JP2015044979A - Medical propylene-ethylene-based resin composition and injection molded article thereof - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an excellent medical propylene-ethylene-based resin composition and an injection molded article thereof good in moldability during injection molding, excellent in a balance of rigidity and shock resistance, low temperature shock resistance, low debris occurrence and transparency, especially excellent in shock resistance and low leachability after radiation sterilization, and satisfying 6 chemical requirements described in JIS T3210:2011 sterilized injection syringe, or a heavy metal test, a lead test, a cadmium test and an eluate test described in Notification No.494 of the Pharmaceutical Affairs Bureau, a quality and test method of a blood circuit in dialysis type artificial kidney apparatus approval standard IV, after the radiation sterilization.SOLUTION: There is provided a medical propylene-ethylene-based resin composition consisting of a propylene-ethylene copolymer (A) having the ethylene content of 0.1 to 3 wt.%, a melt flow rate (MFR) according to JIS K 7210 (230°C, 2.16 kg load) of 10 to 300 g/10 min and a propylene-ethylene copolymer (B) having the ethylene content of 5 to 20 wt.% and MFR of 1 to 50 g/10 min. The weight ratio of the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B) is 90:10 to 60:40, and the ethylene content in the medical propylene-ethylene-based resin composition is 2 to 8 wt.%.

Description

  The present invention relates to a medical propylene-ethylene-based resin composition and an injection-molded product obtained by using the same, and more specifically, has good moldability during injection molding, a balance between rigidity and impact resistance, and low temperature. 6 chemical requirements described in the JIS T3210: 2011 sterilized syringe, excellent in impact resistance, appearance of low foreign matter, and transparency, in particular, excellent in impact resistance after radiation sterilization, low elution, or Yakuhin No.494 Dialysis-type Artificial Kidney Approval Criteria IV Propylene-ethylene resin composition for medical use satisfying heavy metal test, lead test, cadmium test, and eluate test described in quality and test method of blood circuit after radiation sterilization And an injection-molded article obtained by using the same.

Propylene polymers are excellent in molding processability, mechanical properties, and gas barrier properties, so they are molded by various methods, and like other resins such as polyvinyl chloride and polystyrene, food containers, caps, medical Widely used in various applications such as industrial equipment, medical containers, daily necessities, automobile parts, electrical parts, sheets, films, fibers and the like. Depending on the application, a higher balance of rigidity and impact resistance, transparency, and appearance of low foreign matter are strongly required for the propylene-based polymer or the composition thereof. For example, if the rigidity of the syringe barrel is reduced to improve impact resistance, the product strength of the outer cylinder will be insufficient, the outer cylinder will be crushed during use, and the drug will leak unintentionally from the tip of the syringe needle On the contrary, if the rigidity is increased, the product strength is improved, but the impact resistance is lowered, and there is a concern that the instrument may be damaged during use. Further, when the syringe barrel is stored in a refrigerator, the temperature of the syringe barrel itself is lowered, so that low temperature impact resistance is also required. Furthermore, in order to confirm the bubbles during use, transparency is required, and it is necessary to minimize the appearance of foreign substances that may cause poor appearance and unintended danger in the molded product.
Also in some dialysers, hollow fibers are dried with hot air in some products, so if the product rigidity is low, there is a concern that the product will be deformed during drying, and if the rigidity is high and impact resistance is low, the dialyzer is set in the dialyzer At this time, there is a concern that the D nozzle portion may be broken or may be damaged if the dialyzer is struck with forceps or the like to remove bubbles remaining in the dialyzer before use. In addition, in order to confirm the state of breakage of the hollow fiber, transparency is also required, and it is necessary to minimize the appearance of foreign matters that cause poor appearance and unintended danger in the molded product.

Propylene polymers are propylene homopolymers in terms of rigidity, heat resistance and gas barrier properties, and propylene-ethylene random copolymers in terms of transparency and impact resistance. In this respect, a propylene-ethylene block copolymer is suitable, and is selectively used as appropriate depending on the situation.
However, the propylene homopolymer is not as transparent as the propylene-ethylene block copolymer, and it is difficult to exhibit sufficient performance in terms of impact resistance. A conventional propylene-ethylene random copolymer is excellent in transparency but may not have sufficient impact resistance. Although the propylene-ethylene block copolymer has excellent impact resistance, it has a drawback that it is extremely difficult to impart transparency. In addition, the added elastomer and subsequently copolymerized ethylene-propylene random copolymer may cause stickiness and bleed-out of the molded product, which may cause problems such as drug adsorption and poor appearance. However, it has the disadvantage of inducing problems such as adhesion and contamination to the mold. Patent Document 1 discloses a propylene block copolymer having a homopolypropylene block and a copolymer block having specific physical properties, and Patent Document 2 includes a random copolymer having a different amount of ethylene using a metallocene catalyst. Propylene-ethylene block copolymers obtained by sequential polymerization were obtained by sequentially polymerizing blocks (A) and blocks (B) having different physical properties in Patent Documents 3 to 5, respectively. Propylene block copolymers are each disclosed. However, these techniques are not sufficient to obtain an injection molded product having a good balance between rigidity and impact resistance, excellent low-temperature impact resistance and transparency, and less stickiness and bleeding out.

In addition, since the medical propylene-based resin composition is used as a member of a medical instrument, various sterilization resistances performed at the final product stage are required. The sterilization generally performed includes high pressure steam sterilization, ethylene oxide gas sterilization, and radiation sterilization. Radiation sterilization can be divided into sterilization by γ-ray irradiation and sterilization by electron beam irradiation. A characteristic as a medical propylene-based resin composition required for high-pressure steam sterilization is high heat distortion resistance, and a propylene homopolymer is generally used. The medical propylene-based resin composition required for radiation sterilization is characterized by preventing significant resin deterioration due to radiation irradiation and preventing deterioration of elution due to decomposition of the prescribed additive. It is known that irradiation of a propylene-based resin composition with a radiation breaks the tie molecular chain and significantly lowers impact resistance (see, for example, Non-Patent Document 1).
As a method for preventing a decrease in impact resistance due to radiation, a method of blending polyethylene or hydrogenated SBR resistant to radiation sterilization into a propylene polymer is known (for example, see Non-Patent Document 1). In addition, the propylene-type polymer said here is a propylene homopolymer, a propylene-ethylene random copolymer, and a propylene-ethylene block copolymer.
However, since polyethylene stays in the dead space of the hot runner in the molding machine and heat deteriorates, it crosslinks and gels, so the propylene-based resin composition blended with polyethylene appears in the molded product as a foreign matter. May be easy to do. This possibility is especially true when the polyethylene to be blended has a large molecular weight, or when the organic peroxide compounded to adjust the molecular weight of the propylene resin composition is normally decomposed during pelletization in a nitrogen atmosphere. If the unreacted material remains in the pellet without reacting, it may become prominent. This is considered to be caused by oxidative degradation in addition to decomposition of the organic peroxide because it is plasticized in an air atmosphere in normal injection molding. Moreover, since hydrogenated SBR has a higher price as a resin than polypropylene, there is a drawback that a propylene-based resin composition cannot be produced at a low cost. On the other hand, as a method for increasing the resistance of polypropylene itself to radiation sterilization, there is a method in which propylene and ethylene are copolymerized in a single polymerization tank (see, for example, Non-Patent Document 1). However, the conventional method requires excessive copolymerization of ethylene in order to give excellent resistance to radiation sterilization. On the other hand, the rigidity is significantly reduced, and the rigidity and impact resistance after radiation sterilization are reduced. It was difficult to maintain a balance of sex.

  Furthermore, in order to mold a thin injection molded product typified by a syringe, high fluidity in the mold is required. There is a method of increasing the MFR (melt flow rate) of the propylene-based resin composition in order to enhance the fluidity in the mold, but the molecular weight decreases as the MFR increases, so that the impact resistance, particularly after radiation sterilization Impact resistance is reduced. Therefore, in order to achieve both fluidity in the mold and impact resistance, there has been a conventional method of blending polyethylene or hydrogenated SBS as a modified rubber component with a high MFR propylene polymer. It was difficult to achieve both high fluidity in the mold and impact resistance with the propylene polymer itself without adding a rubber component.

On the other hand, in order to improve the performance of the propylene-based polymer, the performance has been supplemented by blending a nucleating agent.
For example, as a nucleating agent for modifying a propylene-based polymer, a sorbitol-based transparent nucleating agent (see, for example, Patent Document 6) or an organic phosphate-based rigid nucleating agent (for example, improving the transparency and molding processability) Patent Document 7), triaminobenzene-based rigid nucleating agent (see, for example, Patent Document 8) and the like are widely used.

  Molded products using sorbitol-based nucleating agents are excellent in transparency, and those added with organic phosphoric acid-based nucleating agents are excellent in low bleed-out properties of nucleating agents, and triaminobenzene-based rigid nucleating agents are added. Is excellent in low bleed-out property, low foreign substance appearance property, low elution property, and transparency. When used in medical applications, it is necessary to formulate with particular attention to the balance between rigidity and impact resistance after sterilization and low elution.

  In addition, it is also known that the impact resistance after radiation sterilization is significantly reduced by blending a nucleating agent with a conventional propylene-based resin composition as compared with those without a nucleating agent (for example, Non-patent document 1).

Furthermore, it is also known that additives in the propylene-based resin composition are decomposed by performing radiation sterilization (see, for example, Non-Patent Documents 2 and 3). Degraded additives tend to bleed out by lowering the molecular weight, particularly affecting the results of the eluate test. In addition, for example, in the case of a syringe, there is a concern that when the medicine is filled in the syringe barrel, the drug effect is affected when the additive which has been decomposed and reduced in molecular weight on the inner surface of the syringe barrel is bleed out. In general, the migration rate of the additive is higher in the amorphous region than in the crystalline phase, so that bleedout due to the decomposition of the additive after radiation sterilization is included in the amorphous region of the propylene polymer. It is thought that when an additive is decomposed, it has an effect. Therefore, it is estimated that the nucleating agent considered to be usually incorporated in the crystal phase of the propylene polymer is hardly affected by bleed out. On the other hand, in order to improve the resistance after radiation sterilization of the propylene-based polymer excluding the propylene homopolymer, when a large amount of ethylene is copolymerized, the degree of crystallinity decreases and the proportion of the crystal phase decreases. For this reason, the nucleating agent that is normally considered to be incorporated into the crystal phase becomes supersaturated with respect to the ratio of the crystal phase and is present in the amorphous phase, which is considered to be affected by radiation irradiation. Further, additive bleedout is believed to have an interaction effect between the additives. This is because the easy bleedout additive or other additives are decomposed by irradiation to reduce the molecular weight to become an easy bleedout product, but other additives or other additives are decomposed by irradiation. And by intermolecular interaction, the other bleed-out additive or other bleed-out product is pulled into the other additive or other additive decomposed by irradiation, or both As a result of the association, the compatibility with the propylene-based polymer is lowered, and it can be considered that bleeding occurs. Intermolecular interactions mentioned here include hydrogen bonds, van der Waals forces, and London dispersion forces.
Furthermore, the influence of radiation irradiation is also received by the propylene-based polymer itself, and the amount and type of the deteriorated product generated changes. This differs depending on whether the irradiation atmosphere is an air atmosphere or a nitrogen atmosphere. Generally, since irradiation is performed in an air atmosphere, various kinds of oxidized deterioration products are generated.
Since these factors are influenced by various factors, it is impossible to elucidate them with current technology. Therefore, the development of medical propylene resin compositions with excellent impact resistance and low elution properties after radiation sterilization is impossible to predict with existing technologies. Types of propylene polymers, nucleating agents It can be developed only by extensive screening such as selection of other additives. Therefore, it has good moldability during injection molding, excellent balance between rigidity and impact resistance, low temperature impact resistance, appearance of low foreign matter and transparency, especially in impact resistance and low elution after radiation sterilization. It is extremely difficult to develop an excellent medical propylene resin composition.

JP-A-11-349649 Japanese Patent Laid-Open No. 06-287257 Japanese Patent Laid-Open No. 11-228648 JP-A-11-240929 JP-A-11-349650 JP-A-53-117044 Japanese Patent Laid-Open No. 05-140466 International Publication No. 2011-089133

Radiation processing of polymer: Published April 15, 2000, Rubber Digest Co., Ltd. Food irradiation No. 38 No. 1, No. 2 (2003) p. 11-22 Radiation Physics and Chemistry 75 (2006) p. 87-97

  Therefore, the molding processability at the time of injection molding represented by products for medical use such as syringes and dialyzers is good, the balance between rigidity and impact resistance, low temperature impact resistance, low foreign matter appearance and transparency, In particular, there is a strong demand for a propylene-based resin composition for medical use that is excellent in impact resistance and low dissolution after radiation sterilization.

  The object of the present invention is to solve the above-mentioned drawbacks and to have good molding processability at the time of injection molding, excellent balance between rigidity and impact resistance, low-temperature impact resistance, low foreign matter appearance and transparency. In particular, it has excellent impact resistance after radiation sterilization and low elution, and JIS T3210: 2011 6 chemical requirements described in sterilized syringes, or Yakusei No.494 dialysis type artificial kidney device approval criteria IV The object is to provide a medical propylene-ethylene resin composition that satisfies the heavy metal test, the lead test, the cadmium test, and the eluate test described in the quality of blood circuit and test method after radiation sterilization, and an injection molded product thereof.

As a result of intensive studies to solve the above problems, the present inventors have good moldability at the time of injection molding when two types of propylene-ethylene copolymers having different ethylene contents are used at a specific weight ratio. Excellent balance between rigidity and impact resistance, low-temperature impact resistance, low foreign substance appearance and transparency, especially excellent impact resistance after radiation sterilization, low elution, and JIS T3210: 2011 sterilized injection 6 chemical requirements listed on the tube, or Yakusei No.494 dialysis artificial kidney device approval criteria IV quality of blood circuit and test methods for heavy metal, lead test, cadmium test, eluate test described in radiation sterilization The present invention was completed by finding that a later-obtained medical propylene-ethylene resin composition was obtained.
The present invention relates to a medical propylene-ethylene resin composition comprising two types of propylene-ethylene copolymers having different ethylene contents, and an injection molded product thereof.
[1] The melt flow rate (hereinafter sometimes abbreviated as MFR) conforming to JIS K7210 (230 ° C., 2.16 kg load) is 10 to 300 g / 10 min with an ethylene content of 0.1 to 3% by weight. A medical propylene-ethylene resin composition comprising a propylene-ethylene copolymer (A), a propylene-ethylene copolymer (B) having an ethylene content of 5 to 20% by weight and an MFR of 1 to 50 g / 10 min. Yes, the weight ratio of propylene-ethylene copolymer (A) and propylene-ethylene copolymer (B) is 90: 10-60: 40, and the ethylene content of the medical propylene-ethylene resin composition is 2-2. A medical propylene-ethylene resin composition that is 8% by weight.
[2] The MFR ratio (A / B) of the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B) is 1 to 30, and the MFR of the medical propylene-ethylene resin composition is 20 The medical propylene-ethylene resin composition according to [1], which is ˜100 g / 10 min.
[3] A medical propylene-ethylene resin composition, wherein the medical propylene-ethylene resin composition according to [1] or [2] contains a nucleating agent.
[4] An injection molded product for medical use obtained using the medical propylene-ethylene resin composition according to any one of [1] to [3].
[5] An injection molded product for medical use in which the injection molded product for medical use according to [4] is sterilized by γ rays or electron beams.
[6] An injection molded product for medical use, wherein the molded product according to [4] or [5] is a syringe member.
[7] An injection molded product for medical use, wherein the molded product according to [4] or [5] is an artificial dialysis member.

  The medical propylene-ethylene resin composition of the present invention has good molding processability at the time of injection molding, is excellent in the balance between rigidity and impact resistance, low-temperature impact resistance, low foreign matter appearance and transparency, particularly radiation. Excellent chemical resistance after sterilization, low elution, and 6 chemical requirements as described in JIS T3210: 2011 sterilized syringe or Yakusei No.494 dialysis artificial kidney device approval criteria IV Blood circuit It has excellent properties of satisfying the heavy metal test, lead test, cadmium test, and eluate test described in the quality and test methods after radiation sterilization. In addition, JIS T3210: 2011 6 chemical requirements described in sterile syringes and Yakusei No.494 dialysis artificial kidney device approval criteria IV blood circuit quality and test methods described in heavy metal test, lead test, cadmium test In the eluate test, both standards may be satisfied simultaneously, or only one of the standards may be satisfied.

It is a conceptual diagram of artificial dialysis. It is principal part sectional drawing of a dialyzer. It is sectional drawing of a syringe. 2 is a flow sheet of a continuous horizontal gas phase polymerization apparatus used in Examples.

  Embodiments of the present invention will be described in detail below. However, the description of the constituent elements described below is an example of the embodiments of the present invention, and the present invention is not limited to these contents.

[Propylene-ethylene copolymer (A)]
The propylene-ethylene copolymer (A) used in the present invention satisfies the following characteristics.
Characteristic 1: MFR
The MFR of the propylene-ethylene copolymer (A) used in the present invention needs to be in the range of 10 to 300 g / 10 min, preferably 30 to 200 g / 10 min, more preferably 50 to 150 g / 10 min. If it is above the lower limit of this range, the moldability is improved due to the improvement of fluidity, and even when the molded product is molded with a thickness of 2.5 mm or less, the molding orientation is difficult to be applied and impact is applied. In this case, cracks can be prevented from occurring in the molding orientation direction, and those having an upper limit value or less are preferable in terms of economy because the productivity of the resin composition is good and excellent in impact resistance after radiation sterilization of the molded product.
The method for controlling the MFR value is well known, and can be easily adjusted by adjusting the temperature and pressure, which are polymerization conditions, or by controlling the amount of hydrogen added during the polymerization of a chain transfer agent such as hydrogen.
In the present invention, the MFR of the propylene-based resin is JIS K7210: 1999 “Method of plastic-thermoplastic plastic melt mass flow rate (MFR) and test method for melt volume flow rate (MVR)”, condition M (230 ° C, 2.16 kg load), and the unit is g / 10 min. In addition, a method for adjusting MFR by CR (control rheology) using a molecular weight modifier is generally known. However, in the present invention, it is possible to adjust MFR only by polymerization conditions without CR. From the viewpoint of preventing resin burn at the time.

Characteristic 2: Ethylene content The ethylene content of the propylene-ethylene copolymer (A) used in the present invention needs to be in the range of 0.1 to 3% by weight, preferably 1.0 to 2.8% by weight. More preferably, it is 1.5 to 2.6% by weight. If it is at least the lower limit of this range, the transparency of the molded article becomes good and the impact resistance after radiation sterilization is excellent. On the other hand, if it is less than or equal to the upper limit, the crystallization temperature rises and the solidification at the time of molding becomes faster and the molding processability becomes good.
The ethylene content can be adjusted by controlling the monomer composition of propylene and ethylene during polymerization.

[Propylene-ethylene copolymer (B)]
The propylene-ethylene copolymer (B) used in the present invention satisfies the following characteristics.
Characteristic 1: MFR
The MFR of the propylene-ethylene copolymer (B) used in the present invention needs to be in the range of 1 to 50 g / 10 min, preferably 1 to 30 g / 10 min, more preferably 1 to 15 g / 10 min, most preferably. Is 1 to 10 g / 10 min. If it is at least the lower limit of this range, the dispersibility in the propylene-ethylene copolymer (A) is improved, and it becomes possible to suppress the generation of fish eyes in the molded product. When the amount is not more than the upper limit, the low crystal component is less likely to bleed on the surface, so that the drug adsorption is good and the impact resistance after radiation sterilization is good. In addition, a method for adjusting MFR by CR (control rheology) using a molecular weight modifier is generally known. However, in the present invention, it is possible to adjust MFR only by polymerization conditions without CR. From the viewpoint of preventing resin burn at the time.

Characteristic 2: Ethylene content The ethylene content of the propylene-ethylene copolymer (B) used in the present invention needs to be in the range of 5 to 20 wt%, preferably 7 to 15 wt%, more preferably 8 to 13% by weight. When it is at least the lower limit of this range, the impact resistance of the molded product after radiation sterilization is improved. Further, when the amount is not more than the upper limit, the compatibility with the propylene-ethylene copolymer (A) is improved, thereby improving the transparency of the molded product, and the propylene-ethylene copolymer (B) is formed on the surface of the molded product. By making it difficult to bleed, stickiness and drug adsorption are improved.
Here, solid viscoelasticity was measured as an index for evaluating the compatibility of the mixture of the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B), and the temperature was determined to be 0 ° C. or lower in the temperature-tan δ curve. It is necessary to confirm whether it has a peak. When taking a phase separation structure, the glass transition temperature of the amorphous part component contained in the propylene-ethylene copolymer (A) and the glass transition temperature of the amorphous part component contained in the propylene-ethylene copolymer (B). Since each is different, there are a plurality of peaks. Conversely, when they are compatible, both components are mixed in the order of molecules and have a single peak at a temperature intermediate between the glass transition temperatures of both components. That is, whether or not the phase separation structure is taken can be determined in the temperature-tan δ curve in the solid viscoelasticity measurement, and in order to maintain transparency, the tan δ curve has a single peak at 0 ° C. or lower. is necessary.

Specifically, solid viscoelasticity measurement is performed by applying a sinusoidal strain of a specific frequency to a strip-shaped sample piece and detecting the generated stress. Here, the frequency is 1 Hz and the measurement temperature is raised stepwise from −60 ° C. until the sample is melted and cannot be measured. Further, it is recommended that the magnitude of distortion is about 0.1 to 0.5%. From the obtained stress, the storage elastic modulus G ′ and the loss elastic modulus G ″ are obtained by a known method, and the loss tangent (= loss elastic modulus / storage elastic modulus) defined by this ratio is plotted against the temperature. It shows a sharp peak in the temperature range below 0 ° C. Generally, the peak of the tan δ curve below 0 ° C. is for observing the glass transition of the amorphous part, and here the peak temperature is defined as the glass transition temperature Tg (° C.). Define.
As a specific example of the measurement, a sample was cut from a sheet of 2 mm thickness formed by injection molding under the following conditions into a strip shape of 10 mm width × 18 mm length × 2 mm thickness, and the apparatus was manufactured by Rheometric Scientific. ARES is used. The frequency is 1 Hz. The measurement temperature is raised stepwise from −60 ° C., and measurement is performed until the sample is melted and cannot be measured. The strain is performed in the range of 0.1 to 0.5%.
Sample preparation condition standard number: JIS-7152 (ISO294-1)
Molding machine: IS80 injection molding machine manufactured by Toyo Machine Metal Co., Ltd. Setting temperature: 165 ° C, 200 ° C, 200 ° C, 200 ° C from below the hopper
Mold temperature: 40 ℃
Injection speed: 200 mm / s (speed in the mold cavity)
Injection pressure: 800 kgf / cm ²
Holding pressure: 800 kgf / cm ²
Holding time: 40 seconds Mold shape: Flat plate (thickness 2 mm, width 30 mm, length 90 mm)

[Propylene-ethylene resin composition for medical use]
The weight ratio of the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B) used in the present invention needs to be in the range of 90:10 to 60:40, preferably 87:13. 65:35, more preferably 84:16 to 70:30. When the upper limit value of the propylene-ethylene copolymer (A) is 90 or less, the impact resistance after radiation sterilization of the molded product is improved. Improves.

The medical propylene-ethylene resin composition of the present invention satisfies the following characteristics.
Characteristic 1: MFR
The MFR of the medical propylene-ethylene resin composition of the present invention is preferably in the range of 20 to 100 g / 10 min, more preferably 25 to 50 g / 10 min.
When the MFR is 20 g / 10 min or more, molding processability is improved due to improvement in fluidity, and when it is 100 g / 10 min or less, impact resistance after radiation sterilization is improved. Moreover, it is preferable that the MFR ratio (A / B) of a propylene-ethylene copolymer (A) and a propylene-ethylene copolymer (B) is the range of 1-30, More preferably, it is 3.5-30. More preferably, it is 5-30, Most preferably, it is 10-30. When it is above the lower limit of this range, the impact resistance is improved, and when it is below the upper limit, the dispersibility of the propylene-ethylene copolymer (B) with respect to the propylene-ethylene copolymer (A) is improved and the transparency is improved. To do. In addition, a method for adjusting MFR by CR (control rheology) using a molecular weight modifier is generally known. However, in the present invention, it is possible to adjust MFR only by polymerization conditions without CR. From the viewpoint of preventing resin burn at the time.

Characteristic 2: Ethylene content The ethylene content of the medical propylene-ethylene resin composition of the present invention needs to be in the range of 2 to 8% by weight, preferably 3 to 7% by weight, more preferably 3 to 6%. % By weight, most preferably 4-6% by weight.
When it is at least the lower limit of this range, the transparency and impact resistance of the molded product are improved. If it is less than or equal to the upper limit, stickiness is reduced due to a decrease in the low crystalline component, and drug adsorption is improved.
Further, the medical propylene-ethylene resin composition of the present invention preferably has a −15 ° C. soluble content by a temperature-temperature elution fractionation method (TREF) in order to reduce stickiness and drug adsorption, preferably 10% by weight or less. It is important that the content is 9% by weight or less, more preferably 8% by weight or less, particularly preferably 7% by weight or less, and most preferably 6% by weight or less. If this soluble content is within this range, the adverse effects on product quality due to stickiness and bleed-out can be suppressed, and powder particles do not flow poorly due to particle aggregation and reactor adhesion during polymer production. A polymer can be produced stably.
In the present invention, the TREF measurement method is specifically performed as follows. A sample is dissolved in o-dichlorobenzene (containing 0.5 mg / ml BHT (2,6-di-t-butyl-p-cresol)) at 140 ° C. to obtain a solution. After this is introduced into a TREF column at 140 ° C., it is cooled to 100 ° C. at a temperature decreasing rate of 8 ° C./min, subsequently cooled to −15 ° C. at a temperature decreasing rate of 4 ° C./min, and held for 60 minutes. Thereafter, -15 ° C o-dichlorobenzene (containing 0.5 mg / ml BHT), which is a solvent, flows through the column at a flow rate of 1 ml / min, and is dissolved in -15 ° C o-dichlorobenzene in the TREF column. The components are eluted for 10 minutes, and then the column is linearly heated to 140 ° C. at a rate of temperature increase of 100 ° C./hour to obtain an elution curve. The TREF evaluation method is well known to those skilled in the art. For example, detailed measurement methods are described in the following documents.
G. Glockner, J. et al. Appl. Polym. Sci. : Appl. Polym. Symp. 45, 1-24 (1990)
L. Wild, Adv. Polym. Sci. 98, 1-47 (1990)
J. et al. B. P. Soares, A .; E. Hamielec, Polymer; 36, 8, 1639-1654 (1995)

In addition, the ratio of the propylene-ethylene copolymer (A) and (B) in the medical propylene-ethylene-based resin composition is a value obtained from the material balance at the time of polymerization when manufactured by continuous polymerization, When manufactured by blending, it is a value obtained from each prescription ratio.
Each ethylene content is a value obtained by measurement by ¹³ C-NMR method.

The catalyst used for obtaining the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B) used in the present invention is not particularly limited, and a known catalyst can be used. is there. For example, a so-called Ziegler-Natta catalyst or metallocene catalyst (for example, described in JP-A-5-295022) in which a titanium compound and organoaluminum are combined can be used.
In the present invention, a medical propylene-ethylene resin composition is particularly preferred because of its excellent injection molding processability and good balance between rigidity and impact resistance after radiation sterilization. High Ziegler-Natta catalysts are more preferred. In addition, when the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B) are obtained with the Ziegler-Natta catalyst, the molecular weight distribution is generally broader than that obtained with the metallocene catalyst. The compatibility of the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B) is increased due to the increase in fluidity, the injection molding processability is improved, and the composition distribution is widened. Improves impact resistance after radiation sterilization.
Specifically, regarding stereoregularity, the isotactic pentad fraction (mmmm) of the polypropylene segment is 90% or more, preferably 94% or more, more preferably 97% or more. When the isotactic pentad fraction (mmmm) is 90% or more, the balance between rigidity and impact resistance after radiation sterilization is good. Here, the isotactic pentad fraction (mmmm) is a value measured by ¹³ C-NMR method.

  Regarding the molecular weight distribution, the value of (weight average molecular weight) / (number average molecular weight), which is an index of the width of the molecular weight distribution, is preferably 2.0 to 8.0, more preferably 2.5 to 7.0, and further Preferably it is 3.0-6.0. When it is at least the lower limit, the resin fluidity during injection molding is excellent. On the other hand, if it is less than or equal to the upper limit, molding orientation is difficult to be applied, and cracking along the molding orientation hardly occurs, and the impact resistance after radiation sterilization is good. Here, the weight average molecular weight and the number average molecular weight are values measured by a gel permeation chromatography (GPC) method described later.

Regarding the production process of the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B), any process may be used as long as the above-mentioned characteristics are satisfied. The mixture of A) and the propylene-ethylene copolymer (B) may be produced by any method as long as the above-mentioned characteristics are satisfied. In particular, it is preferable to produce a mixture of propylene-ethylene copolymer (A) and propylene-ethylene copolymer (B) by a two-stage continuous gas phase polymerization method using a horizontal reactor. The reason for this is that when a mixture of propylene-ethylene copolymer (A) and propylene-ethylene copolymer (B) is produced by a two-stage continuous polymerization method, the method of producing by a bulk or slurry batch polymerization method is a unit. Since the yield of the polymer per unit polymerizer per time is lower than that in the gas phase continuous polymerization method, the cost is increased. On the other hand, in the two-stage continuous gas phase polymerization method using a gas phase vertical reactor, a distribution occurs in the residence time of each catalyst particle in the polymerizer of each stage, so that the propylene-ethylene copolymer (A) and propylene-ethylene are produced. It becomes a collection of polymer particles having a distribution in the content ratio of the copolymer (B), and a defect in quality due to the nonuniformity of the distribution occurs. In addition, as a problem when the polymerization process of the propylene-ethylene copolymer (B) containing a relatively large amount of ethylene in the second stage is carried out by gas phase polymerization using a gas medium, the amount of polymerization in the second stage is increased. As the adhesiveness of the polymer particles increases, stable operation becomes difficult, and if the polymerization heat is not sufficiently cooled, adhesion to the polymerizer walls, stirring blades, etc. occurs. One way to prevent stickiness is to reduce the amount of catalyst that enters the second stage polymerization reactor while the residence time is short. Disadvantages such as increase in operation and complexity of operation. Therefore, regarding the production process of the mixture of propylene-ethylene copolymer (A) and propylene-ethylene copolymer (B), the residence time is obtained by removing the heat of polymerization using the latent heat of vaporization of liquefied propylene. A horizontal reactor having a stirrer that rotates about a horizontal axis that enables production of a mixture of propylene-ethylene copolymer (A) having a narrow distribution and high quality, and propylene-ethylene copolymer (B) Most preferably, it is produced by a two-stage continuous gas phase polymerization process.
When a mixture of propylene-ethylene copolymer (A) and propylene-ethylene copolymer (B) is produced by a two-stage continuous gas phase polymerization process having the above horizontal reactor, the first stage is propylene-ethylene. After the copolymer (A) is polymerized, the propylene-ethylene copolymer (B) is polymerized in the second stage with the same catalyst particles, so that the propylene-ethylene copolymer (A) and propylene are contained in the same powder particles. -The ethylene copolymer (B) coexists. In that case, the dispersibility of the propylene-ethylene copolymer (B) with respect to the propylene-ethylene copolymer (A) becomes the best, and when the powder particles are pelletized into a molded product, the propylene- produced separately The ethylene copolymer (A) pellets and the propylene-ethylene copolymer (B) pellets are melt-kneaded with an extruder and then compared with the molded one, the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer are compared with those molded. Since the compatibility of the polymer (B) is remarkably good, it is possible to obtain a high-quality molded product resulting from the uniformity of physical properties in the molded product, excellent transparency, and resistance to radiation after sterilization. What has excellent impact properties can be obtained.

[Nucleating agent]
When the medical propylene-ethylene resin composition of the present invention contains a nucleating agent, a molded product with better transparency can be obtained. As the nucleating agent, a nucleating agent comprising a triaminobenzene derivative, an organic phosphate metal salt, an organic monocarboxylic acid metal salt, an organic dicarboxylic acid metal salt, a polymer nucleating agent, dibenzylidene sorbitol or a derivative thereof, a metal of diterpenic acids Salt or the like is used.
Examples of the organic phosphate metal salt include sodium-2,2′-methylene-bis (4,6-di-t-butylphenyl) phosphate, sodium-2,2′-ethylidene-bis (4,6 -Di-t-butylphenyl) phosphate, lithium-2,2'-methylene-bis (4,6-di-t-butylphenyl) phosphate, lithium-2,2'-ethylidene-bis (4,6 -Di-t-butylphenyl) phosphate, sodium-2,2'-ethylidene-bis (4-i-propyl-6-t-butylphenyl) phosphate, lithium-2,2'-methylene-bis (4 -Methyl-6-tert-butylphenyl) phosphate, lithium-2,2'-methylene-bis (4-ethyl-6-tert-butylphenyl) phosphate, sodium-2 , 2'-butylidene-bis (4,6-di-methylphenyl) phosphate, sodium-2,2'-butylidene-bis (4,6-di-t-butylphenyl) phosphate, sodium-2,2 '-T-octylmethylene-bis (4,6-di-methylphenyl) phosphate, sodium-2,2'-t-octylmethylene-bis (4,6-di-t-butylphenyl) phosphate, calcium -Bis [(2,2′-methylene-bis (4,6-di-t-butylphenyl) phosphate], magnesium-bis [2,2′-methylene-bis (4,6-di-t-butyl) Phenyl) phosphate], barium-bis [2,2′-methylene-bis (4,6-di-t-butylphenyl) phosphate], sodium-2,2′-methylene-bis (4- Til-6-tert-butylphenyl) phosphate, sodium-2,2′-methylene-bis (4-ethyl-6-tert-butylphenyl) phosphate, sodium-2,2′-ethylidene-bis (4- s-butyl-6-tert-butylphenyl) phosphate, sodium-2,2′-methylene-bis (4,6-di-methylphenyl) phosphate, sodium-2,2′-methylene-bis (4 6-di-ethylphenyl) phosphate, potassium-2,2′-ethylidene-bis (4,6-di-t-butylphenyl) phosphate, calcium-bis [2,2′-ethylidene-bis (4 6-di-t-butylphenyl) phosphate], magnesium-bis [2,2′-ethylidene-bis (4,6-di-t-butylphenyl) phosphate] Barium-bis [2,2′-ethylidene-bis (4,6-di-t-butylphenyl) phosphate], aluminum-tris [2,2′-methylene-bis (4,6-di-t-butylfell) ) Phosphate], aluminum-tris [2,2′-ethylidene-bis (4,6-di-t-butylphenyl) phosphate], aluminum hydroxy-bis [2,2′-methylene-bis (4 6-di-t-butylphenyl) phosphate], aluminum dihydrooxy-2,2′-methylene-bis (4,6-di-t-butylphenyl) phosphate, and the like.

  Examples of the organic monocarboxylic acid metal salt include metal salts such as benzoic acid and allyl-substituted acetic acid. Specifically, benzoic acid, p-isopropylbenzoic acid, o-tertiary butylbenzoic acid, Examples include pt-butylbenzoic acid, monophenylacetic acid, diphenylacetic acid, phenyldimethylacetic acid, adipic acid and their Li, Na, Mg, Ca, Ba, Al salts, and the like. Examples of the organic dicarboxylic acid metal salt include succinic acid, glutaric acid, adipic acid, suberic acid, sebacic acid, phthalic acid, cyclohexanecarboxylic acid, norbornane dicarboxylic acid and their Li, Na, Mg, Ca, Ba, Al A salt etc. can be mentioned. Examples of the polymer nucleating agent include polyvinylcyclohexane and poly-3-methyl-butene-1.

  Examples of the dibenzylidene sorbitol or a derivative thereof include 1,3,2,4-dibenzylidene sorbitol, 1,3-benzylidene-2,4-p-methylbenzylidene sorbitol, 1,3-benzylidene-2,4- p-ethylbenzylidene sorbitol, 1,3-p-methylbenzylidene-2,4-benzylidene sorbitol, 1,3-p-ethylbenzylidene-2,4-benzylidene sorbitol, 1,3-p-methylbenzylidene-2,4 -P-ethylbenzylidene sorbitol, 1,3-p-ethylbenzylidene-2,4-p-methylbenzylidene sorbitol, 1,3,2,4-di (p-methylbenzylidene) sorbitol, 1,3,2,4 -Di (p-ethylbenzylidene) sorbitol, 1,3,2,4-di (pn- (Lopylbenzylidene) sorbitol, 1,3,2,4-di (p-i-propylbenzylidene) sorbitol, 1,3,2,4-di (pn-butylbenzylidene) sorbitol, 1,3,2, 4-di (ps-butylbenzylidene) sorbitol, 1,3,2,4-di (pt-butylbenzylidene) sorbitol, 1,3,2,4-di (p-methoxybenzylidene) sorbitol, , 3,2,4-di (p-ethoxybenzylidene) sorbitol, 1,3-benzylidene-2,4-p-chlorobenzylidenesorbitol, 1,3-p-chlorobenzylidene-2,4-benzylidenesorbitol, 3-p-chlorobenzylidene-2,4-p-methylbenzylidenesorbitol, 1,3-p-chlorobenzylidene-2,4-p-ethylbenzene Dilidenesorbitol, 1,3-p-methylbenzylidene-2,4-p-chlorobenzylidenesorbitol, 1,3-p-ethylbenzylidene-2,4-p-chlorobenzylidenesorbitol, 1,3,2,4- Examples include di (p-chlorobenzylidene) sorbitol, 1,2,3-trideoxy-4,6: 5,7-bis-O-[(4-propylphenyl) methylene] -nonitol. Particularly preferably, 1,3,2,4-dibenzylidene sorbitol, 1,3,2,4-di (p-methylbenzylidene) sorbitol, 1,3-p-chlorobenzylidene-2,4-p-methylbenzylidene Examples include sorbitol, 1,2,3-trideoxy-4,6: 5,7-bis-O-[(4-propylphenyl) methylene] -nonitol.

  The metal salt of the diterpenic acid is a reaction product of the diterpenic acid and a predetermined metal compound such as a magnesium compound or an aluminum compound. Diterpenic acid is a rosin generally known as a natural resin obtained from Pinaceae plants, specifically, natural rosins such as gum rosin, tall oil rosin, wood rosin; disproportionated rosin, hydrogenated rosin, dehydrogenated Various rosins such as rosin, polymerized rosin, α, β-ethylenically unsaturated carboxylic acid-modified rosin; and purified products of the natural rosin and modified rosin are used as raw materials. Examples of the diterpenic acids include pimaric acid, sandaracopimalic acid, parastrinic acid, isopimaric acid, abietic acid, dehydroabietic acid, neoabietic acid, dihydropimaric acid, dihydroabietic acid, tetrahydroabietic acid, and the like.

Of these, a preferred nucleating agent is a nucleating agent comprising an organic phosphate metal salt, an organic dicarboxylic acid metal salt, or a triaminobenzene derivative. These preferred nucleating agents not only improve transparency, but also provide a better balance between stiffness and impact, and have low elution properties while having impact resistance after radiation sterilization suitable for medical applications. In addition, it exhibits good molding processing characteristics such as no foreign matter in the molded product, and provides a balanced and effective effect. Of the organic phosphoric acid ester metal salts and organic dicarboxylic acid metal salts, sodium-2,2'-methylene-bis (4,6-di-t-butylphenyl) phosphate, sodium-2,2'- Ethylidene-bis (4,6-di-t-butylphenyl) phosphate, aluminum-tris [2,2′-methylene-bis (4,6-di-t-butylfell) phosphate], aluminum hydroxy-bis [2,2′-methylene-bis (4,6-di-t-butylphenyl) phosphate], aluminum dihydrooxy-2,2′-methylene-bis (4,6-di-t-butylphenyl) phosphate Phosphate metal salts having bridged substituted aromatic groups such as fete, or sodium 2-cyclohexanedicarboxylate, 1,2-norbornane di Sodium carboxylic acid, alicyclic hydrocarbon dicarboxylic acid metal salts such as 1,2-norbornane magnesium carboxylic acid. Examples of the metal salt include lithium, sodium, potassium, calcium, magnesium, aluminum salts and the like, and more preferred are Group 1 metals such as lithium, sodium and potassium.
The most preferred nucleating agent in the resin composition is a nucleating agent composed of a triaminobenzene derivative, and the nucleating agent composed of a triaminobenzene derivative is excellent in the transparency improving effect and low foreign matter appearance property of the resin composition. In addition, it has an excellent balance between rigidity and impact resistance after radiation sterilization, and furthermore, it can be said to be an optimal nucleating agent because it has a low elution property with very little elution into a chemical solution due to decomposition of the nucleating agent during radiation sterilization.

  Examples of the nucleating agent comprising a triaminobenzene derivative include 1,3,5-tris- [2,2-dimethylpropionylamino) -benzene (CAS No. 745070-64-5), 1,3,5- Tris- [cyclohexylcarbonylamino) -benzene, 1,3,5-tris- [4-methylbenzoylamino) -benzene, 1,3,5-tris- [1-adamantanecarbonylamino) -benzene, 1,3, 5-tris- [3- (trimethylsilyl) propionylamino) -benzene, Nt-butyl-3,5-bis- (pivaloylamino) -benzamide, Nt-octyl-3,5-bis- (pivaloylamino)- Benzamide, Nt-butyl-3,5-bis- (cyclopentanecarbonylamino) -benzamide, N-cyclope Tyl-3,5-bis- (3-methylbutyrylamino) -benzamide, N-cyclopentyl-3,5-bis- (pivaloylamino) -benzamide, 5-pivaloylamino-isophthalic acid N, N′-di-t- Butyldiamide, 5-pivaloylamino-isophthalic acid N, N′-di-t-octyldiamide, 5- (3-methylbutyrylamino) -isophthalic acid N, N′-di-cyclohexyldiamide, 5- (pivaloylamino)- Examples thereof include isophthalic acid N, N′-di-cyclohexyldiamide, 5- (cyclopentanecarbonylamino) -isophthalic acid N, N′-di-cyclohexyldiamide, and preferably 1,3,5-tris- [2 , 2-dimethylpropionylamino) -benzene (CAS No. 745070-64-5).

The content of the nucleating agent other than the nucleating agent comprising the triaminobenzene derivative is preferably 0.01 to 0.7 parts by weight with respect to 100 parts by weight of the medical propylene-ethylene resin composition, and more Preferably it is 0.1-0.5 weight part. When the content of the nucleating agent is 0.01 parts by weight or more, the effect of improving the transparency is sufficient, and when it is 0.7 parts by weight or less, it is advantageous from the viewpoint of the cost (the cost / performance). .
The content of the nucleating agent comprising a triaminobenzene derivative is preferably 0.005 to 0.04 parts by weight, more preferably 0.010 parts per 100 parts by weight of the medical propylene-ethylene resin composition. It is -0.030 weight part, More preferably, it is 0.011-0.020 weight part. If the content of the nucleating agent is 0.005 parts by weight or more, the effect of improving transparency and the balance between rigidity and impact resistance after radiation sterilization are sufficient, and if it is 0.04 parts by weight or less, This is advantageous in terms of the effects (cost / performance).
In addition, you may use these nucleating agents in combination of 2 or more type as long as the effect of this invention is acquired.

[Neutralizer]
In the medical propylene-ethylene resin composition of the present invention, it is desirable to add a neutralizing agent. Specific examples of the neutralizing agent include metal fatty acid salts such as calcium stearate, zinc stearate, and magnesium stearate, hydrotalcite (trade name: DHT-4A, manufactured by Kyowa Chemical Industry Co., Ltd., the following general formula (5) Magnesium aluminum composite hydroxide salt represented by the formula (1), Mizukarak (trade name, lithium aluminum composite hydroxide salt represented by the following general formula (6) manufactured by Mizusawa Chemical Co., Ltd.), and the like. In particular, when used as a member that comes into contact with a long-term chemical solution, such as a prefilled syringe, a kit preparation, or an infusion bag, hydrotalcite or Mizukarak that is difficult to elute into a chemical solution that comes into contact after high-pressure steam sterilization is advantageous. Note that calcium stearate, which also acts as a lubricant, is advantageous for an outer cylinder of a disposable syringe or a cylindrical injection-molded product such as a dialyzer housing.

Mg _1-x Al _x (OH) ₂ (CO ₃ ) _{x / 2} · mH ₂ O (5)
[Wherein x is 0 <x ≦ 0.5, and m is a number of 3 or less. ]

[Al ₂ Li (OH) ₆ ] _n X · mH ₂ O (6)
[Wherein, X is an inorganic or organic anion, n is the valence of the anion (X), and m is 3 or less. ]

  The blending amount of the neutralizing agent is preferably in the range of 0.005 to 0.2 parts by weight and more preferably in the range of 0.02 to 0.15 parts by weight with respect to 100 parts by weight of the polymer mixture. If it is 0.005 parts by weight or more, the effect as a neutralizing agent is sufficient, and if it is 0.2 parts by weight or less, it is advantageous from the viewpoint of cost vs. the above effects (cost / performance).

[Lubricant]
In the medical propylene-ethylene resin composition of the present invention, a lubricant may be blended within a range in which the effects of the present invention are obtained. Examples of the lubricant include known lubricants, but butyl stearate and silicone oil are preferable. Specific silicone oils include dimethylpolysiloxane, methylphenylpolysiloxane, methylhydrodienepolysiloxane, α-ωbis (3-hydroxypropyl) polydimethylsiloxane, polyoxyalkylene (C ₂ -C ₄ ) dimethylpolysiloxane. And a condensate of polyorgano (C ₁ -C ₂ alkyl and / or phenyl) siloxane and polyalkylene (C ₂ -C ₃ ) glycol. Of these, dimethylpolysiloxane and methylphenylpolysiloxane are preferred. In addition, when printing a label directly on the surface of a molded product with a syringe outer cylinder or the like, it is required to have good printability and good printability so that the ink does not peel off during use. In that case, butyl stearate having a sufficient lubricant performance and excellent printability is particularly preferable.

  The blending amount of the lubricant is preferably 0.001 to 0.5 parts by weight, more preferably 0.01 to 0.15 parts by weight, and 0.03 to 0.1 parts by weight with respect to 100 parts by weight of the polymer mixture. Particularly preferred. When the amount is 0.001 part by weight or more, the effect of the lubricant is sufficiently exhibited, and when the amount is 0.5 part by weight or less, it is advantageous from the viewpoint of the cost to the effect (cost / performance).

[Antioxidant]
In the medical propylene-ethylene resin composition of the present invention, it is desirable to incorporate an antioxidant. Specific examples of the antioxidant include bis (2,6-di-t-butyl-4-methylphenyl) pentaerythritol-di-phosphite, di-stearyl-pentaerythritol-di-phosphite, bis (2, 4-di-t-butylphenyl) pentaerythritol-di-phosphite, tris (2,4-di-t-butylphenyl) phosphite, tetrakis (2,4-di-t-butylphenyl) -4,4 Phosphorus-based antioxidants such as' -biphenylene-diphosphonite, tetrakis (2,4-di-t-butyl-5-methylphenyl) -4,4'-biphenylene-diphosphonite, n- Hexadecyl-3,5-di-t-butyl-4-hydroxybenzoate, 2,4-di-t-butylphenyl-3 ′, 5′-di-t-butyl-4′-hydro Cibenzoate, bis (2,2,6,6-tetramethyl-4-piperidyl) sebacate, dimethyl-2-succinate (4-hydroxy-2,2,6,6-tetramethyl-1-piperidyl) Ethanol condensate, poly {[6-[(1,1,3,3-tetramethylbutyl) amino] -1,3,5-triazine-2,4diyl] [(2,2,6,6-tetra Methyl-4-piperidyl) imino] hexamethylene [(2,2,6,6-tetramethyl-4-piperidyl) imino]}, N, N′-bis (3-aminopropyl) ethylenediamine-2,4-bis [N-butyl-N- (1,2,2,6,6-pentamethyl-4-piperidyl) amino] -6-chloro-1,3,5-triazine condensate and other hindered amine stabilizers, 2 , 6-Di-t-butyl-p-cle Tetrakis [methylene (3,5-di-t-butyl-4-hydroxyhydrocinnamate)] methane, 1,3,5-trimethyl-2,4,6-tris (3,5-di-t Phenol-type antioxidants such as -butyl-4-hydroxybenzyl) benzene and tris (3,5-di-t-butyl-4-hydroxybenzyl) isocyanurate, di-stearyl-β, β'-thio-di- And thio-based antioxidants such as propionate, di-myristyl-β, β′-thio-di-propionate, and di-lauryl-β, β′-thio-di-propionate.
In addition, although antioxidant may be used individually or in multiple, the medical propylene-ethylene-based resin composition of the present invention has a discoloration after sterilization when used for a medical molded article for radiation sterilization. From the viewpoint, it is preferable to add a phosphorus-based antioxidant or a hindered amine-based stabilizer. Among phosphorous antioxidants, tris (2,4-di-t-butylphenyl) phosphite is particularly preferable because of excellent balance between resin deterioration suppression and discoloration during radiation sterilization. Among the hindered amine stabilizers, a high molecular weight type hindered amine stabilizer is preferable from the viewpoint of low elution, and dimethyl-2- (4-hydroxy-2,2,6,6-tetramethyl-1-succinate) is particularly preferable. Piperidyl) ethanol condensate has excellent balance between resin deterioration suppression during radiation sterilization, long-term stability of the molded product after sterilization, and discoloration, low elution, and basic hindered amine stability. Since it is weak and close to neutral in the agent, it is preferable because it does not affect the content liquid. It is most preferable to use a phosphorus-based antioxidant and a hindered amine-based antioxidant in combination from the viewpoint of suppressing resin deterioration during radiation sterilization and maintaining long-term stability of the molded product after sterilization.

  Furthermore, in the propylene-ethylene resin composition for medical use according to the present invention, amine-based oxidation represented by the following general formula (7) or the following general formula (8), which has no discoloration by radiation treatment and good NOx gas discoloration resistance. Inhibitors, lactone-based antioxidants such as 5,7-di-t-butyl-3- (3,4-di-methyl-phenyl) -3H-benzofuran-2-one, and the following general formula (9) You may mix | blend a vitamin E type antioxidant in the range with which the effect of this invention is acquired.

[Other additives]
Furthermore, the medical propylene-ethylene-based resin composition of the present invention is a known copper damage preventive agent, ultraviolet absorber, antistatic agent, hydrophilizing agent, slip agent, anti-blocking agent as long as the performance is not impaired. , Antifogging agents, colorants, fillers, polyethylene, olefinic elastomers, non-olefinic elastomers, petroleum resins, antibacterial agents and the like. Moreover, an organic peroxide can also be mix | blended when MFR adjustment is required. However, from the viewpoint of preventing resin burn at the time of molding, it is preferable not to combine polyethylene and a molecular weight modifier such as organic peroxide in combination. Moreover, since there exists a possibility that a burn may generate | occur | produce also when there is much ethylene content of a propylene-ethylene copolymer (B), it is preferable not to mix | blend molecular weight modifiers, such as an organic peroxide.

[Resistance to radiation sterilization]
With respect to the radiation sterilization resistance of the medical propylene-ethylene resin composition of the present invention, an ISO flat plate having a thickness of 2 mm is formed by injection molding and adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% after molding. After conditioning for 72 hours, the Z-average molecular weight (Mz) measured by GPC and γ-ray 50KGY (average dose) were applied in an air atmosphere after conditioning to room temperature, and the room temperature was 23 ° C. After conditioning for another 2 weeks in a constant temperature room at ± 0.5 ° C. and relative humidity 50 ± 5%, when taking a ratio with Mz measured by GPC (Mz after sterilization with γ-ray 50KGY / Mz before sterilization) The ratio is preferably 0.4 or more, more preferably 0.5 or more, still more preferably 0.6 or more, and most preferably 0.7 or more. In the case of 0.4 or more, since the decrease in the high molecular weight component that affects the impact resistance is small, the impact resistance after radiation sterilization is good.
Similarly, an ISO flat plate having a thickness of 2 mm was formed by injection molding, and after conditioning, the temperature was adjusted to a constant temperature room adjusted to 23 ± 5 ° C. and relative humidity 50 ± 5% for 72 hours, and then measured by GPC. Weight-average molecular weight (Mw) and γ-ray 50KGY (average dose) under room temperature conditions after air conditioning after conditioning, and then in a temperature-controlled room at room temperature 23 ° C ± 0.5 ° C and relative humidity 50 ± 5% Further, after adjusting the condition for 2 weeks, when the ratio with Mw measured by GPC was taken (Mw after sterilization with γ rays 50KGY / Mw before sterilization), the ratio is preferably 0.4 or more, more preferably 0. It is 5 or more, more preferably 0.6 or more, and most preferably 0.7 or more. In the case of 0.4 or more, since the decrease in the component on the high molecular weight side that affects the impact resistance is small, the impact resistance after radiation sterilization is good.
Here, the weight average molecular weight (Mw) and the Z average molecular weight (Mz) are values obtained by measurement by gel permeation chromatography (GPC) method, and are specifically determined as follows.
Conversion from the retention volume to the molecular weight is performed using a calibration curve prepared in advance with standard polystyrene.
The standard polystyrene used is F380, F288, F128, F80, F40, F20, F10, F4, F1, A5000, A2500, and A1000, all of which are manufactured by Tosoh Corporation. A calibration curve is created by injecting 0.2 mL of a solution dissolved in ODCB (containing 0.5 mg / mL BHT) to 5 mg / mL. The calibration curve uses a cubic equation obtained by approximation by the least square method. The viscosity equation [η] = K × Mα used for conversion to molecular weight uses the following numerical values.
PS: K = 1.38 × 10 −4, α = 0.7
PP: K = 1.03 × 10−4, α = 0.78
The measurement conditions for GPC are as follows.
Apparatus: Waters GPC (ALC / GPC 150C)
Detector: MIRAN 1A IR detector manufactured by FOXBORO (measurement wavelength: 3.42 μm)
Column: AD806M / S (3 pieces) manufactured by Showa Denko KK
Mobile phase solvent: o-dichlorobenzene Measurement temperature: 140 ° C
Flow rate: 1.0 ml / min Injection volume: 0.2 ml
Sample preparation: Prepare a 1 mg / mL solution using ODCB (containing 0.5 mg / mL BHT) and dissolve at 140 ° C. for about 1 hour.
As a representative example of the antioxidant to be formulated for developing the resistance to radiation sterilization, 0.1 weight of tris (2,4-di-t-butylphenyl) phosphite (trade name: Irgafos 168 manufactured by BASF) is used. 0.05 part by weight of dimethyl-2- (4-hydroxy-2,2,6,6-tetramethyl-1-piperidyl) ethanol condensate (trade name: TINUVIN622 manufactured by BASF) Can be mentioned.

[Method for producing propylene-ethylene resin composition for medical use]
The medical propylene-ethylene resin composition of the present invention comprises the above-mentioned propylene-ethylene copolymer (A), propylene-ethylene copolymer (B), nucleating agent, neutralizing agent, lubricant, antioxidant, And a predetermined amount of various compounding components such as other additives can be obtained by mixing using a conventional mixing apparatus such as a Henschel mixer (trade name), a super mixer, a ribbon blender, a tumbler mixer, a Banbury mixer, and the like. it can. The resulting mixture is melt kneaded and pelletized at a melt kneading temperature of 150 to 300 ° C., preferably 180 to 250 ° C., using a single screw extruder, twin screw extruder, Banbury mixer, plastic bender, roll, etc. Can also be made into a pellet-like composition.

[Molding]
The molded article of the present invention can be obtained by molding the above-described medical propylene-ethylene resin composition with a known extrusion molding machine, injection molding machine, blow molding machine or the like.

  As the molded product of the present invention, an injection molded product, an extrusion molded product, a hollow molded product, a compression molded product, a calendar molded product, a laminated molded product, a fluidized immersion molded product, a blow molded product, a slush molded product, a rotational molded product, There are thermoformed products, CCM molded products, etc. Especially, since this resin composition is excellent in molding processability at the time of injection molding, it is possible to obtain highly accurate injection molded products in a short molding cycle. Suitable for. The resulting injection-molded products are used in a wide variety of medical applications. Specific molded products include medical instruments and containers (disposable syringes and parts thereof, catheters and tubes, infusion bags, blood bags, vacuum blood collection tubes, and surgical instruments. Disposable devices such as non-woven fabrics, blood filters, blood circuits, artificial organ parts such as artificial lungs and colostomy, dialyzers, prefilled syringes, kit preparations, drug containers, test tubes, sutures, compress base materials, dental use Material parts, orthopedic material parts, contact lens cases, contact lens molds, PTP, SP / packaging, P vials, eye drops containers, liquid medicine containers, liquid long-term storage containers, etc.), medical containers ( Infusion packs), daily necessities (costume cases, buckets, washbasins, writing utensils, etc.). Specific examples of other molded products include films (medical packaging materials, etc.), fibers (masks, sanitary nonwoven fabrics, etc.), sheets, and the like.

In the case of medical products, there are many cases of sterilization, and examples of sterilization methods include gas sterilization (EOG), high-pressure steam sterilization, and radiation sterilization (γ rays, electron beams). I can do it. In particular, a molded product obtained using this resin composition is suitable for radiation sterilization, and has excellent impact resistance and low elution properties even after radiation sterilization. The radiation sterilization dose suitable for the present resin composition and molded article is preferably 1 KGY to 100 KGY, and more preferably 10 KGY to 60 KGY. Although depending on the product, sterilization can be performed when the dose exceeds the lower limit, and when the dose is less than the upper limit, the balance between sterility, impact resistance after sterilization and low elution is excellent.
In the resin composition, the average thickness of the molded product is preferably 3.0 mm or less, more preferably 2.5 mm or less, and further preferably 2.0 mm or less, from the viewpoint of transparency. The thickness is particularly preferably 1.5 mm, more particularly preferably 1.2 mm or less, and most preferably 1.0 mm or less. When the thickness is less than the upper limit, sufficient transparency is exhibited. In addition, the average thickness of the molded product referred to here refers to the thickness of the widest part in the ratio of the total surface area of the molded product. As a typical example, the dialyzer refers to the thickness of the cylindrical portion of the housing having the largest surface area among the molded products including the housing and the header, and the syringe refers to the thickness of the cylindrical portion of the outer cylinder.
Further, in the resin composition, from the viewpoint of product rigidity, the flexural modulus of the molded product is preferably 400 to 2000 MPa, more preferably 600 to 1500 MPa, further preferably 700 MPa to 1200 MPa, and most preferably 750 to 700 MPa. 1100 MPa. When it is at least the lower limit value, the molded product is difficult to deform during use, and when it is at most the upper limit value, an injection molded product having a good balance between product rigidity and impact resistance can be obtained. This resin composition is intended to satisfy the heavy metal test, lead test, cadmium test, and eluate test described in Yakuhin No.494 Dialysis Type Artificial Kidney Device Approval Standard IV Blood Circuit Quality and Test Methods after radiation sterilization. Suitable for members for artificial dialysis, especially suitable for the housing and header of dialyzer, and related members. In order to satisfy the 6 chemical requirements described in JIS T3210: 2011 sterilized syringe, Particularly suitable for a disposable syringe.

[dialysis]
When kidney function declines, a device called an artificial kidney removes water and waste products from the blood and makes adjustments to keep the blood from becoming acidic. In general, this is called artificial dialysis. The concept is shown in FIG. 1, and the details of a dialyzer for cleaning blood are shown in FIG.
1 and 2, first, a needle is inserted into the blood vessel of the arm 1 of a person undergoing dialysis, and blood is continuously taken out by the blood pump 3. The blood pump 3 can feed blood in one direction by rotating while pressing the roller against the soft tube 2. The part that cleans blood is a tool called a dialyzer 5. In order to reduce the efficiency when air enters the dialyzer 5 and to protect the safety of a person undergoing dialysis, cylinders called air traps 4 are attached to the front and rear of the dialyzer so that the air does not enter. In the dialyzer 5, excess water and waste products can be discharged from the blood through the semipermeable membrane to clean the blood. At that time, the dialysate is accurately sent to the dialyzer 5 by the adjusting device called the console 6, and the dialysate mixed with moisture and waste inside is carried out to the outside. Various alarms are also attached to the console 6 so that artificial dialysis can be performed safely.

The dialyzer 5 is composed of a cylindrical plastic container having a length of about 30 cm. Among them, about 10,000 very thin threads of hollow fibers 11 that are semipermeable membranes are parallel to the container. It is stored in bundles. The hollow fiber 11 has a hole in the center like macaroni, blood flows through the hole, and dialysate flows outside the hollow fiber 11. Since the hollow fiber 11 is made so that moisture and waste products can be passed through the dialysate, the blood can be cleaned by continuously feeding the blood.
The dialyzer 5 is composed of a cylindrical outer cylinder (housing) 12 and a header 13 for covering the outer cylinder 12. The headers 13 on both sides are coupled to the hollow fiber 11, and when blood flows from the blood inlet 7 of one header 13 and flows through the hollow fiber 11, the moisture and waste in the blood are hollow. It is discharged into the dialysate, which is outside the fiber 11, and then the blood flows out from the blood outlet 8 of the other header 13. In addition, the outer cylinder 12 is provided with a dialysate inlet 9 and a dialysate outlet 10, and has a structure in which moisture and waste products are extracted by circulating the dialysate in the dialyzer 5.

  The resin composition can be suitably used as a member for artificial dialysis, but can be suitably used particularly for a housing and header of a dialyzer that require transparency, impact resistance after radiation sterilization, and low elution.

[Syringe]
Syringes include disposable disposable syringes and prefilled syringes that are pre-filled with a chemical solution, and the resin composition can be particularly suitably used for disposable syringes. A schematic diagram of the syringe is shown in FIG.
The syringe is generally composed of an outer cylinder 14, a pusher 15 and a gasket 16. However, this resin composition is suitable for an outer cylinder and a pusher of a syringe because of its excellent balance between rigidity and impact resistance after radiation sterilization. Can be used. Moreover, since this resin composition is excellent in the low elution property after radiation sterilization, and is excellent also in transparency, it can be used suitably with an outer cylinder.

EXAMPLES Hereinafter, although an Example demonstrates this invention concretely, this invention is not limited at all by these examples. The physical property measurement methods and materials used are as follows.
1. Physical Properties, Evaluation Method (1) MFR The melt flow rate MFR of the pellets of the medical propylene-ethylene resin composition of the present invention was measured in accordance with JIS K-7210-1999 (230 ° C., 2.16 kg load). . In addition, the MFR after radiation sterilization was irradiated with γ-ray 25KGY (average dose) under a room temperature condition in an air atmosphere, and then the room temperature was 23 ° C. ± 0.5 ° C. and the relative humidity was 50 ± 5%. Measurements were made after conditioning for 2 weeks in a temperature-controlled room.
(2) Flexural modulus After molding, a test piece was molded and left in a temperature-controlled room adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% for 72 hours, and then JIS K-7171 (ISO178). Sought in accordance with. The flexural modulus after radiation sterilization is as follows: a test piece molded by injection molding is left in a temperature-controlled room adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% after molding for 72 hours, and then the air atmosphere Then, after irradiating γ-ray 25KGY (average dose) under room temperature conditions, it was further measured and determined after conditioning for 2 weeks in a thermostatic chamber at room temperature 23 ° C. ± 0.5 ° C. and relative humidity 50 ± 5%.
(3) Charpy impact strength A test piece was molded by an injection molding method, and after molding it was left in a temperature-controlled room adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% for 72 hours, and in accordance with JIS K-7111. Asked.
The Charpy impact strength after radiation sterilization is as follows: The test piece molded by injection molding is left in a temperature-controlled room adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% for 72 hours after molding, and then the air atmosphere Then, after irradiating γ-ray 25KGY (average dose) under room temperature conditions, it was further measured and determined after conditioning for 2 weeks in a thermostatic chamber at room temperature 23 ° C. ± 0.5 ° C. and relative humidity 50 ± 5%.
(4) Transparency (haze) An ISO flat plate having a thickness of 1 mm was formed by injection molding, and after standing for 72 hours in a temperature-controlled room adjusted to room temperature 23 ± 5 ° C. and relative humidity 50 ± 5%, JIS K-7136 (ISO14782) It calculated | required based on JIS K-7361-1. Transparency after radiation sterilization is as follows: a test piece molded by injection molding is left in a thermostatic chamber adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% after molding for 72 hours, and then in an air atmosphere. Then, after irradiation with γ-ray 25KGY (average dose) under room temperature conditions, the measurement was further conducted after conditioning for 2 weeks in a thermostatic chamber at room temperature 23 ° C. ± 0.5 ° C. and relative humidity 50 ± 5%.
(5) High-speed surface impact test (high rate, HRIT (breaking energy)):
Testing machine: Servo pulsar high-speed impact testing machine EHF-2H-20L type-with thermostatic chamber (manufactured by Shimadzu Corporation)
Test piece: ISO 2 mm thick flat plate (80 mm × 80 mm × 2 mmt)
Test piece preparation method: Using an injection molding machine with a clamping pressure of 100 tons, injection molding was performed at a molding temperature of 200 ° C. and a mold temperature of 40 ° C., and the room temperature was adjusted to 23 ± 5 ° C. and the relative humidity was adjusted to 50 ± 5%. The test was carried out after being left in a constant temperature room for 72 hours.
Test method: A test piece placed on a support base (hole diameter: 40 mm) was impacted with a dart (20 mm diameter, flat dart having a flat striking surface) as a load sensor at a speed of 6.3 m / sec. The deformation fracture behavior under load was measured, the impact energy absorbed up to the crack initiation point in the obtained impact pattern was calculated, and the impact strength of the material was calculated. The measurement ambient temperature was 23 ± 0.5 ° C. and 10 ± 0.5 ° C. Moreover, the high-speed surface impact test after radiation sterilization is performed by leaving a test piece molded by an injection molding method in a temperature-controlled room adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% for 72 hours after molding. After irradiating γ-ray 25KGY (average dose) under ambient conditions at room temperature, each measurement ambient temperature was further adjusted for 2 weeks in a temperature-controlled room at room temperature 23 ° C ± 0.5 ° C and relative humidity 50 ± 5% Measured and obtained. In this measurement, 1J is the lower limit of measurement.
(6) Hue (YI)
An ISO flat plate having a thickness of 2 mm is formed by an injection molding method, and after molding, left in a temperature-controlled room adjusted to room temperature 23 ± 5 ° C. and relative humidity 50 ± 5% for 72 hours, and then hue according to JIS K-7105 (YI) was determined. The hue (YI) after radiation sterilization was determined by leaving a test piece molded by an injection molding method in a temperature-controlled room adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% for 72 hours after molding. After irradiating γ-ray 25KGY (average dose) under ambient conditions at room temperature, it was measured and determined after conditioning for 2 weeks in a temperature-controlled room at room temperature 23 ° C. ± 0.5 ° C. and relative humidity 50 ± 5%. .
(7) GPC measurement An ISO flat plate having a thickness of 2 mm was formed by an injection molding method, and after the molding, the temperature was adjusted to a room temperature of 23 ± 5 ° C. and a relative humidity of 50 ± 5% for 72 hours. Based on the method, Mw and Mz were measured by GPC and used as values before sterilization. In addition, after condition adjustment, after irradiating γ-ray 50KGY (average dose) under air atmosphere and room temperature conditions, condition adjustment is further performed in a temperature-controlled room at room temperature 23 ° C ± 0.5 ° C and relative humidity 50 ± 5% for 2 weeks. Then, Mw and Mz were measured by GPC, and this was taken as the value after γ-ray 50KGY sterilization. And resistance to radiation sterilization was confirmed from Mw after γ-ray 50KGY / Mw before sterilization and Mz after γ-ray 50KGY / Mz before sterilization.
(8) Foreign matter evaluation A molded product for foreign matter evaluation (10 cm × 10 cm × 1 mm plate) was produced by an injection molding machine with a clamping pressure of 100 tons at a molding temperature of 200 ° C. and a mold temperature of 40 ° C. By visually counting the number of foreign matters in the obtained molded product, the appearance of foreign matters was evaluated according to the following criteria.
When the number of foreign matter visually confirmed is 5 or less, the appearance rate of foreign matter is very low, and the molded product has low appearance of foreign matter and has excellent appearance and transparency. Further, when the number of confirmed foreign matters is 6 to 15, the appearance rate of foreign matters is relatively low, but the molded product has some problems in appearance and transparency. Furthermore, when the number of confirmed foreign substances is 16 or more, the molded article has a high foreign substance appearance ratio with a high foreign substance appearance rate and poor appearance and transparency and a poor product value.
○: Foreign matter appearance rate The number of foreign matters is 5 or less.
Δ: Foreign matter appearance rate 6 to 15 foreign matters / sheet.
X: Foreign matter appearance rate 16 or more foreign matters.
(9) Mold contamination When molding a 10cm x 10cm x 2mm flat plate using an injection molding machine with a mold clamping pressure of 100 tons, the weighing is set to about 70% and continuous so as to be a short shot. The mold contamination was evaluated based on the degree (trace) of deposits on the mold part at the filling end. The molding temperature was 240 ° C and the mold temperature was 40 ° C.
○: Even after 50 shot molding, almost no trace is visible.
(Triangle | delta): 20-50 shot molding is carried out and a trace can be recognized visually.
×: 10 to 20 shots molded, and the traces can be visually confirmed.
(10) Burn test (continuous molding)
Before the test, a screw burn test was performed using an SG125 (screw diameter 36 mm, theoretical injection mass (GPPS) 155 g) injection molding machine manufactured by Sumitomo Heavy Industries, Ltd., which cleaned the inside of the screw and barrel. Test conditions are: molding temperature: 240 ° C., screw rotation speed 100 rpm, back pressure 15%, metering 68 mm, PP resin usage per shot about 60 g, firing speed primary 30%, firing speed secondary (pressure holding speed) 30%, injection pressure primary 30%, injection pressure secondary (holding pressure) 10%, filling time about 0.9 seconds, pressure holding time about 1.2 seconds, metering time about 8.2 seconds, cooling time about 24 Seconds.
In the burn test, the result was judged as follows based on the degree of resin burnt adhering to the extraction screw after 10,000 shots. A JIS mold was used as the mold.
○: Discolored resin does not adhere to the screw.
Δ: A brown resin adheres to the screw.
X: Black resin adheres to the screw.

(11) JIS T3210: 2011 Sterilized syringe barrel 6 Chemical requirements The chemical requirements were tested by the following method with reference to this standard.
(A) Production of 100 mm × 120 mm × 1 mmt press sheet A spacer from which a press sheet of 100 mm × 120 mm × 1 mmt was obtained was placed between 150 mm × 150 mm × 3 mmt aluminum plates, and a specified amount of pellets was placed in the frame of the spacer. Thereafter, using a heating press heated to 230 ° C., the pellets were melted in a heating press without applying pressure for the first 7 minutes, and then a pressure of 100 kg / cm ² was applied for 3 minutes. Thereafter, the sample was quickly transferred to a cooling press at 30 ° C., and the sample was cooled by applying a pressure of 150 kg / cm ² for 2 minutes. Thereafter, the press sheet was peeled off from the aluminum plate and the spacer and taken out.
(B) Preparation of test piece for eluate test The press sheet prepared in (a) was equally divided into four by scissors, and four sheets of 60 mm × 50 mm × 2 mmt were collected. Thereafter, the surface of the sheet and the cut surface were washed with distilled water and dried at room temperature to obtain a test piece for the eluate test.
(C) Radiation sterilization of the test piece After irradiating the test piece with γ-ray 25KGY (average dose) in an air atmosphere at room temperature, the room temperature is 23 ° C. ± 0.5 ° C. and the relative humidity is 50 ± 5%. Adjusted for 2 weeks.
(D) Preparation of test liquid 250 ml of distilled water was put into a 500 ml borosilicate glass beaker washed with distilled water and dried at room temperature. Four test pieces (60 mm × 50 mm × 2 mmt) prepared for the eluate test prepared in (C) were put therein and immersed in water. At that time, no bubbles remained on the surface of the test piece. And after sealing the beaker with aluminum foil and keeping at 37 degreeC for 8 hours in a thermostat, the test piece was taken out and it was set as the test liquid.
(E) pH test and dissolution metal test The test was performed in accordance with the method described in JIS T3210: 2011. The blank test solution was distilled water, and the eluted metal was analyzed by the primitive spectrophotometry.
The standard of each test result is as follows.
(I) ΔpH: The difference in pH between the test solution and the blank test solution is 1 or less. (Ii) Elution metal: The total of lead, zinc, and iron is 5 mg / L or less, and the cadmium measurement value of the test solution is the blank test solution. When corrected with the measured cadmium value, the cadmium content of the test solution is 0.1 mg / L or less.
(12) Yakuhin No.494 Dialysis Type Artificial Kidney Approval Criteria IV Blood Circuit Quality and Testing Currently, “Yakuhoku No.494 Dialysis Type Artificial Kidney Approval Criteria” is “Abolition of Notification”. Since this test is a standard for confirming chemical safety in this application, the test was conducted.
The heavy metal test, lead test, and cadmium test were conducted using pellets in accordance with the operation method of the approval standard. The pellets used in the test were sterilized by irradiation with γ-ray 25KGY (average value) two weeks before the main test, and for two weeks in a thermostatic chamber at room temperature 23 ° C ± 0.5 ° C and relative humidity 50 ± 5%. The state is adjusted.
In addition, the eluate test shall be conducted in accordance with the quality and test method of the V dialyzer within the approval criteria. Referring to the eluate test described in the support and blood connection tube, 150 ml of water was added to 15 g of the pellet, and then an extraction test was performed at 70 ° C. for 1 hour. The test was conducted in compliance. The pellets used in the test were sterilized by irradiation with γ-ray 25KGY (average value) two weeks before the main test, and for two weeks in a thermostatic chamber at room temperature 23 ° C ± 0.5 ° C and relative humidity 50 ± 5%. The state is adjusted.
The standard of each test result is as follows.
4). Heavy metal test: 10 μg / g or less Lead test: 1 μg / g or less Cadmium test: 1 μg / g or less Elution test (i) Appearance: colorless and transparent, no foreign matter (ii) Abalone: Disappears within 3 minutes (iii) ΔpH: Difference from blank is 1.5 or less (iv) Zinc: Standard solution (0.5 μg / g ) And below (v) Potassium permanganate (KMnO ₄ ) reducing substance: difference in potassium permanganate consumption from the standard solution is 1.0 ml or less (vi) evaporation residue: 1.0 mg or less (vii) UV absorption spectrum (UV) 220-350 nm: 0.1 or less *) Currently, “Yakuhatsu No. 494 dialysis artificial kidney device approval criteria” is “Abolition of notification”, but this test is a chemical for this application. The test is conducted because it is a guideline for safety confirmation.

2. Materials Used (1) Medical Propylene-Ethylene Resin Composition Each medical propylene-ethylene resin composition obtained in the following Production Examples 1 to 7, that is, propylene polymer (PP-1 to PP-respectively, respectively) 7).
In addition, a propylene polymer (referred to as PP-8) produced using a metallocene catalyst and a commercially available propylene polymer (referred to as PP-9 to PP-11, respectively) were used as comparative examples.

<Production Example 1 (PP-1)>
(I) Production of Solid Catalyst Component (A) A 10 L autoclave equipped with a stirrer was sufficiently substituted with nitrogen, and 2 L of purified toluene was introduced. To this, 200 g of Mg (OEt) ₂ and 1 L of TiCl ₄ were added at room temperature. The temperature was raised to 90 ° C. and 50 ml of di-n-butyl phthalate was introduced. Thereafter, the temperature was raised to 110 ° C. to carry out a reaction for 3 hours. The reaction product was thoroughly washed with purified toluene. Subsequently, the refined toluene was introduce | transduced and the whole liquid quantity was adjusted to 2L. 1 L of TiCl ₄ was added at room temperature, the temperature was raised to 110 ° C., and the reaction was performed for 2 hours. The reaction product was thoroughly washed with purified toluene. Subsequently, the refined toluene was introduce | transduced and the whole liquid quantity was adjusted to 2L. 1 L of TiCl ₄ was added at room temperature, the temperature was raised to 110 ° C., and the reaction was performed for 2 hours. The reaction product was thoroughly washed with purified toluene. Furthermore, using purified n-heptane, toluene was replaced with n-heptane to obtain a solid component slurry. When a part of this slurry was sampled and analyzed, the Ti content of the solid component was 2.7% by weight.
Next, a 20 L autoclave equipped with a stirrer was sufficiently replaced with nitrogen, and 100 g of the solid component slurry was introduced as a solid component. Purified n-heptane was introduced to adjust the solid component concentration to 25 g / L. 50 ml of SiCl ₄ was added and a reaction was performed at 90 ° C. for 1 hr. The reaction product was thoroughly washed with purified n-heptane.
Thereafter, purified n-heptane was introduced to adjust the liquid level to 4 L. To this, 30 ml of dimethyldivinylsilane, 30 ml of (i-Pr) ₂ Si (OMe) ₂ and 80 g of Et ₃ Al in an n-heptane diluted solution were added as Et ₃ Al, and a reaction was carried out at 40 ° C. for 2 hours. The reaction product was thoroughly washed with purified n-heptane, and a portion of the resulting slurry was sampled, dried and analyzed. As a result, the solid component was 1.2% by weight of Ti, (i-Pr) ₂ Si (OMe) ₂ was contained in an amount of 8.8% by weight.
Furthermore, prepolymerization was performed by the following procedure using the solid component obtained above. Purified n-heptane was introduced into the slurry, and the solid component concentration was adjusted to 20 g / L. Next, after cooling to 10 ° C. The slurry, 10 g was added n- heptane dilution of _Et 3 Al as _Et 3 Al, were fed over 4hr of propylene 280 g. After the supply of propylene was completed, the reaction was further continued for 30 minutes. Next, the gas phase was sufficiently replaced with nitrogen, and the reaction product was thoroughly washed with purified n-heptane. The obtained slurry was extracted from the autoclave and vacuum dried to obtain a solid catalyst component (A). This solid catalyst component contained 2.5 g of polypropylene per gram of solid component. Further, the portion of the solid catalyst component (A) excluding polypropylene contained 1.0% by weight of Ti and 8.2% by weight of (i-Pr) ₂ Si (OMe) ₂ .

(Ii) Production of propylene polymer A propylene polymer was produced by two-stage polymerization using a polymerization reactor comprising two gas phase fluidized beds. The solid catalyst component (A) subjected to the above preactivation treatment was continuously supplied to the first reactor (inner volume 2.19 m3) at 0.26 g / hr, and Et ₃ Al as the organoaluminum compound at 5.2 g / hr. . While maintaining the conditions of a reaction temperature of 75 ° C., a reaction pressure of 3.0 MPa, a superficial velocity of 0.35 m / s, and a bed weight of 40 kg, hydrogen and ethylene in the polymerization vessel were respectively hydrogen / propylene = 0.057 molar ratio, ethylene PP component (A) was obtained by continuously supplying / propylene = 0.013 molar ratio.
The PP component (A) had an MFR of 88.0 g / 10 min and an ethylene content of 2.2% by weight.
Next, the obtained polymer was transferred to the second reactor (inner volume 2.19 m ³ ), and the conditions of reaction temperature 80 ° C., reaction pressure 2.5 MPa, superficial velocity 0.50 m / s, bed weight 60 kg were obtained. While maintaining, hydrogen and ethylene were continuously fed into the polymerization vessel at a hydrogen / propylene = 0.021 molar ratio and an ethylene / propylene = 0.051 molar ratio, respectively, to obtain a propylene polymer 1. In order to adjust the reaction amount of the propylene-ethylene copolymer, ethanol / Al = 0.62 molar ratio was supplied as a polymerization activity inhibitor.
The propylene-based polymer had an MFR of 44.0 g / 10 min and an ethylene content of 4.0% by weight. Here, when the index for the PP component (B) produced in the second stage was calculated, the production amount was 33% of the total weight, the MFR was 10.7 g / 10 min, and the ethylene content was 7.5. % By weight.

<Production Example 2 (PP-2)>
(I) Production of propylene polymer Hydrogen and ethylene in the first reactor are hydrogen / propylene = 0.056 molar ratio, ethylene / propylene = 0.013 molar ratio, and hydrogen and ethylene in the second reactor are hydrogen, respectively. /Propylene=0.032 molar ratio, ethylene / propylene = 0.071 molar ratio, and ethanol as a polymerization activity inhibitor to adjust the reaction amount of the second stage propylene-ethylene copolymer, ethanol / Al = 0. The production was performed under the same conditions as in Production Example 1 except that the production was carried out at a 72 molar ratio.
The PP component (A) had an MFR of 79.0 g / 10 min and an ethylene content of 2.2% by weight. The propylene-based polymer had an MFR of 46.0 g / 10 min and an ethylene content of 4.6% by weight. Here, when the index for the PP component (B) produced in the second stage was calculated, the production amount was 30% with respect to the total weight, the MFR was 13.0 g / 10 min, and the ethylene content was 10.0. % By weight.

<Production Example 3 (PP-3)>
(I) Production of propylene-based polymer Hydrogen and ethylene in the first reactor are hydrogen / propylene = 0.039 molar ratio, ethylene / propylene = 0.013 molar ratio, hydrogen and ethylene in the second reactor are hydrogen respectively Ethanol / Al = 0.56 molar ratio, ethylene / propylene = 0.052 molar ratio, and ethanol as a polymerization activity inhibitor to adjust the reaction amount of the second stage propylene-ethylene copolymer. The production was performed under the same conditions as in Production Example 1 except that the production was carried out at a 74 molar ratio.
The PP component (A) had an MFR of 45.0 g / 10 min and an ethylene content of 2.2% by weight. The propylene-based polymer had an MFR of 46.0 g / 10 min and an ethylene content of 3.8% by weight. Here, when the index for the PP component (B) produced in the second stage was calculated, the production amount was 32% with respect to the total weight, the MFR was 49.0 g / 10 min, and the ethylene content was 7.5. % By weight.

<Production Example 4 (PP-4)>
(I) Production of propylene polymer Hydrogen and ethylene in the first reactor are hydrogen / propylene = 0.030 molar ratio, ethylene / propylene = 0.103 molar ratio, and hydrogen and ethylene in the second reactor are hydrogen, respectively. /Propylene=0.030 molar ratio, ethylene / propylene = 0.103 molar ratio, and ethanol as a polymerization activity inhibitor to adjust the reaction amount of the second stage propylene-ethylene copolymer ethanol / Al = 0 The same conditions as in Production Example 1 were carried out except that the production was carried out at a 40 molar ratio.
The PP component (A) had an MFR of 30.0 g / 10 min and an ethylene content of 2.2% by weight. The propylene-based polymer had an MFR of 30.0 g / 10 min and an ethylene content of 2.2% by weight. Here, when the index for the PP component (B) produced in the second stage was calculated, the production amount was 30% with respect to the total weight, the MFR was 30.0 g / 10 min, and the ethylene content was 2.2. % By weight.

<Production Example 5 (PP-5)>
(I) Production of propylene polymer Hydrogen and ethylene in the first reactor are hydrogen / propylene = 0.036 molar ratio, ethylene / propylene = 0.012 molar ratio, and hydrogen and ethylene in the second reactor are hydrogen, respectively. /Ethanol=0.010 molar ratio, ethylene / propylene = 0.210 molar ratio, and ethanol as the polymerization activity inhibitor to adjust the reaction amount of the second stage propylene-ethylene copolymer ethanol / Al = 1 The same conditions as in Production Example 1 were performed except that the production was performed with a 30 molar ratio supply.
The PP component (A) had an MFR of 40.0 g / 10 min and an ethylene content of 2.1% by weight. The propylene-based polymer had an MFR of 13.0 g / 10 min and an ethylene content of 9.1% by weight. Here, when the index for the PP component (B) produced in the second stage was calculated, the production amount was 31% with respect to the total weight, the MFR was 1.0 g / 10 min, and the ethylene content was 25.0. % By weight.

<Production Example 6 (PP-6)>
(I) Production of Propylene Polymer Hydrogen and ethylene in the first reactor are hydrogen / propylene = 0.050 molar ratio, ethylene / propylene = 0.103 molar ratio, and hydrogen and ethylene in the second reactor are hydrogen, respectively. Ethylene / Al = 0 as a polymerization activity inhibitor in order to adjust the reaction amount of the propylene-ethylene copolymer in the second stage in the /propylene=0.027 molar ratio, ethylene / propylene = 0.070 molar ratio. The same conditions as in Production Example 1 were carried out except that the production was carried out at a .57 molar ratio supply.
The PP component (A) had an MFR of 82.0 g / 10 min and an ethylene content of 2.5% by weight. The propylene-based polymer had an MFR of 42.0 g / 10 min and an ethylene content of 4.7% by weight. Here, when the index for the PP component (B) produced in the second stage was calculated, the production amount was 26% of the total weight, the MFR was 6.0 g / 10 min, and the ethylene content was 11.0. % By weight.

<Production Example 7 (PP-7)>
(I) Production of propylene-based polymer This will be described with reference to the attached flow sheet shown in FIG. A gas phase polymerization reactor using two polymerization tanks was used. The two polymerization vessels 17 and 26 are continuous horizontal gas phase polymerization vessels (length / diameter = 5.2) equipped with a stirrer having an inner diameter D: 2100 mm, a length L: 11000 mm, and an internal volume: 40 m ^3. .
After replacing the inside of the polymerization vessel 17, a polypropylene powder from which polymer particles having a particle size of 500 μm or less were removed was charged. As a solid catalyst component (A) of Production Example 1, 120 g / Hr, and a 15 wt% hexane solution of triethylaluminum It supplied continuously so that molar ratio might be set to 350 with respect to 1 mol of Ti atoms in A. Further, hydrogen was adjusted so that the ratio of the hydrogen concentration in the polymerization vessel 17 to the propylene concentration was 0.095, ethylene was adjusted so that the ratio of the ethylene concentration to the propylene concentration was 0.020, and the pressure in the polymerization vessel 17 was 2. Propylene monomers were respectively supplied into the polymerization vessel 17 so as to maintain 2.10 MPa and a temperature of 61 ° C. The reaction heat was removed by the vaporization heat of the raw material propylene supplied from the raw material mixed gas supply pipe 19. The unreacted gas discharged from the polymerization vessel 17 was extracted from the reactor system through the unreacted gas extraction piping 20, cooled and condensed, and refluxed to the polymerization reactor 17 through the recycle gas piping 18.
The propylene-ethylene copolymer (A) produced in the polymerizer 17 is continuously withdrawn from the polymerizer 17 through the polymer withdrawal pipe 21 so that the retained level of the polymer is 45% by volume of the reaction volume. , And supplied to the polymerization vessel 26 in the second polymerization step.
In the polymerization vessel 26, the polymer from the first polymerization step, and hydrogen so that the ratio of the hydrogen concentration in the polymerization vessel 26 to the propylene concentration is 0.021, and the ratio of the ethylene concentration to the propylene concentration is 0.00. Ethylene was supplied to the polymerization vessel 17 so that the pressure in the polymerization vessel 17 was 2.05 MPa and the temperature was maintained at 70 ° C. A polymerization activity inhibitor for adjusting the polymerization amount of the propylene-ethylene copolymer (B) was supplied from the pipe 27. The reaction heat was removed by the vaporization heat of the raw material liquefied propylene supplied from the raw material mixed gas pipe 22. The unreacted gas discharged from the polymerization vessel 26 was extracted out of the reactor system through the unreacted gas extraction piping 24, cooled and condensed, and refluxed to the polymerization reactor 26 through the recycle gas piping 23. The propylene polymer produced in the second polymerization step was continuously extracted from the polymerizer 26 through the polymer extraction pipe 25 so that the retained level of the polymer was 50% by volume of the reaction volume. The extracted powder was subjected to gas separation by a gas recovery machine 28, and the powder part was extracted to a recovery system and granulated by a granulation system.
The production rate of the propylene-based polymer was 9.6 T / Hr, the average residence time in the polymerization vessel 17 was 1.9 Hr, and the average residence time in the polymerization vessel 26 was 1.3 Hr. When the catalyst efficiency was determined by dividing the production rate by the supply rate of the solid catalyst component A, it was 88900 g-PP / g-catalyst.
Moreover, when the obtained propylene-type polymer was analyzed, MFR was 29.1g / 10min and ethylene content was 5.0 wt%. The PP component (A) had an MFR of 71.9 g / 10 min and an ethylene content of 2.5 wt%. The PP component (B) had MFR = 8.0 g / 10 min and the ethylene content was 11.3 wt%. Here, the MFR of the PP component (B) was calculated from the MFR of the PP component (A), the MFR of the propylene polymer, and the weight ratio of the PP components (A) and (B) according to a logarithmic additive equation. The ethylene content was calculated from the ethylene content of the PP component (A), the ethylene content of the propylene polymer, and the weight ratio of the PP components (A) and (B). Here, the weight ratio of PP components (A) and (B) is calculated from the amount of liquefied propylene supplied to the polymerization tank, and the production amount of PP component (B) is 28% of the total weight. %Met.

<Production Example 8 (PP-8)>
Using the solid catalyst component (A) of Production Example 1, the gas concentration in the first polymerization step was such that the ratio of hydrogen concentration to propylene concentration was 0.094, and the ratio of ethylene concentration to propylene concentration was 0.00. The gas concentration in the second polymerization step is adjusted to 022, the hydrogen is adjusted so that the ratio of the hydrogen concentration to the propylene concentration is 0.014, and the ratio of the ethylene concentration to the propylene concentration is 0.061. Polymerization was carried out in the same manner as in Production Example 7 except that ethylene was controlled.
The production rate of the propylene-based polymer was 9.5 T / Hr, the average residence time in the polymerization vessel 1 was 1.9 Hr, and the average residence time in the polymerization vessel 10 was 1.3 Hr. When the catalyst efficiency was determined by dividing the production rate by the supply rate of the solid catalyst component A, it was 92,500 g-PP / g-catalyst.
Moreover, when the obtained propylene polymer was analyzed, MFR was 21.1 g / 10min and ethylene content was 4.8 wt%. The PP component (A) had an MFR of 59.3 g / 10 min and an ethylene content of 2.6 wt%. For PP component (B), MFR, ethylene content and ratio were calculated by the method described in Production Example 7, MFR = 4.8 g / 10 min, ethylene content was 10.2 wt%, and ratio was 29 wt%. It was.

<Production Example 9 (PP-9)>
Using the solid catalyst component (A) of Production Example 1, the gas concentration in the first polymerization step was such that the ratio of hydrogen concentration to propylene concentration was 0.096, and the ratio of ethylene concentration to propylene concentration was 0.00. 021 so that the gas concentration in the second polymerization step is 021, hydrogen is such that the ratio of hydrogen concentration to propylene concentration is 0.015, and the ratio of ethylene concentration to propylene concentration is 0.077. Polymerization was carried out in the same manner as in Production Example 7 except that ethylene was controlled.
The production rate of the propylene polymer was 9.2 T / Hr, the average residence time in the polymerization vessel 1 was 1.9 Hr, and the average residence time in the polymerization vessel 10 was 1.3 Hr. When the catalyst efficiency was determined by dividing the production rate by the supply rate of the solid catalyst component A, it was 85,500 g-PP / g-catalyst.
Moreover, when the obtained propylene polymer was analyzed, MFR was 19.9 g / 10min and ethylene content was 5.2 wt%. The PP component (A) had an MFR of 63.1 g / 10 min and an ethylene content of 2.7 wt%. For PP component (B), MFR, ethylene content and ratio were calculated by the method described in Production Example 7, MFR = 2.6 g / 10 min, ethylene content was 12.0 wt%, and ratio was 27 wt%. It was.

(PP-10) Propylene Polymer A propylene polymer was produced using a metallocene catalyst with reference to Production Example (1) of Japanese Patent Application No. 2013-123079. The PP component (A) had an MFR of 100.0 g / 10 min and an ethylene content of 1.0% by weight. The propylene-based polymer had an MFR of 50.0 g / 10 min and an ethylene content of 4.0% by weight. Here, when the index for the PP component (B) produced in the second stage was calculated, the production amount was 30% with respect to the total weight, the MFR was 10.0 g / 10 min, and the ethylene content was 11.0. % By weight.

(PP-11) Propylene-based polymer Propylene-ethylene copolymer: MFR (JIS K7210, 230 ° C., 2.16 kg load) 30 g / 10 min, ethylene content 2.5% by weight
“NOVATEC MG03BQ” (trade name / Ziegler-Natta catalyst, manufactured by Nippon Polypro Co., Ltd.).
(PP-12) Propylene polymer Propylene-ethylene copolymer: MFR (JIS K7210, 230 ° C., 2.16 kg load) 30 g / 10 min, ethylene content 0.9% by weight
“WINTEC WMG03P” (trade name / metallocene catalyst, manufactured by Nippon Polypro Co., Ltd.).
(PP-13) Propylene polymer Propylene-ethylene copolymer: MFR (JIS K7210, 230 ° C., 2.16 kg load) 7.0 g / 10 min, ethylene content 11% by weight
“Vistamaxx3000” (trade name / metallocene catalyst, manufactured by Exxon Mobil)

(2) Nucleating Agent Nucleating Agent (B-1): Phosphoric acid-2,2′-methylenebis (4,6-di-tert-butylphenyl) aluminum salt “ADK STAB NA-21” (manufactured by ADEKA Corporation) ,Product name)
Nucleator (B-2): 1,2,3-trideoxy-4,6: 5,7-bis-O-[(4-propylphenyl) methylene] -nonitol “Mirad NX8000J” (Milken & Company (Product name)
Nucleator (B-3): 1,3,5-tris- [2,2-dimethylpropionylamino) -benzene “XT-386” (trade name, manufactured by BASF)
(3) Antioxidant Phosphorus antioxidant (C-1): Tris (2,4-di-t-butylphenyl) phosphite “Irgafos168” (trade name, manufactured by BASF)
Hindered amine stabilizer (D-1): Dimethyl-2- (4-hydroxy-2,2,6,6-tetramethyl-1-piperidyl) ethanol condensate “TINUVIN622” (trade name, manufactured by BASF)
(4) Neutralizing agent Neutralizing agent (E-1): Calcium stearate (manufactured by NOF Corporation)
(5) Lubricant Lubricant (F-1): Butyl stearate (manufactured by NOF Corporation)
(6) Other additives Organic peroxide (G-1): 2,5-dimethyl-2,5-di- (t-butyl-peroxy) hexane “Perhexa 25B” (manufactured by NOF Corporation, product Name)
Polyethylene (H-1): Density (JIS K7112) 0.898 g / cm ³ , MFR (JIS K7210, 190 ° C., 2.16 kg load) 16.5 g / 10 min “Kernel KF560T” (manufactured by Nippon Polyethylene Co., Ltd.) Product name)

(Examples 1-22, Comparative Examples 1-8)
Prepare propylene polymer and additives (nucleating agent, antioxidant, neutralizing agent, lubricant, other additives) at the blending ratios (parts by weight) shown in Tables 1-2, and dry for 3 minutes with a super mixer. After blending, using a 35 mmφ twin-screw extruder, the temperature was 200 ° C., the screw rotation speed was 200 rpm, the extrusion rate was about 15 kg / hr, and the sample supply hopper was melt-kneaded under nitrogen atmosphere to form resin pellets. Thereafter, an injection molding machine having a clamping pressure of 100 tons was used, and injection molding was performed at a molding temperature of 200 ° C. and a mold temperature of 40 ° C. to obtain test pieces. Tables 1 and 2 show the compositions, physical properties, evaluation results, and the like of the propylene polymers (PP-1 to PP-13).

上記の結果から、今回発明した樹脂組成物は、成形加工性が良好で、剛性と耐衝撃性のバランス、低温耐衝撃性、低異物出現性及び透明性に優れ、特に放射線滅菌後の耐衝撃性、低溶出性に優れ、かつ、ＪＩＳ Ｔ３２１０：２０１１ 滅菌済み注射筒に記載の６化学的要求事項、又は、薬発第４９４号 透析型人工腎臓装置承認基準 ＩＶ血液回路の品質及び試験法に記載の重金属試験、鉛試験、カドミウム試験、溶出物試験を放射線滅菌後に満足するという優れた樹脂組成物であることが分かる。また、造核剤を含有する実施例１１〜２２は、実施例１〜１０よりもさらに透明性及び剛性が改良されることが分かる。
これに対して、比較例１ではプロピレン−エチレン共重合体（Ｂ）相当品のエチレン含量が低い為、衝撃値が悪化していることが分かる。比較例２では、プロピレン−エチレン共重合体（Ｂ）相当品のエチレン含量が高い為、透明性が悪化していることが分かる。比較例３は、単段重合のプロピレン−エチレン共重合体であり、特に放射線滅菌後の耐衝撃性が著しく乏しいことが分かる。比較例４は、改質材としてポリエチレンを配合しているが、樹脂焼けが酷く、また、放射線滅菌後の耐衝撃性に乏しいことが分かる。比較例５〜８は、比較例１〜４に造核剤を配合したものであるが、比較例５、７では、造核剤を配合すると特に放射線滅菌後の低温面衝撃値が悪化しており、測定下限値になっていることが分かる。また、比較例６は、造核剤を配合しても透明性を改良することが出来ていないことが分かる。比較例８では、造核剤を配合しても樹脂焼けが酷く、また、放射線滅菌後の耐衝撃性に乏しいことが分かる。

From the above results, the resin composition invented this time has good moldability, excellent balance between rigidity and impact resistance, low temperature impact resistance, low foreign matter appearance and transparency, especially impact resistance after radiation sterilization. 6 chemical requirements described in the JIS T3210: 2011 sterilized syringe, or Yakusei No. 494 dialysis-type artificial kidney device approval criteria for IV blood circuit quality and test methods It can be seen that the resin composition is excellent in satisfying the described heavy metal test, lead test, cadmium test and elution test after radiation sterilization. Moreover, it turns out that Example 11-22 containing a nucleating agent improves transparency and rigidity further than Examples 1-10.
On the other hand, in Comparative Example 1, it can be seen that since the ethylene content of the propylene-ethylene copolymer (B) equivalent product is low, the impact value is deteriorated. In Comparative Example 2, it can be seen that since the ethylene content of the propylene-ethylene copolymer (B) equivalent is high, the transparency is deteriorated. Comparative Example 3 is a single-stage polymerization propylene-ethylene copolymer, and it can be seen that the impact resistance after radiation sterilization is particularly poor. Although the comparative example 4 mix | blends polyethylene as a modifier, it turns out that resin burning is severe and the impact resistance after radiation sterilization is scarce. Comparative Examples 5 to 8 are those in which a nucleating agent was blended with Comparative Examples 1 to 4, but in Comparative Examples 5 and 7, when the nucleating agent was blended, the low-temperature surface impact value after radiation sterilization deteriorated. Thus, it can be seen that the lower limit of measurement is reached. Moreover, it turns out that the comparative example 6 cannot improve transparency, even if it mix | blends a nucleating agent. In Comparative Example 8, it can be seen that even if a nucleating agent is blended, the resin is burned severely and the impact resistance after radiation sterilization is poor.

  The present invention has good moldability during injection molding, excellent balance between rigidity and impact resistance, excellent low-temperature impact resistance, low foreign matter appearance and transparency, especially impact resistance after radiation sterilization, low elution 6 chemical requirements described in JIS T3210: 2011 sterilized syringe, or Yakusei No. 494 dialysis artificial kidney device approval criteria IV quality of blood circuit and heavy metal test described in test method , Lead propylene test, cadmium test, eluate test medical propylene-ethylene resin composition satisfying after radiation sterilization, and injection molded products obtained by using it, especially injection molded products for medical use, especially syringe parts and artificial Since a dialysis member can be provided, it is very useful in the industry.

1 Arm of person undergoing dialysis 2 Tube 3 Blood pump 4 Air trap 5 Dializer 6 Console 7 Blood inlet (with cap)
8 Blood outlet (with cap)
9 Dialysate inlet (with cap)
10 Dialysate outlet (with cap)
11 Hollow Fiber 12 Dializer Housing 13 Dializer Header 14 Outer Cylinder 15 Pusher 16 Gasket 17 Polymerizer (First Polymerization Step)
18 Recycled gas pipe 19 Raw material mixed gas pipe 20 Unreacted gas outlet pipe 21 Polymer outlet pipe 22 Raw material mixed gas pipe 23 Recycled gas pipe 24 Unreacted gas outlet pipe 25 Polymer outlet pipe 26 Polymerizer (second polymerization step)
27 Pipeline for adding polymerization activity inhibitor 28 Gas recovery machine 29 Bag filter

Claims (7)

  Propylene having an ethylene content of 0.1 to 3% by weight and a melt flow rate (hereinafter sometimes abbreviated as MFR) according to JIS K7210 (230 ° C., 2.16 kg load) of 10 to 300 g / 10 min. A medical propylene-ethylene resin composition comprising an ethylene copolymer (A), a propylene-ethylene copolymer (B) having an ethylene content of 5 to 20% by weight and an MFR of 1 to 50 g / 10 min. -The weight ratio of ethylene copolymer (A) and propylene-ethylene copolymer (B) is 90: 10-60: 40, and the ethylene content of the medical propylene-ethylene resin composition is 2-8 wt% A medical propylene-ethylene resin composition.   The MFR ratio (A / B) of the propylene-ethylene copolymer (A) and the propylene-ethylene copolymer (B) is 1 to 30, and the MFR of the medical propylene-ethylene resin composition is 20 to 100 g / The medical propylene-ethylene resin composition according to claim 1, wherein the composition is 10 min.   The medical propylene-ethylene-type resin composition in which the medical propylene-ethylene-type resin composition of Claim 1 or 2 contains a nucleating agent.   An injection molded product for medical use obtained by using the medical propylene-ethylene resin composition according to any one of claims 1 to 3.   An injection-molded product for medical use, wherein the injection-molded product for medical use according to claim 4 is sterilized by γ rays or electron beams.   An injection molded product for medical use, wherein the injection molded product for medical use according to claim 4 or 5 is a syringe member.   An injection molded product for medical use, wherein the injection molded product for medical use according to claim 4 or 5 is an artificial dialysis member.

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