Patent Application
20220265869
The application relates to the field of biomedicine, in particular to a composition for magnetic ultrasound contrast agent, a magnetic ultrasound contrast agent including the composition for magnetic ultrasound contrast agent, a preparation method of a magnetic microbubble ultrasound contrast agent, and a magnetic microbubble ultrasound contrast agent prepared by the preparation method.
At present, efficient drugs for treating various cancers are usually insoluble in water, having great side effects, and prone to drug resistance. Study shows that target delivery may solve the above problem. In recent years, many researches have been made by scientists from all over the world in the field of nano-controlled release drug delivery system, such as a tumor-sensitive pH controlled release system, a drug-loaded nanoparticle, and the like. Although these nano-drug delivery systems may realize the responsive release of a drug at the tumor site, there are also some problems: such as insufficient of local release amount and low response sensitivity of tumor; especially in a high flow rate area, it is difficult to achieve drug-enriched delivery and visual controlled release.
In recent years, Ultrasonic Targeted Microbubble Destruction (UTMD) technology has been widely studied. Because the inertial cavitation occurs upon rupture of a microbubble under a high-energy ultrasonic wave, the microbubble loaded drug blasts at the target area and releases the drug locally, thereby exhibiting the therapeutic effect of targeted drug delivery. Based on the UTMD technology, the microbubble ultrasound contrast agent loaded with a magnetic particle has been studied in the prior art in order to further achieve the drug-enriched delivery and the visual controlled release. However, the stability (cavitation threshold) of the magnetic microbubble ultrasound contrast agent currently used in the UTMD technology is not ideal, and it is hard to meet requirements for in vivo cyclic targeted delivery.
Therefore, it is of great significance to study a magnetic microbubble ultrasound contrast agent with ideal stability for treating diseases, especially for treating cancers.
The object of the present application is to overcome the problem that the existing magnetic microbubble ultrasound contrast agent has poor stability, and to provide a composition for magnetic ultrasound contrast agent, a magnetic ultrasound contrast agent including the composition for magnetic ultrasound contrast agent, a preparation method of a magnetic microbubble ultrasound contrast agent, and a magnetic microbubble ultrasound contrast agent prepared by the preparation method.
The magnetic microbubble ultrasound contrast agent obtained from the composition for magnetic ultrasound contrast agent has higher stability and may meet requirements for in vivo cyclic targeted delivery, thereby achieving the local high-concentration targeted delivery of a medication.
The inventors of the present application have found that by introducing the surfactant with specific component and ratio into a magnetic ultrasound contrast agent, the cavitation threshold of a magnetic microbubble ultrasound contrast agent may be improved effectively. The inventors of the present application also found that, in a particularly preferred embodiment, by selecting poloxamer and sodium citrate and combining poloxamer and sodium citrate specially, the surface tension of a magnetic microbubble may be changed and the holes on the surface of the microbubble may be filled, so that the cavitation threshold and stability of the magnetic microbubble ultrasound contrast agent are improved further.
In order to achieve the above object, a first aspect of the present application provides a composition for magnetic ultrasound contrast agent, which includes a lipid, a surfactant and a magnetic nanoparticle, wherein the surfactant consists of a surfactant A and a surfactant B, the surfactant A is in a free state, and the surfactant B is in a bonding state and is modified on the surface of the magnetic nanoparticle; the surfactant A is a nonionic surfactant whose HBL value is greater than 8, and the surfactant B is a citric acid-based compound; and relative to 1 mol of the lipid, the content of the surfactant A is 0.1 mol to 1 mol (e.g., 0.1, 0.2, 0.3, 0.4, 0.5, 0.6, 0.7, 0.8, 0.9 or 1), the content of the surfactant B is 0.1 mol to 1 mol (e.g., 0.1, 0.2, 0.3, 0.4, 0.5, 0.6, 0.7, 0.8, 0.9 or 1), and the content of the magnetic nanoparticle is 0.05 mol to 0.5 mol (e.g., 0.05, 0.06, 0.07, 0.08, 0.09, 0.1, 0.2, 0.3, 0.4 or 0.5).
Preferably, the surfactant A is a nonionic surfactant with a HBL value is greater than 15; more preferably, a nonionic surfactant with a HBL value is 20 to 35 (e.g., 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34 or 35).
In the present application, the HLB value is determined by inverse gas chromatography, referring to Jiang Chaoxue, et al., Determination of Hydrophilic-lipophilic Balance of Nonionic Emulsifier by Inverse Gas Chromatography, China Synthetic Rubber Industry, 1991, 14(6): 399-401.
According to a specific embodiment, the surfactant A is any one or more selected from the group consisting of: poloxamer, poly(isobutene-maleic anhydride), and poly(maleic anhydride-alt-1-octadecene); more preferably, the surfactant A is poloxamer.
Preferably, the surfactant B is citrate and/or citrate ester.
According to a specific embodiment of the present application, the surfactant A is poloxamer, and the surfactant B is citrate.
The ratio of the above lipid, surfactant A, surfactant B and magnetic nanoparticle according to the present application may achieve better effects. In order to further improve stability, preferably, relative to 1 mol of the lipid, the content of the surfactant A is 0.2 mol to 0.6 mol, the content of the surfactant B is 0.2 mol to 0.5 mol, and the content of the magnetic nanoparticle is 0.1 mol to 0.3 mol; more preferably, relative to 1 mol of the lipid, the content of the surfactant A is 0.3 mol to 0.5 mol, the content of the surfactant B is 0.3 mol to 0.4 mol, and the content of the magnetic nanoparticle is 0.18 mol to 0.25 mol.
Preferably, the molar ratio of the magnetic particle to the surfactant B is 1:0.6 to 1:2.5, more preferably 1:1.2 to 1:1.8. The 1:1.2 to 1:1.8 is only a specific embodiment, and the upper limit may reach the saturation capacity of the surfactant B in the magnetic nanoparticle. Similarly, the upper limit 1:2.5 in the molar ratio 1:0.6 to 1:2.5 is only an illustration. In different situations, all values may be taken in the range of 1:0.6 to 1:“the saturation capacity” according to the actual situation when the saturation capacity is lower than 2.5 or higher than 2.5.
Understandably, although the magnetic microbubble ultrasound contrast agent of the present application may be used as a drug delivery agent, the composition for ultrasound contrast agent of the present application may not include the a drug based on the needs of production and transportation according to a specific embodiment.
According to another specific embodiment of the present application, the composition for ultrasound contrast agent further includes a drug, relative to 100 parts by weight of a sum of the lipid, the surfactant, and the magnetic nanoparticle, the content of the drug is 1 to 20 parts by weight, more preferably 2 to 8 parts by weight.
In the present application, the lipid may be a lipid commonly used in the art for the ultrasound contrast agent. Preferably, the lipid is phospholipids. In order to have a better synergistic effect with other components in the composition for the ultrasound contrast agent of the present application, preferably, the lipid is any one or more selected from the group consisting of: polysorbate-based compounds and sorbitan monostearate.
In the present application, preferably the lipid is a combination of two or more substances. According to a preferred embodiment, the lipid consists of sorbitan monostearate and polysorbate 80 in a molar ratio of 1:0.5 to 1:2 (more preferably 1:0.8 to 1:1.2).
In the present application, the magnetic nanoparticle may be a magnetic nanoparticle commonly used in the art for the magnetic ultrasound contrast agent. Preferably, the magnetic nanoparticle is a superparamagnetic Fe3O4 nanoparticle.
In the present application, preferably, the particle size of the magnetic nanoparticle is 3 nm to 20 nm, more preferably 7 nm to 10 nm.
In the present application, the term “particle size” refers to the geometric spherical diameter of a single particle rather than an average value; when it is a range value, it means that the particle sizes of the particles in the same material fall within the range; meanwhile, the present application allows a certain amount of error, i.e., when the particle sizes of less than 5% of the total number are not within the required range, it is also considered to meet the requirements. The particle size of the magnetic nanoparticle according to the present application is measured by transmission electron microscope, and the particle size of the microbubble is measured by optical microscope.
In the present application, the drug may be various drugs as required for actual treatment. For example, the drug includes, but is not limited to: paclitaxel, adriamycin, bleomycin, and the like. All drugs used in ultrasound contrast agents in the art may be used in the present application, and those skilled in the art may select one as required.
The composition for magnetic ultrasound contrast agent according to the present application may also include other conventional adjuvants in the art; as long as the performance of other components is not adversely affected, those skilled in the art may choose these other adjuvants and the contents of them may refer to the conventional contents in the art.
The second aspect of the present application provides a magnetic ultrasound contrast agent, which including the composition for magnetic ultrasound contrast agent according to the first aspect of the present application.
According to a specific embodiment of the present application, the ultrasound contrast agent includes a large number of gas-filled microbubbles.
In this specific embodiment, preferably, the particle size of the gas-filled microbubbles is 0.3 μm to 5 μm, more preferably 0.8 μm to 3 μm.
Preferably, the gas in the gas-filled microbubbles is an inert gas and may be commonly used in the art for microbubble ultrasound contrast agent, such as, any one or more selected from the group consisting of: perfluoropropane, perfluorobutane and sulfur hexafluoride. The shell of the gas-filled microbubbles includes the composition for ultrasound contrast agent according to the first aspect of the present application.
According to another specific embodiment of the present application, the ultrasound contrast agent may not contain gas-filled microbubbles. Generally in the art, the ultrasound contrast agent in this state is called film-forming agent for ultrasound contrast agent. The ultrasound contrast agent that includes a large number of gas-filled microbubbles and may be used in clinical application is obtained by the film-forming agent for ultrasound contrast agent through putting a degree of mechanical force (such as ultrasonic cavitation).
In the present application, the term “ultrasound contrast agent” also includes film-forming agent for ultrasound contrast agent.
According to a specific embodiment of the present application, the ultrasound contrast agent consists of a continuous phase and a dispersed phase. The continuous phase may be a conventional continuous phase used to prepare an ultrasound contrast agent in the field, such as phosphate (PBS) buffer solution. The dispersed phase includes the composition for magnetic ultrasound contrast agent according to the first aspect of the present application and may be the gas-filled microbubbles (i.e. forming an ultrasound contrast agent) or a lipid-droplet (i.e. forming a film-forming solution for ultrasound contrast agent).
A third aspect of the present application provides a method for preparing a magnetic microbubble ultrasound contrast agent, wherein the raw materials include the composition for magnetic ultrasound contrast agent according to the first aspect of the present application, and the method includes the following steps:
(1) making a first contact between the lipid and the surfactant A;
(2) mixing the drug with the resulting material obtained by step (1), pumping gases into the mixed resulting material, and processing ultrasonic cavitation to form a first microbubble suspension;
(3) processing a treatment for loading a positive charge on the first microbubble suspension to obtain a second microbubble suspension with a positive charge on the surface;
(4) making a second contact between the magnetic nanoparticle modified with the surfactant B on the surface and the obtained second microbubble suspension with a positive charge on the surface.
In the method of the third aspect of the present application, the specific selection and ratio of the raw materials used are all processed according to the definition in the composition for magnetic ultrasound contrast agent described in the first aspect of the present application, so that won't be covered again here.
In step (1), the first contact makes the mixing of the lipid and the surfactant A fuller, so that the core-shell structure of the microbubble in the first microbubble suspension obtained by step (2) is more stable; preferably, the first contact conditions include: a temperature of 110° C. to 130° C., and a time of 8 min to 16 min.
In step (2), preferably, the mixing is processed at a temperature of 30° C. to 50° C. For example, cooling the resulting material obtained by step (1) until the temperature fall within the range, and then processing the mixing with the drug.
In step (2), preferably, the ultrasonic cavitation conditions include: a ultrasonic power of 8 kW to 12 kW, and a time of 1 min to 8 min; more preferably, the ultrasonic cavitation conditions include: a ultrasonic power of 9 kW to 11 kW, and a time of 2 min to 4 min.
In step (3), preferably, before the treatment of loading a positive charge, leaving the first microbubble suspension to stand and centrifuge for separation to remove the microbubble with larger particle size in the upper layer, preferably, the particle size of the microbubble in the first microbubble suspension after centrifugalization is 0.3 μm to 5 μm, more preferably 0.8 μm to 3 μm.
In step (3), preferably, the process of the treatment for loading a positive charge includes: contacting the first microbubble suspension with a aqueous solution of cationic reagent.
Preferably, the volume ratio of the aqueous solution of cationic reagent and the first microbubble suspension is 0.8:1 to 1.2:1. Preferably, the concentration of the cation in the aqueous solution of the cationic reagent is 0.5 mg/L to 2 mg/L (e.g., 0.5, 0.6, 0.7, 0.8, 0.9, 1, 1.1, 1.2, 1.3, 1.4, 1.5, 1.6, 1.7, 1.8, 1.9 or 2).
The contacting mode between the first microbubble suspension and the aqueous solution of cationic reagent is not particularly limited, preferably, the contacting mode is ultrasonic oscillation, the ultrasonic power is 170 W to 420 W, and the time is 20 min to 40 min. The positive charge carried by the cationic reagent is adsorbed on the surface of the microbubble in the first microbubble suspension by the contacting.
In step (3), preferably, the method further includes: leaving the resulting material which contacted with the cationic reagent to stand for stratification, taking upper layer materials, and washing the upper layer materials with buffer solution, to obtained the second microbubble suspension with a positive charge on the surface.
The upper layer materials obtained after standing and stratification is an oily solution including the first microbubble suspension, and the lower layer material is an aqueous solution. Taking the upper layer solution and then washing the upper layer solution with buffer solution for 2 to 5 times to remove excess cationic reagent. The buffer solution may be commonly used in the art for acid-base buffer solution, such as phosphate (PBS) buffer solution.
In step (4), preferably, the second contact conditions include: processing the material with ultrasonic oscillation, a ultrasonic power of 170 W to 420 W, and a time of 15 min to 50 min, more preferably, the ultrasonic power of 250 W to 350 W, and a time for 20 min to 40 min.
In the present application, preferably, the magnetic nanoparticle is a superparamagnetic nanoparticle.
In the present application, the magnetic nanoparticle modified with the surfactant B on the surface may be prepared according to a conventional method in the art. Preferably, the preparation method of the magnetic nanoparticle modified with the surfactant B on the surface includes the following steps: ultrasonically oscillating the mixture of the magnetic nanoparticle and the aqueous solution of the surfactant B with a ultrasonic power of 170 W to 420 W and a time of 8 min to 30 min, and then separating a solid magnetic nanoparticle; this process is repeated for 2 to 5 times; thereby obtaining the magnetic nanoparticle modified with the surfactant B on the surface.
The amount of the magnetic nanoparticle and the surfactant B magnetic nanoparticle is such that the weight ratio satisfies the definition in the composition for magnetic ultrasound contrast agent in the first aspect of the present application.
In the present application, preferably, the magnetic nanoparticle is a superparamagnetic nanoparticle, which may be obtained by commerce or preparation. When the magnetic nanoparticle is obtained by preparation, the preparation method preferably includes: processing a thermal decomposition reaction with the mixture of ferric precursor and solvent under the water-free and oxygen-free conditions to obtain a superparamagnetic nanoparticle; and then purifying the superparamagnetic nanoparticle by magnetism.
More preferably, the preparation method preferably includes: processing a thermal decomposition reaction with the mixture of ferric acetylacetonate and triethylene glycol in a molar ratio of 2.5:1 to 3.5:1 under the water-free and oxygen-free conditions, wherein the temperature of the thermal decomposition reaction is 270° C. to 290° C. and the time is 0.8 h to 1.2 h, to obtain a superparamagnetic nanoparticle, and then purifying the superparamagnetic nanoparticle by magnetism.
Through the above technical solutions, compared with the prior art the present application has at least the following advantages: the microbubble ultrasound contrast agent obtained by the composition for ultrasound contrast agent of the present application may achieve the enrichment and response release of a drug at a specific site by controlling the external magnetic field and ensure sufficient stability and maintain stability in a local high flow rate state, as well as the performance of the ultrasound contrast agent in the present application is controllable. Therefore, the present application enables the targeted drug delivery stable and reliable in a local high flow rate state.
The endpoints of a range and any values disclosed herein are not limited to the precise ranges or values, which are to be understood to encompass values proximate to those ranges or values. For value ranges, the endpoints of each range, an endpoint of each range and an individual point value, and the individual point values may be combined with each other to yield one or more new value ranges which should be considered as particularly disclosed herein.
(a) of
(b) of
The present application will be described in detail below by the Examples. The described Examples of the present application are only a part of the examples of the present application, but not all of the examples. Based on the Examples of the present application, all other examples obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present application.
Unless otherwise specified, the materials used in the following Examples are all commercially available analytical grades.
The following preparation examples are used to prepare the magnetic nanoparticle modified with the surfactant B on the surface using in the Examples. The following preparation example is only a specific embodiment of the present application and not a limitation of the present application.
(a) Triethylene glycol and ferric acetylacetonate are mixed in a molar ratio of 3:1 and heated at high temperature of 280° C. for 1 h, thereby obtaining a superparamagnetic Fe3O4 nanoparticle. And then the particle size is observed as 7 nm to 10 nm by a transmission electron microscope.
(b) The superparamagnetic nanoparticle is purified by magnetism.
(c) The superparamagnetic nanoparticle obtained by step (b) and the aqueous solution (sodium citric acid solution) of surfactant B are mixed in a molar ratio of 1:1.5, and then oscillated under the ultrasonic power of 300 kW. This process is repeated for 3 times.
A superparamagnetic Fe3O4 nanoparticle modified with the sodium citric acid on the surface is obtained.
Referring to the method of Preparation Example 1, the difference is that the amount of the sodium citric acid is changed so that the molar ratio of the superparamagnetic nanoparticle to the surfactant B is 1:1.8.
Referring to the method of Preparation Example 1, the difference is that the amount of the sodium citric acid is changed so that the molar ratio of the superparamagnetic nanoparticle to the surfactant B is 1:1.2.
Referring to the method of Preparation Example 1, the difference is that the amount of the sodium citric acid is changed so that the molar ratio of the superparamagnetic nanoparticle to the surfactant B is 1:0.5.
Referring to the method of Preparation Example 1, the difference is that the sodium citric acid is replaced with the same molar weight of poloxamer, thereby obtaining a superparamagnetic Fe3O4 nanoparticle modified with the poloxamer on the surface.
Processed by the Following Steps:
(1) Sorbitan monostearate (lipid), polysorbate 80 (lipid) and poloxamer F68 (Germany BASF, P21489-25G, surfactant A, HLB value=29) are mixed well in a molar ratio of 1:1:1.5, 10 mL of the obtained mixture is taken and put into a 120° C. sterilization pot under the high-temperature and high-pressure conditions for 12 min, and then continuously stirred and cooled until the temperature is 40° C.;
(2) The resulting material obtained by step (1) and paclitaxel (chemotherapy drug) are mixed in a weight ratio of 100:5, applying ultrasonic cavitation method, perfluorocarbon gases are pumped into the obtained mixture at room temperature, processing ultrasonic cavitation for 3 min under the power of 10 kW, and cooling down to room temperature to obtain a first microbubble suspension;
(3) The first microbubble suspension is stood for 12 h, and then centrifuged to remove the upper layer microbubbles with bigger particle size, measuring the particle size distribution of the microbubbles is in the range of 0.8 μm to 3 μm by a light microscope, and then 10 mL polyethyleneimine solution (concentration of 1 mg/L) is added slowly into the obtained microbubble suspension, oscillating under the ultrasonic power of 300 kW, after allowing to adsorb for 30 min, put into the 4° C. refrigerator to stand for stratification, discarding the subnatant, and then the upper layer solution is washed with PBS buffer repetitive for 3 times to remove the excess polyelectrolyte, thereby obtaining the second microbubble suspension with a positive charge on the surface;
(4) 10 mL of the aqueous solution of superparamagnetic nanoparticle modified with the sodium citric acid (wherein the molar ratio of the superparamagnetic nanoparticle to the lipid in the second microbubble suspension is 0.25:1) obtained by the Preparation Example 1 is added into the second microbubble suspension slowly, oscillating under the ultrasonic power of 300 kW, after allowing to adsorb for 30 min, put into the 4° C. refrigerator to stand for stratification, discarding the subnatant, and then the upper layer solution is washed with PBS buffer repetitive for 3 times to obtain a magnetic microbubble ultrasound contrast agent, denoted as S1.
The obtained magnetic microbubble ultrasound contrast agent S1 is observed by an optical microscope and the result is shown in
Processed by the Following Steps:
(1) Sorbitan monostearate (lipid), polysorbate 80 (lipid) and poloxamer F127 (Sigma-Aldrich P2443-250G, surfactant A, HLB value=23) are mixed well in a molar ratio of 1:0.8:1.35, 10 mL of the obtained mixture is taken and put into a 110° C. sterilization pot under the high-temperature and high-pressure conditions for 16 min, and then continuously stirred and cooled until the temperature is 40° C.;
(2) The resulting material obtained by step (1) and paclitaxel (chemotherapy drug) are mixed in a weight ratio of 100:8, applying ultrasonic cavitation method, perfluorocarbon gases are pumped into the obtained mixture at room temperature, processing ultrasonic cavitation for 3 min under the power of 10 kW, and cooling down to room temperature to obtain a first microbubble suspension;
(3) The first microbubble suspension is stood for 12 h, and then centrifuged to remove the upper layer microbubbles with bigger particle size, measuring the particle size distribution of the microbubbles is in the range of 0.8 μm to 3 μm by a light microscope, and then 10 mL polyethyleneimine solution (concentration of 1.5 mg/L) is added slowly into the obtained microbubble suspension, oscillating under the ultrasonic power of 250 kW, after allowing to adsorb for 40 min, put into the 4° C. refrigerator to stand for stratification, discarding the subnatant, and then the upper layer solution is washed with PBS buffer repetitive for 3 times to remove the excess polyelectrolyte, thereby obtaining the second microbubble suspension with a positive charge on the surface;
(4) 10 mL of the aqueous solution of superparamagnetic nanoparticle modified with the sodium citric acid (wherein the molar ratio of the superparamagnetic nanoparticle to the lipid in the second microbubble suspension is 0.18:1) obtained by the Preparation Example 2 is added into the second microbubble suspension slowly, oscillating under the ultrasonic power of 350 kW, after allowing to adsorb for 20 min, put into the 4° C. refrigerator to stand for stratification, discarding the subnatant, and then the upper layer solution is washed with PBS buffer repetitive for 3 times to obtain a magnetic microbubble ultrasound contrast agent, denoted as S2.
Processed by the Following Steps:
(1) Sorbitan monostearate (lipid), polysorbate 80 (lipid) and poloxamer F68 (Germany BASF, P21489-25G, surfactant A, HLB value=29) are mixed well in a molar ratio of 1:1.2:1.65, 10 mL of the obtained mixture is taken and put into a 130° C. sterilization pot under the high-temperature and high-pressure conditions for 8 min, and then continuously stirred and cooled until the temperature is 40° C.;
(2) The resulting material obtained by step (1) and paclitaxel (chemotherapy drug) are mixed in a weight ratio of 100:2, applying ultrasonic cavitation method, perfluorocarbon gases are pumped into the obtained mixture at room temperature, processing ultrasonic cavitation for 3 min under the power of 10 kW, and cooling down to room temperature to obtain a first microbubble suspension;
(3) The first microbubble suspension is stood for 12 h, and then centrifuged to remove the upper layer microbubbles with bigger particle size, measuring the particle size distribution of the microbubbles is in the range of 0.8 μm to 3 μm by a light microscope, and then 10 mL polyethyleneimine solution (concentration of 0.8 mg/L) is added slowly into the obtained microbubble suspension, oscillating under the ultrasonic power of 350 kW, after allowing to adsorb for 20 min, put into the 4° C. refrigerator to stand for stratification, discarding the subnatant, and then the upper layer solution is washed with PBS buffer repetitive for 3 times to remove the excess polyelectrolyte, thereby obtaining the second microbubble suspension with a positive charge on the surface;
(4) 10 mL of the aqueous solution of superparamagnetic nanoparticle modified with the sodium citric acid (wherein the molar ratio of the superparamagnetic nanoparticle to the lipid in the second microbubble suspension is 0.25:1) obtained by the Preparation Example 3 is added into the second microbubble suspension slowly, oscillating under the ultrasonic power of 250 kW, after allowing to adsorb for 40 min, put into the 4° C. refrigerator to stand for stratification, discarding the subnatant, and then the upper layer solution is washed with PBS buffer repetitive for 3 times to obtain a magnetic microbubble ultrasound contrast agent, denoted as S3.
Referring to the method of Example 1, the difference is that the ratio of the two lipids is changed, specifically, the molar ratio of sorbitan monostearate to polysorbate 80 is 1:2.5. [92] Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S4.
Referring to the method of Example 1, the difference is that the superparamagnetic nanoparticle modified with the sodium citric acid obtained by the Preparation Example 1 used in step (4) is replaced with the same weight of the superparamagnetic nanoparticle modified with the sodium citric acid obtained by the Preparation Example 4.
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S5.
Referring to the method of Example 1, the difference is that the poloxamer is replaced with the same molar weight of poly(isobutene-maleic anhydride) (Sigma-Aldrich, 531278-250G).
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S6.
Referring to the method of Example 1, the difference is that the poloxamer is replaced with the same molar weight of poly(maleic anhydride-alt-1-octadecene) (Sigma-Aldrich, 419117-250G).
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S7.
Referring to the method of Example 1, the difference is that the dosage of the poloxamer is changed, specifically, sorbitan monostearate, polysorbate 80 and poloxamer F68 are mixed in the molar ratio of 1:1:1.2.
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S8.
Referring to the method of Example 1, the difference is that the dosage of the poloxamer is changed, specifically, sorbitan monostearate, polysorbate 80 and poloxamer F68 are mixed in the molar ratio of 1:1:1.0.
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S9.
Referring to the method of Example 1, the difference is that the dosage of the poloxamer is changed, specifically, sorbitan monostearate, polysorbate 80 and poloxamer F68 are mixed in the molar ratio of 1:1:0.8.
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S10.
Referring to the method of Example 1, the difference is that the dosage of the poloxamer is changed, specifically, sorbitan monostearate, polysorbate 80 and poloxamer F68 are mixed in the molar ratio of 1:1:0.6.
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S11.
Referring to the method of Example 1, the difference is that the dosage of the poloxamer is changed, specifically, sorbitan monostearate, polysorbate 80 and poloxamer F68 are mixed well in the molar ratio of 1:1:2.
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S12.
Referring to the method of Example 1, the difference is that the poloxamer is replaced with the same ratio weight of poloxamer P123 (Sigma-Aldrich, 435465-250ML, surfactant A, HLB value=9).
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as S13.
Referring to the method of Example 1, the difference is that no poloxamer is added.
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as D1.
Referring to the method of Example 1, the difference is that the surfactant A poloxamer used in the Example 1 is replaced with glycerol monostearate (TianWeiTaiDa RH30299-100g).
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as D2.
Referring to the method of Example 1, the difference is that the superparamagnetic nanoparticle modified with the sodium citric acid obtained by the Preparation Example 1 is replaced with the same weight of superparamagnetic Fe3O4 nanoparticle modified with poloxamer on the surface obtained by the Comparative Preparation Example 1.
Finally, a magnetic microbubble ultrasound contrast agent is obtained, denoted as D3.
Referring to the method of Example 1, the difference is that no superparamagnetic nanoparticle modified with the sodium citric acid is added, i.e., no step (3) or step (4) is performed, the first microbubble suspension with a positive charge on the surface obtained by step (2) is the final microbubble ultrasound contrast agent, denoted as D4.
(1) Stability Test
The stability of the ultrasound contrast agent in vivo is reflected by the half-life of the ultrasound contrast agent, and the longer the half-life, the higher the stability. Particularly, the test method includes (taking a rabbit as the object):
Selecting a length of vascular area in the ultrasonic image randomly after the ultrasound contrast agent is injected under the record of real-time ultrasound imaging, and recording the change of the average grey value in the area. Recording the point-in-time as t1 when the average grey value reaches a maximum A, and recording the point-in-time as t2 when the average grey value drops to 50% of the A, so the half-life of this kind of microbubbles is 10421. Note: Ensuring the concentration and dosage of the ultrasound contrast agent are same for each injection.
The measured half-life results of the ultrasound contrast agents from the Examples and Comparative Examples are recorded in Table 1, respectively.
(2) Mechanical Index Test
In vitro enriched blasting experiment is performed. Particularly, the test method includes:
Injecting the ultrasound contrast agent of the Examples and Comparative Examples with the same concentration (106 pcs/mL) into the cellulose hose (inner diameter is 1 mm) with ndfeb magnet (5000 Gs) placed on one side respectively, and performing an in-vitro enriched blasting experiment of magnetic microbubbles under the condition of physiological flow rate (100 mL/h). The ultrasonic imaging/blasting probe uses a linear array probe with 196 array elements, a center frequency of 12 MHz and a bandwidth of 6 MHz. Controlling the mechanical index (control range is MI=0.1-2.5, stepping is 0.1) of the ultrasonic wave emitted by the ultrasonic probe, and observing the blast of the microbubbles under different mechanical index and recording the mechanical indexes respectively when the blasting rates of the ultrasound contrast agent according to each Examples and Comparative Example are greater than 90% (time is less than 10 s) (blasting rate=|before blasting−after blasting|/before blasting*100%), and the results are recorded in Table 1.
(3) Magnetism Test
In vitro enrichment experiment is performed. Particularly, the test method includes:
Injecting the ultrasound contrast agent of the Examples and Comparative Examples with the same concentration (106 pcs/mL) into the cellulose hose (inner diameter is 1 mm) with ndfeb magnet (5000 Gs) placed on one side respectively, and performing an in-vitro enriched blasting experiment of magnetic microbubbles under the condition of static flow rate (0 mL/h). The ultrasonic imaging probe uses a linear array probe with 196 array elements, a center frequency of 12 MHz and a bandwidth of 6 MHz. Controlling the mechanical index (control range is MI<0.1) of the ultrasonic wave emitted by the ultrasonic probe, and observing the magnetism of the magnetic microbubbles under different mechanical index.
Within 15 min, if almost all the magnetic microbubbles are enriched on the magnet side (ultrasonic image shows that the gray characteristic of the magnetic microbubbles on the magnet side is larger than 95% of all the microbubbles signal), it is considered that the magnetism is normal.
Within 15 min, if more than half of the magnetic microbubbles are enriched on the magnet side (ultrasonic image shows that the gray characteristic of the magnetic microbubbles on the magnet side is larger than 50% of all the microbubbles signal), it is considered that the magnetism is weak.
Within 15 min, if the magnetic microbubbles are uniformly distributed and have no adsorption effect (ultrasonic image shows that the gray characteristic of the magnetic microbubbles on the magnet side is distributed in the cellulose hose uniformly), it is considered as no magnetism.
(4) Taking the magnetic microbubble ultrasound contrast agent S1 of Example 1 and the ultrasound contrast agent D4 of Comparative Example 4 as examples, after 10 enriched blasting experiment, the enriched gray scales of S1 and D4 are compared, as shown in (a) of
It can be seen from Table 1, the composition for ultrasound contrast agent and the ultrasound contrast agent according to the present application have both longer half-life and higher blasting mechanical index, as well as good magnetism, thereby the requirements for in vivo cyclic targeted delivery may be met by the magnetic microbubble ultrasound contrast agent.
And it can be seen from Example 1, Example 8 to Example 11, when the amount of emulsifier is in a proper range, the higher the content of emulsifier, the longer half-life of the magnetic ultrasound contrast agent and the higher threshold of blasting mechanical index; It can be seen from Example 12, when the content of the emulsifier is too high, the half-life of the magnetic ultrasound contrast agent and the threshold of blasting mechanical index are decreased. Therefore, the performance of the ultrasound contrast agent is controllable and is of great significance for practical application.
The preferred embodiments of the present application have been described above in detail; however, the present application is not limited thereto. Within the scope of the technical concept of the present application, a variety of simple modifications may be made to the technical solutions of the present application, including combining various technical features in any other suitable manner. These simple modifications and combinations should also be regarded as the content disclosed in the present application, and they all belong to the protection scope of the present application.
| Number | Date | Country | Kind |
|---|---|---|---|
| 202010597816.2 | Jun 2020 | CN | national |
This application is a continuation of International Application No. PCT/CN2021/084076 filed on Mar. 30, 2021, which claims priority to Chinese Patent Application No. 202010597816.2 filed on Jun. 28, 2020. The disclosures of the above-mentioned applications are hereby incorporated by reference in their entireties.
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/CN2021/084076 | Mar 2021 | US |
| Child | 17741764 | US |
