component of radiotherapy quality assurance.
  • the current dose verification method is to perform a CT scan on a static phantom under the same conditions as the patient's positioning, then import the patient's treatment plan into the phantom's CT image sequence for calculation to obtain the theoretical dose distribution, and then use the phantom to replace the patient to carry out the radiotherapy plan.
  • the measured dose distribution (GAFCH R OMIC EBT3+ film) is compared with the dose distribution calculated by the planning system.
  • the EBT film measures the optical density value (OD), which has the disadvantage of a narrow linear range, resulting in inaccurate comparison results.
  • the current common model for radiotherapy verification is based on the target position and shape being known and remaining stationary. Such a rigid relationship is not valid in some cases. For example, the chest will be affected by movements such as breathing and heartbeat. , During the radiotherapy process, the target area moves together with the moving organs, resulting in a large difference between the dose distribution in the treatment plan and the dose distribution actually received by the target.
  • this application provides a method for preparing a thin film and its application.
  • An object of the present invention is to provide a method for preparing a film.
  • the film prepared by this method can solve the dose distribution in the treatment plan and the dose distribution actually received by the target due to the verification materials and verification modes used in the prior art. The problem of large differences exists.
  • the preparation method of the film includes the steps of preparing the functional layer:
  • the vacuum-treated mixture is solidified to obtain the functional layer.
  • the mass ratio of the dispersant, the curing agent and the radioactive afterglow luminescent material is 1000:10:1.
  • the dispersant is a hydrophobic polymer material
  • the curing agent is Dow Corning 184.
  • the vacuuming conditions are 10-4000Pa
  • the curing conditions are the drying oven parameter setting temperature is 20-100°C
  • the curing time is 10-300 minutes.
  • the preparation method of the film also includes the step of preparing an adhesive layer:
  • Polyvinyl alcohol gel is coated on the functional layer at a coating amount of 1.2g/ m2-2g / m2 to obtain the adhesive layer.
  • the preparation method of the polyvinyl alcohol gel is as follows:
  • the preparation method of the film also includes a composite step of the base layer:
  • the semi-finished film is subjected to aging treatment at a temperature of 50°C to 55°C for 5h to 8h to obtain the film.
  • the polyethylene resin is produced by a casting process.
  • One object of the present invention is to provide the application of the film prepared by the film preparation method as described in any one of the above in clinical radiotherapy dose quantitative imaging.
  • the functional layer prepared by the film preparation method provided by the present invention contains radioactive afterglow luminescent materials, which can replace EBT film to obtain the two-dimensional dose distribution of the radiotherapy plan, obtain a wider linear range, and increase the dose in the treatment plan.
  • the accuracy of the comparison between the distribution and the dose distribution actually received by the target; at the same time, the film can be worn on the human body to eliminate the possibility that the target area moves with the moving organs during radiotherapy, causing the dose distribution in the treatment plan and the dose actually received by the target. There is a large difference in distribution, further improving the accuracy of comparing the dose distribution in the treatment plan with the dose distribution actually received by the target.
  • Figure 1 is a flow chart of a film preparation method provided by the present invention.
  • Figure 2 shows the linear range and sensitivity value of EBT provided by the present invention
  • Figure 3 shows the linear range and sensitivity value of the film provided by the present invention.
  • the present invention provides a method for preparing a film , the film prepared by the film preparation method can improve the accuracy of the comparison between the dose distribution in the treatment plan and the dose distribution actually received by the target.
  • the preparation method of the film includes the steps of preparing the functional layer:
  • the radioactive afterglow luminescent material is excited by radiation, causing the radioactive afterglow luminescent material to emit afterglow, which can be identified by the naked eye or an instrument.
  • the dispersant makes the radioactive afterglow luminescent material evenly dispersed in the functional layer, and the curing agent is used to solidify the dispersant and the radioactive afterglow luminescent material into a film, which can cover the lesion area.
  • the mass ratio of the dispersant, curing agent and radioactive afterglow-emitting material is 200-2000:6-240:1, the radioactive afterglow-emitting material is evenly distributed in the functional layer, so that each part of the functional layer is After being irradiated by radiation, it can be excited to emit afterglow.
  • the intensity of the afterglow at each part is proportional to the intensity of the irradiation.
  • the functional layer can be solidified into a film, and at the same time, the radioactive afterglow luminescent material occupies a larger mass fraction in the functional layer. Proportion, so that the afterglow emitted by the functional layer is of sufficient intensity to be recognized by the naked eye or machine.
  • the above operation removes the moisture in the mixture, which facilitates the curing operation.
  • the vacuum treatment can remove bubbles in the mixture and avoid the presence of bubbles in the prepared film that causes uneven radioactive afterglow luminescence materials to affect film imaging.
  • the vacuum-treated mixture is solidified to obtain a functional layer.
  • the mixture is cured to form a film to obtain a functional layer, which can be used alone for clinical radiotherapy dose quantitative imaging, attached to the lesion area, or combined with other film layers to form a multifunctional film.
  • This film can replace EBT film to obtain the two-dimensional dose distribution of the radiotherapy plan, obtain a wider linear range, and improve the accuracy of the comparison between the dose distribution in the treatment plan and the dose distribution actually received by the target; at the same time, the film can be worn on the human body
  • the target area moves along with the moving organs during radiotherapy, resulting in a large difference between the dose distribution in the treatment plan and the dose distribution actually received by the target, which further improves the dose distribution in the treatment plan and the dose actually received by the target. Accuracy of distribution comparison.
  • the mass ratio of the dispersant, curing agent and radioactive afterglow luminescent material is 1000:10:1.
  • the dispersant is a hydrophobic polymer material
  • the curing agent is Dow Corning 184.
  • a small amount of Dow Corning 184 can be used to achieve curing without diluting the concentration of the radioactive long-lasting afterglow luminescent material.
  • Dow Corning 184 can be used as vinyltriamine DETA, aminoethylpiperazine AE, diaminocyclohexane DACH, isophorone diamine IPDA, methylene bicyclohexaneamine 4,4'-PACM, ethanol Diamine EDA, diethylenetriamine DETA and dihexyltriamine are substituted.
  • the hydrophobic high molecular polymer is selected from polydimethylsiloxane, cyclomethicone, aminosiloxane, polymethylphenylsiloxane, polyetherpolysiloxane copolymer, One or more of polyolefin, polycarbonate, polyamide, polyacrylonitrile and polyester.
  • polydimethylsiloxane is selected from polydimethylsiloxane, cyclomethicone, aminosiloxane, polymethylphenylsiloxane, polyetherpolysiloxane copolymer, One or more of polyolefin, polycarbonate, polyamide, polyacrylonitrile and polyester.
  • polydimethylsiloxane Preferably, polydimethylsiloxane.
  • the vacuuming condition is 10-4000 Pa
  • the curing condition is the drying oven parameter setting temperature is 20-100°C
  • the curing time is 10-300 minutes.
  • the preparation method of the film further includes the step of preparing an adhesive layer:
  • Polyvinyl alcohol gel is coated on the functional layer at a coating amount of 1.2g/ m2-2g / m2 to obtain an adhesive layer.
  • polyvinyl alcohol gel preparation method of polyvinyl alcohol gel is as follows:
  • the preparation method of the film also includes the step of compounding the base layer:
  • the film semi-finished product is aged at a temperature of 50°C-55°C for 5h-8h to obtain a film.
  • the polyethylene resin is produced through a casting process.
  • the preparation steps of the present invention are simple and the preparation process is precise and controllable.
  • the surface of the prepared film is highly durable and has good toughness. It can be used to fit various parts of the body, and can be reused through multiple cycles of fitting and peeling. With a wide range of applicable substrates, the film can be used to study the spatial distribution of doses under respiratory motion, making it possible to analyze points of interest and space to guide radiotherapy doctors in target area delineation.
  • One object of the present invention is to provide the application of the film prepared by the film preparation method as described in any one of the above in clinical radiotherapy dose quantitative imaging.
  • the film provided by the present invention has a wider linear range and a higher sensitivity value than EBT film.
  • step 2 Coat the polyvinyl alcohol hydrogel on the base film prepared in step 1 at a coating amount of 1.5g/ m2 to obtain an adhesive layer, and then put the base film under a pressure of 2MPa and a temperature of 60°C. It is compounded with the adhesive layer under certain conditions to obtain a semi-finished composite film;
  • step 3 Aging the composite film semi-finished product in step 2 at a temperature of 50°C for 5 hours to obtain the wearable film.
  • the PE resin is made into a base film through a casting process
  • step 4 Coat the polyvinyl alcohol hydrogel obtained in step 1 on the base film obtained in step 2 at a coating amount of 1.5g/m2 to obtain an adhesive layer, and then apply the outer layer film obtained in step 3 It is compounded with the adhesive layer under the conditions of a pressure of 2MPa and a temperature of 60°C to obtain a composite film semi-finished product;
  • step 4 Aging the composite film semi-finished product in step 4 at a temperature of 50°C for 5 hours to obtain the wearable film.
  • the PE resin is made into a base film through a casting process
  • step 4 Coat the polyvinyl alcohol hydrogel obtained in step 1 on the base film obtained in step 2 at a coating amount of 1.5g/m2 to obtain an adhesive layer, and then apply the outer layer film obtained in step 3 It is compounded with the adhesive layer under the conditions of a pressure of 2MPa and a temperature of 60°C to obtain a composite film semi-finished product;
  • step 4 Aging the composite film semi-finished product in step 4 at a temperature of 50°C for 5 hours to obtain the wearable film.
  • the PE resin is made into a base film through a casting process
  • step 4 Coat the polyvinyl alcohol hydrogel obtained in step 1 on the base film obtained in step 2 at a coating amount of 1.5g/m2 to obtain an adhesive layer, and then apply the outer layer film obtained in step 3 It is compounded with the adhesive layer under the conditions of a pressure of 2MPa and a temperature of 60°C to obtain a composite film semi-finished product;
  • step 4 Aging the composite film semi-finished product in step 4 at a temperature of 50°C for 5 hours to obtain the wearable film.

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Abstract

本发明涉及医用材料领域，提供一种薄膜的制备方法及其应用。该薄膜的制备方法包括功能层的制备步骤：将质量比为200-2000:6-240:1的分散剂、固化剂和放射性致长余辉发光材料混合均匀，得到混合物；将所述混合物倒入平底容器中，在真空干燥箱箱内进行抽真空处理；对抽真空处理后的所述混合物进行固化，得到所述功能层。本发明所提供的薄膜的制备方法制备的功能层中包含放射性致长余辉发光材料，可以代替EBT胶片获得放射治疗计划的二维剂量分布，获得较宽的线性范围；同时，该薄膜可以穿戴在人体上，提高了治疗计划中的剂量分布和目标实际接受的剂量分布的准确性。

Description

一种薄膜的制备方法及其应用 技术领域
本发明属于医用材料领域，具体设计一种薄膜的制备方法和应用。
背景技术
放射治疗是利用放射线，如α射线、β射线、X射线、γ射线、质子线、重离子线等治疗肿瘤的一种局部治疗方法。放射治疗按照射方法分为两类，即远距离治疗和近距离治疗。其中，远距离治疗又称外照射，通过身体皮肤照射肿瘤。近距离治疗又称体内照射，可将放射源直接植入在肿瘤内或靶区边缘，从而可以使辐射剂量精准覆盖病灶区域，同时最大限度的避免周边重要组织器官受到辐射。近距离放疗将放射性核素外面包裹上一层金属，制成针状、管状或粒子状，置于组织、器官或腔道内进行近距离放疗，如腔内照射通过体腔照肿瘤，如通过阴道照射子宫颈癌；管内照射通过食管、气管、胆管照射该处癌症；组织间照射将放射源陷植到肿瘤组织进行照射，如舌癌以及术中插植照射。现有技术中，近距离放疗中的操作并不精确，如放射粒子的位置、剂量和放射源种类是根据医生的经验粗略地估计、选择并固定的，而不是由具体病灶的范围、方位、大小、肿瘤细胞活性、类型等决定的。因此，放疗过程中患者面临的放疗剂量出错风险也在加大，剂量验证作为放疗质量保证的重要组成部分变得越来越重要。
目前剂量验证方法是将静态体模按照与患者定位时相同条件进行CT扫描，再将患者的治疗计划导入到模体CT图像序列进行计算，得到理论剂量分布，然后以模体代替患者将放疗计划在加速器上执行，将实测的剂量分布(GAFCH R OMIC EBT3+胶片)与计划系统计算的剂量分布进行比较。然而，在上述剂量验证方法中EBT胶片测得的是光密度值(OD)，存在线性范围窄的缺点，导致对比结果不准确。而且，当前放疗验证普遍的模式是建立在目标位置和形状是己知而且是保持静止的基础上，这样的刚性关系在某些情况下是不成立的，例如胸腔会受到呼吸和心跳等运动的影响，在放射治疗过程中目标区域随着运动器官一起运动造成了治疗计划中的剂量分布和目标实际接受的剂量分布存在较大差异。
为了解决由于所采用的验证材料和验证模式造成的治疗计划中的剂量分布和目标实际接受的剂量分布存在的较大差异的问题，保证治疗计划中的剂量分布和目标实际接受的剂量分布对比的准确性，本申请提供了一种薄膜的制备方法及其应用。
发明内容
本发明的一个目的是提供一种薄膜的制备方法，通过该方法制备的薄膜可以解决现有技术中由于所采用的验证材料和验证模式造成的治疗计划中的剂量分布和目标实际接受的剂量分布存在的较大差异的问题。
该薄膜的制备方法包括功能层的制备步骤：
将质量比为200-2000:6-240:1的分散剂、固化剂和放射性致长余辉发光材料混合均匀，得到混合物；
将所述混合物倒入平底容器中，在真空干燥箱箱内进行抽真空处理；
对抽真空处理后的所述混合物进行固化，得到所述功能层。
可选地，所述分散剂、所述固化剂和放射性致长余辉发光材料的质量比为1000：10：1。
可选地，所述分散剂为疏水性高分子聚合物材料，所述固化剂为道康宁184。
可选地，抽真空的条件为10-4000Pa，固化条件为干燥箱参数设定温度为20-100℃，固化时间为10-300分钟。
可选地，该薄膜的制备方法还包括粘结层的制备步骤：
将聚乙烯醇凝胶以1.2g/m 2-2g/m 2的涂布量涂布在所述功能层上，得到所述粘结层。
可选地，所述聚乙烯醇凝胶的制备方法如下：
将聚乙烯醇加入去离子水中，使得聚乙烯醇的浓度达到7％，煮沸溶解后于-20℃下冷冻12小时，室温解冻4小时，重复冷冻和解冻操作5次，得到所述聚乙烯醇水凝胶。
可选地，该薄膜的制备方法还包括基层的复合步骤：
将聚乙烯树脂在压力为1.8MPa-4.5MPa、温度为50℃-65℃的条件下与所述粘结层复合，得到薄膜半成品；
将所述薄膜半成品在50℃-55℃的温度下进行熟化处理5h-8h，得到所述薄膜。
可选地，所述聚乙烯树脂通过流延工艺制得。
本发明的一个目的是提供如上任一项所述的薄膜的制备方法制备的薄膜在临床放疗剂量定量成像中的应用。
本发明所提供的薄膜的制备方法制备的功能层中包含放射性致长余辉发光材料，可以代替EBT胶片进行获得放射治疗计划的二维剂量分布，获得较宽的线性范围，提高治疗计划中的剂量分布和目标实际接受的剂量分布对比的准确性；同时，该薄膜可以穿戴在人体上，排除放射治疗过程中目标区随着运动器官一起运动造成了治疗计划中的剂量分布和目标实际接受的剂量分布存在较大差异，进一步提高了治疗计划中的剂量分布和目标实际接受的剂量分 布对比的准确性。
附图说明
图1为本发明提供的一个薄膜的制备方法的流程图；
图2为本发明提供的EBT的线性范围和灵敏度值；
图3为本发明提供的薄膜的线性范围和灵敏度值。
具体实施方式
为了使本发明的上述目的、特征和优点能够更加明显易懂，下面结合附图对本发明的具体实施方式做详细的说明，但不能理解为对本发明的可实施范围的限定。
鉴于现有技术中，EBT胶片的线性范围窄和目标区域随运动器官一起运动导致的计划中的剂量分布和目标实际接受的剂量分布存在较大差异的问题，本发明提供一种薄膜的制备方法，通过该薄膜的制备方法制备的薄膜可以提高了治疗计划中的剂量分布和目标实际接受的剂量分布对比的准确性。
该薄膜的制备方法包括功能层的制备步骤：
将质量比为200-2000:6-240:1的分散剂、固化剂和放射性致长余辉发光材料混合均匀，得到混合物。
放射性致长余辉发光材料在放射线中被激发，使放射性致长余辉发光材料发出余辉，该余辉可以被肉眼或仪器识别。分散剂使放射性致长余辉发光材料均匀地分散在功能层中，固化剂用于使分散剂和放射性致长余辉发光材料固化成膜，可以覆盖在病灶区域。在分散剂、固化剂和放射性致长余辉发光材料的质量比为200-2000:6-240:1的情况下，放射性致长余辉发光材料在功能层的分布均匀，使功能层的各部位在放射线的照射后都可以受到激发发出余晖，各部位余晖的光强和受到照射的强度成正比，功能层能够固化成膜，同时使得放射性致长余辉发光材料在功能层中质量分数占有较大的比例，使功能层发出的足够强度的余晖被肉眼或机器识别。
将混合物倒入平底容器中，在真空干燥箱箱内进行抽真空处理。
上述操作去除混合物中的水分利于进行固化操作，同时真空处理能够去除混合物中的气泡，避免制备的薄膜中存在气泡使得放射性致长余辉发光材料不均匀对薄膜成像的影响。
将抽真空处理后的混合物进行固化，得到功能层。
混合物固化成膜得到功能层，该功能层可单独用于临床放疗剂量定量成像，附着在病灶 区域，也可和其他膜层复合，形成具备多功能的薄膜。
该薄膜可以代替EBT胶片进行获得放射治疗计划的二维剂量分布，获得较宽的线性范围，提高治疗计划中的剂量分布和目标实际接受的剂量分布对比的准确性；同时，该可以穿戴在人体上，排除放射治疗过程中目标区随着运动器官一起运动造成了治疗计划中的剂量分布和目标实际接受的剂量分布存在较大差异，进一步提高了治疗计划中的剂量分布和目标实际接受的剂量分布对比的准确性。
在一个实施例中，分散剂、固化剂和放射性致长余辉发光材料的质量比为1000:10:1。
进一步地，分散剂为疏水性高分子聚合物材料，固化剂为道康宁184。
少量的道康宁184即可实现固化，避免放射性致长余辉发光材料的浓度被稀释。
可选地，道康宁184可用乙烯基三胺DETA、氨乙基哌嗪AE、二氨基环己烷DACH、异佛尔酮二胺IPDA、亚甲基双环己烷胺4,4'-PACM、乙二胺EDA、二乙烯三胺DETA和二已基三胺代替。
可选地，疏水性高分子聚合物选自聚二甲基硅氧烷、环甲基硅氧烷、氨基硅氧烷、聚甲基苯基硅氧烷、聚醚聚硅氧烷共聚物、聚烯烃、聚碳酸酯、聚酰胺、聚丙烯腈和聚酯中的一种或多种。优选，聚二甲基硅氧烷。
在一个实施例中，抽真空的条件为10-4000Pa，固化条件为干燥箱参数设定温度为20-100℃；固化时间为10-300分钟。
在一个实施例中，该薄膜的制备方法还包括粘结层的制备步骤：
将聚乙烯醇凝胶以1.2g/m 2-2g/m 2的涂布量涂布在所述功能层上，得到粘结层。
进一步地，聚乙烯醇凝胶的制备方法如下：
将聚乙烯醇加入去离子水中，使得聚乙烯醇的浓度达到7％，煮沸溶解后于-20℃下冷冻12小时，室温解冻4小时，重复冷冻和解冻操作5次，得到所述聚乙烯醇水凝胶。
在一个实施例中，该薄膜的制备方法还包括基层的复合步骤：
将聚乙烯树脂在压力为1.8MPa-4.5MPa、温度为50℃-65℃的条件下与粘结层复合，得到薄膜半成品；
将薄膜半成品在50℃-55℃的温度下进行熟化处理5h-8h，得到薄膜。
进一步地，聚乙烯树脂通过流延工艺制得。
本发明的制备步骤简洁，制备过程精确可控，所制备薄膜表面耐用性强，具备良好的韧性，可贴合身体各部位来使用，并能进行多次贴合、剥离的循环重复使用，可适用基体范围广，该薄膜可以应用于研究在呼吸运动状态下的剂量空间分布，让感兴趣点和空间分析变成 可能，以指导放疗医生靶区勾画。
本发明的一个目的是提供如上任一项所述的薄膜的制备方法制备的薄膜在临床放疗剂量定量成像中的应用。
参阅说明书图2和图3，本发明所提供的薄膜具有较EBT胶片更宽的线性范围和更高的灵敏值。该薄膜穿戴在人体上，可以提高治疗计划中的剂量分布和目标实际接受的剂量分布的准确性。
实施例1
取质量比为1000：10：1的疏水性高分子聚合物材料、固化剂、放射性致长余辉发光材料，然后由搅拌机搅拌混合均匀，得到混合物；将混合均匀后的混合物倒入平底容器中，然后放置在真空干燥箱中进行抽真空处理，去除混合物中的气泡；将真空处理后的混合物进行固化，获得表面平整的外层薄膜。
实施例2
1、取质量比为1000：10:1的疏水性高分子聚合物材料、固化剂、放射性致长余辉发光材料，然后由搅拌机搅拌混合均匀，得到混合物；将混合均匀后的混合物倒入平底容器中，然后放置在真空干燥箱中进行抽真空处理，去除混合物中的气泡；将真空处理后的混合物进行固化，获得表面平整的外层薄膜；
2、将聚乙烯醇水凝胶以1.5g/m 2的涂布量涂布在步骤1制得的基层薄膜上，得到粘结层，然后将基层薄膜在压力为2MPa、温度为60℃的条件下与粘结层复合而成，得到复合薄膜半成品；
3、将步骤2的复合薄膜半成品在50℃的温度下进行熟化处理5h，即得所述可穿戴薄膜。
实施例3
1、将聚乙烯醇(PVA-1779)加入去离子水中，使得PVA的浓度达到7％，煮沸溶解后于-20℃下冷冻12小时，室温解冻4小时，重复冷冻和解冻操作5次，得到聚乙烯醇水凝胶；
2、将PE树脂经流延工艺制得基层薄膜；
3、取质量比为1000：10:1的疏水性高分子聚合物材料、固化剂、放射性致长余辉发光材料，然后由搅拌机搅拌混合均匀，得到混合物；将混合均匀后的混合物倒入平底容器中，然后放置在真空干燥箱中进行抽真空处理，去除混合物中的气泡；将真空处理后的混合物进行固化，获得表面平整的外层薄膜；
4、将步骤1得到的聚乙烯醇水凝胶以1.5g/m 2的涂布量涂布在步骤2制得的基层薄膜上，得到粘结层，然后将步骤3制得的外层薄膜在压力为2MPa、温度为60℃的条件下与粘结层复 合而成，得到复合薄膜半成品；
5、将步骤4的复合薄膜半成品在50℃的温度下进行熟化处理5h，即得所述可穿戴薄膜。
实施例4
1、将聚乙烯醇(PVA-1779)加入去离子水中，使得PVA的浓度达到7％，煮沸溶解后于-20℃下冷冻12小时，室温解冻4小时，重复冷冻和解冻操作5次，得到聚乙烯醇水凝胶；
2、将PE树脂经流延工艺制得基层薄膜；
3、取质量比为1000：10:1的疏水性高分子聚合物材料、固化剂、放射性致长余辉发光材料，然后由搅拌机搅拌混合均匀，得到混合物；将混合均匀后的混合物倒入平底容器中，然后放置在真空干燥箱中进行抽真空处理，去除混合物中的气泡；将真空处理后的混合物进行固化，获得表面平整的外层薄膜；
4、将步骤1得到的聚乙烯醇水凝胶以1.5g/m 2的涂布量涂布在步骤2制得的基层薄膜上，得到粘结层，然后将步骤3制得的外层薄膜在压力为2MPa、温度为60℃的条件下与粘结层复合而成，得到复合薄膜半成品；
5、将步骤4的复合薄膜半成品在50℃的温度下进行熟化处理5h，即得所述可穿戴薄膜。
实施例5
1、将聚乙烯醇(PVA-1779)加入去离子水中，使得PVA的浓度达到7％，煮沸溶解后于-20℃下冷冻12小时，室温解冻4小时，重复冷冻和解冻操作5次，得到聚乙烯醇水凝胶；
2、将PE树脂经流延工艺制得基层薄膜；
3、取质量比为1000：10：1的疏水性高分子聚合物材料、固化剂、放射性致长余辉发光材料，然后放置在真空干燥箱中进行抽真空处理，去除混合物中的气泡；将真空处理后的混合物进行固化，获得表面平整的外层薄膜；
4、将步骤1得到的聚乙烯醇水凝胶以1.5g/m 2的涂布量涂布在步骤2制得的基层薄膜上，得到粘结层，然后将步骤3制得的外层薄膜在压力为2MPa、温度为60℃的条件下与粘结层复合而成，得到复合薄膜半成品；
5、将步骤4的复合薄膜半成品在50℃的温度下进行熟化处理5h，即得所述可穿戴薄膜。

Claims (9)

  1. 一种薄膜的制备方法，其特征在于，包括功能层的制备步骤：
    将质量比为200-2000:6-240:1的分散剂、固化剂和放射性致长余辉发光材料混合均匀，得到混合物；
    将所述混合物倒入平底容器中，在真空干燥箱箱内进行抽真空处理；
    对抽真空处理后的所述混合物进行固化，得到所述功能层。
  2. 如权利要求1所述的薄膜的制备方法，其特征在于，所述分散剂、所述固化剂和放射性致长余辉发光材料的质量比为1000：10：1。
  3. 如权利要求1所述的薄膜的制备方法，其特征在于，所述分散剂为疏水性高分子聚合物材料，所述固化剂为道康宁184。
  4. 如权利要求1所述的薄膜的制备方法，其特征在于，抽真空的条件为10-4000Pa，固化条件为干燥箱参数设定温度为20-100℃，固化时间为10-300分钟。
  5. 如权利要求1所述的薄膜的制备方法，其特征在于，还包括粘结层的制备步骤：
    将聚乙烯醇凝胶以1.2g/m 2-2g/m 2的涂布量涂布在所述功能层上，得到所述粘结层。
  6. 如权利要求5所述的薄膜的制备方法，其特征在于，所述聚乙烯醇凝胶的制备方法如下：
    将聚乙烯醇加入去离子水中，使得聚乙烯醇的浓度达到7％，煮沸溶解后于-20℃下冷冻12小时，室温解冻4小时，重复冷冻和解冻操作5次，得到所述聚乙烯醇水凝胶。
  7. 如权利要求5所述的薄膜的制备方法，其特征在于，还包括基层的复合步骤：
    将聚乙烯树脂在压力为1.8MPa-4.5MPa、温度为50℃-65℃的条件下与所述粘结层复合，得到薄膜半成品；
    将所述薄膜半成品在50℃-55℃的温度下进行熟化处理5h-8h，得到所述薄膜。
  8. 如权利要求7所述的薄膜的制备方法，其特征在于，所述聚乙烯树脂通过流延工艺制得。
  9. 如权利要求1-8所述的薄膜的制备方法制备的薄膜在临床放疗剂量定量成像中的应用。
PCT/CN2022/105478 2022-07-13 2022-07-13 一种薄膜的制备方法及其应用 WO2024011452A1 (zh)

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JP2015175806A (ja) * 2014-03-18 2015-10-05 国立研究開発法人日本原子力研究開発機構 半透明ＺｎＳ／１０Ｂコンバータ中性子シンチレータ及びその製造方法
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US6391279B1 (en) * 1997-11-14 2002-05-21 Bristol-Myers Squibb Pharma Company Radioactive seeds for brachytherapy and a process for making the same
US6086942A (en) * 1998-05-27 2000-07-11 International Brachytherapy S.A. Fluid-jet deposition of radioactive material for brachytherapy devices
CN103736200A (zh) * 2013-12-31 2014-04-23 原子高科股份有限公司 一种放射性粒子链的制备方法
JP2015175806A (ja) * 2014-03-18 2015-10-05 国立研究開発法人日本原子力研究開発機構 半透明ＺｎＳ／１０Ｂコンバータ中性子シンチレータ及びその製造方法
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