KR101292939B1 - A phospholipid nanoparticle for theragnostics of MR-guided high-intensity focused ultrasound and a method for preparation thereof - Google Patents

Abstract

The present invention relates to a MR-induced high-intensity focused ultrasound therapy and diagnostic phospholipid nanoparticles and a method of manufacturing the same. More specifically, the T1 MRI contrast agent is coupled to the gas-containing phospholipid nanoparticles to enable simultaneous high-intensity focused ultrasound therapy and monitoring by MR. It also relates to a MR induction high intensity focused ultrasound therapy and diagnostic phospholipid nanoparticles and a method of manufacturing the same.

Description

A phospholipid nanoparticle for theragnostics of MR-guided high-intensity focused ultrasound and a method for preparation

The present invention relates to a MR-induced high-intensity focused ultrasound therapy and diagnostic phospholipid nanoparticles and a method of manufacturing the same. More specifically, the T1 MRI contrast agent is coupled to the gas-containing phospholipid nanoparticles to enable simultaneous high-intensity focused ultrasound therapy and monitoring by MR. It also relates to a MR induction high intensity focused ultrasound therapy and diagnostic phospholipid nanoparticles and a method of manufacturing the same.

High intensity focused ultrasound introduces focused ultrasound that provides continuous, high intensity ultrasound energy to the focal point, and provides instantaneous thermal effects (65-100 ° C), cavitation effects, mechanical effects, and sonochemical depending on energy and frequency. It is known to be effective.

Ultrasound is not harmful when it passes through human tissue, but the high-intensity ultrasound that forms a focal point generates enough energy to cause coagulation necrosis and thermal cauterization effects, regardless of the type of tissue.

High-intensity focused ultrasound (HIFU) is commercially available for clinical use as a new technology for treating tumors and various diseases. HIFU is a non-invasive treatment that effectively thermally targets targets, mainly solid tumors, without damaging surrounding tissue. The frequency used in HIFU is 0.5-5 MHz and 1,000-5,000 Wcm ^-2 (~ 10 MPa). It is performed in the energy domain.

Despite the excellent advantages of HIFU, HIFU also has the disadvantage of being applied only to limited application areas due to problems such as long-term procedures, skin burns, and residual tumor cells around blood vessels.

In order to overcome this problem, the present inventors not only shorten the procedure time by increasing the HIFU effect, but also can be operated in a low energy region, and the blood vessel remaining time is long, thereby enhancing the treatment effect by a single injection and distributing cancer cells around blood vessels. A HIFU material that can be easily removed was synthesized, and the MAL contrast agent was mounted thereon, thereby completing the present invention by synthesizing a therapeutic image material for high intensity focused ultrasound.

An object of the present invention is to provide a phospholipid nanoparticles for diagnosis and diagnostic high-strength intensive ultrasound therapy and diagnostics capable of simultaneously monitoring the high-strength focused ultrasound therapy and MR by combining T1 MRI contrast agent to the gas-containing phospholipid nanoparticles.

Another object of the present invention is to provide a method of manufacturing the phospholipid nanoparticles for the MR induced high intensity focused ultrasound therapy and diagnostics.

In order to solve the above problems, the present invention is a phospholipid nanoparticles containing a dodecafluoropentane (C ₅ F ₁₂ ) gas therein, wherein the phospholipid nanoparticles are hydrophobic of the fatty acid chain of the phospholipid and the surfactant Formed evenly internal hydrophobic layer by bonding and surface modified with PEG 350, dodecafluoropentane gas contained in the hydrophobic inner region, T1 MRI contrast agent is bonded to the hydrophilic surface, the phospholipid nano The particles provide phospholipid nanoparticles having a particle size of 10 to 100 nm.

Phospholipid nanoparticles of the present invention contains dodecafluoropentane gas therein and has a circulation time sufficient for high intensity focused ultrasound therapy, so that it can be used as a material for high intensity focused ultrasound therapy, and at the same time T1 on the surface MRI contrast agent can be combined to monitor the image by MR can be used for diagnostic purposes. That is, in the present invention, the phospholipid nanoparticles of the above-described type may be used as MR induction high intensity focused ultrasound therapeutic imaging material.

In the present invention, the phospholipid nanoparticles form a homogeneous inner hydrophobic layer by hydrophobic bonding of a phospholipid fatty acid chain and a surfactant, and is surface-modified with PEG 350, and dodecafluoropentane gas is contained in the hydrophobic inner region. And a T1 MRI contrast agent bound to the hydrophilic surface.

In the present invention, the phospholipids include 1,2-stearic five days - sn - glycero-3-phosphocholine (1,2-distearoyl- sn -glycero-3 -phosphocholine, DSPC), 1,2- diacyl - sn - glycero-3-phospho-ethanolamine (1,2-diacyl- sn -glycero-3 -phosphoethanolamine, DOPE), 1,2- Dima Iris weekends - sn - glycero-3-phosphatidylethanolamine in (1 , 2-Dimyristoyl- sn -glycero-3 -phosphatidylethanolamine, DMPE), 1,2- di-stearic five days - sn - glycero-3-phospho-ethanolamine (1,2-distearoyl-sn-glycero -3-phosphoethanolamine, DSPE) and the like, but are not limited thereto.

In the present invention, the T1 MRI contrast agent may be used gadolinium or iron oxide, but is not limited thereto.

In the present invention, it is designed in such a way that the gadolinium can be mounted on the phospholipid nanoparticles containing perfluorocarbons to increase the HIFU effect and provide a therapeutic image material for the MR induced high intensity focused ultrasound which can be monitored by MR. It was.

One of the prerequisites for MR imaging with high intensity focused ultrasound is stability that can provide sufficient body circulation time during the procedure. On the other hand, gas-filled particles are more effective at larger sizes, such as microbubbles, as a therapeutic material that can increase the effect of high intensity focused ultrasound. Therefore, the present invention designed a therapeutic imaging material suitable for application in an in vivo environment by compromising circulation time and HIFU effect.

Accordingly, in order to improve short plasma half-life (<30 min) due to instability in the bloodstream of microbubbles (0.1 micron <Φ <5 micron), dodecafluoropentane (C ₅ F ₁₂ Phospholipid nanoparticles in the 10nm <Φ <100nm region containing gas were synthesized and examined by the distribution of body and circulation time.They were not rapidly removed by the kidneys and captured by the reticuloendothelial system (RES) of the liver and spleen. It was confirmed that it had sufficient circulation time (plasma half-life> ˜1.5). That is, the phospholipid nanoparticles of the present invention preferably have a particle size of 10 to 100 nm in terms of stability and therapeutic effect.

As an embodiment of the present invention, a phospholipid nanoparticle having a structure as shown in FIG. 1 may be provided.

Phospholipid nanoparticles of Figure 1 is a model of a bioapplicable HIFU agonist is designed to be easily biodegradable in the body based on the hydrophobic bond based on the phospholipid, which is basically a biomaterial.

The nanoparticles of HIFU agonists are surface-modified with polyethylene glycol so that they are injected intravenously and are not easily removed from liver and spleen filled with reticuloendothelial cells, and the essential condition to be equipped as HIFU agonist in the body is HIFU procedure time. (> 1hr) or more circulation time should be maintained to adjust the size to the proper size (10nm <Φ <100nm) so that the PEG is evenly distributed on the surface to avoid the rapid release to the kidneys or excessive liver absorption. Designed using materials that decompose.

In the embodiment of the present invention, the hydrophobic interaction of polysorbate 80 with fatty acid chains such as oleic acid, myristoyl acid, palmitic acid, and stearic acid basically gives structural stability in physiological buffer solution and slightly reduces solubility. Phospholipid nanoparticles surface-modified uniformly with PEG 350 were synthesized in the size of 30, 50, and 100 nm in order to increase the circulation time by preventing them from being trapped by the reticuloendothelial system in vivo, and then DTPA- was formed on the surface of the phospholipid nanoparticles. MR imaging was performed by combining Dolanium and a dodecafluoropentane gas was mounted therein to synthesize a therapeutic imaging material for MR-induced high-intensity ultrasound focused therapy that provided HIFU effect.

Synthesis strategy of the therapeutic image material for the MR-guided high-intensity ultrasound focused therapy synthesized in the present invention focused on the effective application in vivo. For this purpose, the distribution of the body and the residual time in the blood flow were measured along with the HIFU effect.

In one experimental example of the present invention, the HIFU enhancement effect of the synthesized C ₅ F ₁₂ -PLN (Φ = 30, 50, 100nm) was investigated. As a result, Φ = 50nm and Φ = 100nm C ₅ F ₁₂ gas-loaded phospholipids. Significant effects were confirmed in the nanoparticles.

In one experimental example of the present invention, the therapeutic imaging material, ie, phospholipid nanoparticles can be monitored by MAL at the same time as the HIFU therapeutic effect, DTPA (diethylenetriaminepentaacetic acid) on the surface of the phospholipid nanoparticles containing the synthesized dodecafluoropentane gas The gadolinium content in the phospholipid nanoparticles of the present invention prepared by binding to form a gadolinium complex compound was investigated and the magnetism was identified as a squid. As a result, a significant amount of gadolinium content was confirmed in the phospholipid nanoparticles of the present invention and it was confirmed that it had paramagnetic properties.

In one experimental example of the present invention, the synthesized Gd-C ₅ F ₁₂ -PLN (Φ = 30, 50, 100 nm) not only provides a long circulation time but also EPR that can accumulate in cancer tissues due to high permeability of tumor tissues. The accumulation of nanoparticles by EPR in tumor tissues was evaluated to confirm that they have an enhanced permeability retention effect. As a result, it was confirmed that the degree of high accumulation of the phospholipid nanoparticles of the present invention in the tumor tissue.

In addition, in one experimental example of the present invention, the HIFU enhancement effect of Gd-C ₅ F ₁₂ -PLN synthesized in a tumor model of a mouse was evaluated using a HIFU device for experimental animals. As a result, it was confirmed that the necrosis range of tumor tissues injected with Gd-C ₅ F ₁₂ -PLN and HIFU was significantly increased.

As a result, the present invention Gd-C ₅ F ₁₂ -PLN in the order of increasing the size (100nm>50nm> 30nm) HIFU effect was increased and the plasma half-life in the mouse has a circulation time of 1.5 hours or more to utilize during the HIFU procedure It was found to be a possible therapeutic imaging material.

Therefore, Gd-C ₅ F ₁₂ -PLN with long circulation time will be able to be used as an effective therapeutic image material because it will be able to supply continuous therapeutic image material to tumor tissue during HIFU procedure according to tumor tissue concentration of high intensity focused ultrasound. have.

In addition, the present invention provides a method for producing the phospholipid nanoparticles comprising the following steps.

1) preparing a phospholipid mixture solution by sonicating phospholipid and dodecafluoropentane in a solvent;

2) preparing a phospholipid nanoparticle loaded with dodecafluoropentane gas by mixing a surfactant with the phospholipid mixture solution and performing ultrasonic treatment; And

3) binding a T1 MRI contrast agent to the phospholipid nanoparticles loaded with dodecafluoropentane gas.

Step 1 is a step of preparing a phospholipid mixed solution by mixing the phospholipid and dodecafluoropentane in the solvent and sonication, wherein the phospholipid and dodecafluoropentane are uniformly dispersed in the solvent.

In the present invention, methanol or chloroform may be used as the solvent, and any solvent capable of dissolving phospholipid may be used without limitation.

In the present invention, the phospholipids include 1,2-stearic five days - sn - glycero-3-phosphocholine (1,2-distearoyl- sn -glycero-3 -phosphocholine, DSPC), 1,2- diacyl - sn - glycero-3-phospho-ethanolamine (1,2-diacyl- sn -glycero-3 -phosphoethanolamine, DOPE), 1,2- Dima Iris weekends - sn - glycero-3-phosphatidylethanolamine in (1 , 2-Dimyristoyl- sn -glycero-3 -phosphatidylethanolamine, DMPE), 1,2- di-stearic five days - sn - glycero-3-phospho-ethanolamine (1,2-distearoyl-sn-glycero -3-phosphoethanolamine, DSPE) and the like, but are not limited thereto.

In the present invention, the phospholipid mixed solution is a form of phospholipids combined with polyethylene glycol (PEG) 350 in order to reduce the solubility of the finally prepared phospholipid nanoparticles slightly and not be trapped in the reticulum endothelial system in order to increase the circulation time Can be used. The PEG 350 modifies the surface of the phospholipid nanoparticles to be prepared later.

In the present invention, dodecafluoropentane is mounted in gaseous form in the hydrophobic inner region of the phospholipid nanoparticles which are then synthesized to provide a HIFU effect.

In the present invention, it is preferable that the ultrasonic treatment conditions treat 50 to 80 W of ultrasonic waves at 50 to 70 DEG C for 10 to 40 minutes.

In one embodiment of the present invention, the sonication was performed by treating 70 W of ultrasonic waves at 65 ° C. for 15 minutes.

Step 2 is a step of preparing a phospholipid nanoparticles loaded with dodecafluoropentane gas by mixing a surfactant in the phospholipid mixture solution and sonicating, and uniformly internally by hydrophobic bonding of the phospholipid fatty acid chain and the surfactant Forming a hydrophobic layer, dodecafluoropentane gas is mounted in the hydrophobic inner region and the surface is a step of synthesizing phospholipid nanoparticles exhibiting hydrophilicity.

In the present invention, the phospholipid nanoparticles basically have a form that gives structural stability in a physiological buffer solution by hydrophobic interaction of a fatty acid chain and a surfactant therein.

In addition, in the present invention, the phospholipid nanoparticles preferably have a form that is surface-modified with polyethylene glycol (PEG) 350 in order to decrease the solubility and not be trapped in the reticulum endothelial system in vivo to increase the circulation time.

In the present invention, the phospholipid nanoparticles preferably have a size of 10nm to 100nm in order to compromise the circulation time and HIFU effect.

In the present invention, the surfactant may be a polysorbate 80 known under the trade name Tween 80, but is not limited thereto.

In the present invention, it is preferable that the ultrasonic treatment conditions treat 50 to 80 W of ultrasonic waves at 50 to 70 DEG C for 10 to 40 minutes.

In one embodiment of the present invention, the sonication was performed by treating 70 W of ultrasonic waves at 65 ° C. for 15 minutes.

Step 3 is a step of binding a T1 MRI contrast agent to the phospholipid nanoparticles loaded with dodecafluoropentane gas, wherein the T1 MRI contrast agent is bound to the surface of the phospholipid nanoparticles to have an MR contrast effect.

In the present invention, the T1 MRI contrast agent may be used gadolinium (iron) or iron oxide, but is not limited thereto.

In the present invention, the T1 MRI contrast agents include 1,2-di-myristoyl-sn-glycero-3-phosphatidylethanolamine-diethylenetriamine pentaacetic acid (1,2-Dimyristoyl- sn -glycero-3 -phosphatidylethanolamine- diethylenetriaminepentaacetic acid (DMPE-DTPA) can be used to bind phospholipid nanoparticles.

MR-induced high intensity focused ultrasound therapeutic image material according to the present invention, unlike the conventional high-strength focused ultrasound treatment material, it can be utilized as a therapeutic image material by simultaneously implementing the therapeutic enhancement effect and the MR image contrast effect for the MR-induced high intensity focused ultrasound therapy. Its stability is high enough to maintain the body during high-intensity focused ultrasound procedure, and it is more likely to be clinically applied than conventional materials by maintaining the therapeutic effect during the whole procedure.

MR-induced high intensity focused ultrasound therapy image material according to the present invention can enhance the therapeutic effect in the lower and safe energy area than the existing high intensity focused ultrasound therapy image material can reduce the side effects of high intensity focused ultrasound therapy and various types of tumors Organizations can extend their application.

MR-guided high-intensity focused ultrasound therapy image material according to the present invention can be characterized by the magnetic resonance imaging of the lesion image, differential diagnosis of the local lesion, the extent of the tumor lesion and determination of the progression of the disease, early diagnosis of the tumor lesion, etc. It can be effectively used for MR-induced high-intensity focused ultrasound therapy according to this diagnosis.

Figure 1 schematically shows the structure of one embodiment of the phospholipid nanoparticles of the present invention.
Figure 2 is a graph showing the results of the squid test of Gd-C ₅ F ₁₂ -PLN-100.
Figure 3 shows the results of testing the cytotoxicity of Gd-C ₅ F ₁₂ -PLN.
4 is a simplified diagram of an in vitro HIFU evaluation system for testing candidates of HIFU agents.
Figure 5 is a high-temperature phenomenon due to the HIFU strengthening effect of Gd-C ₅ F ₁₂ -PLN-30, Gd-C ₅ F ₁₂ -PLN-50 and Gd-C ₅ F ₁₂ -PLN-100 as white opaque white The result of comparing each degree of change is shown.
Figure 6 measures the half-life in the bloodstream of Gd-C ₅ F ₁₂ -PLN-30 (A), Gd-C ₅ F ₁₂ -PLN-50 (B) and Gd-C ₅ F ₁₂ -PLN-100 (C) A graph showing one result.
7 shows muscle, kidney, liver and liver following 24 hours after injection of Gd-C ₅ F ₁₂ -PLN-30, Gd-C ₅ F ₁₂ -PLN-50 and Gd-C ₅ F ₁₂ -PLN-100 It is a graph showing the degree of distribution in the spleen.
FIG. 8 shows Gd-C ₅ F ₁₂ -PLN-50 and Gd-C ₅ F ₁₂ -PLN-100 in mice, respectively. T1-weighted images of tumor tissues were obtained up to 8 hours after caudal vein injection in mice. The result of the measurement is shown.
Figure 9 is the one performed in tumor models in mice injected with Gd-C ₅ F ₁₂ -PLN-100 and a tumor necrosis HIFU treatment to a range with only HIFU group to identify the high-intensity focused ultrasound therapy enhancing effect anatomically The result of comparing the necrotic range is shown.

It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the invention, as claimed.

Example  1 to 3: C ₅ F ₁₂  Gas free Gd Phospholipid Nanoparticles Preparation

As phospholipids in vitro, DSPC (25 mM), DOPE-PEG 350 (22.2 mM), DMPE-DTPA (22.8 mM) and DSPE-PEG 350 (17.7 mM) were mixed in a ratio of 25: 10: 50: 15. Methanol was added to the phospholipid mixture in the same amount and mixed with the phospholipid mixture. The phospholipid mixture was dried like a thin film by flowing nitrogen flux into the test tube for 1 to 1 and a half hours. After dissolving fat in PBS, it was left at 60 ℃ for about 10 minutes. The ultrasonic bath was sonicated at 70W intensity with a 90% duty cycle at 65 ° C. for 15 min. Tween 80 was added at 14% (v / v) of the total volume. Again, the ultrasonic bath was sonicated at 70W intensity with a 90% duty cycle at 65 ° C. for 15 min. Repeated pumping 11 times using a film of Min-extruder with cut-off (Φ) = 30 nm, 50 nm and 100 nm, respectively, the size of 30 nm (Example 1), 50 nm (Example 2) and 100 nm (Example 3), respectively. Phospholipid nanoparticles were prepared. 100 mM of Gd was added to each of the phospholipid nanoparticles and mixed. Gd was washed three times by filtration (cut-off 3K) by adding 10 times the volume of PBS.

Example  4 to 6: C ₅ F ₁₂  Gas-containing Gd Phospholipid Nanoparticles Preparation

As phospholipids in vitro, DSPC (25 mM), DOPE-PEG 350 (22.2 mM), DMPE-DTPA (22.8 mM) and DSPE-PEG 350 (17.7 mM) were mixed in a ratio of 25: 10: 50: 15. For the production of phospholipid nanoparticles including C ₅ F _12, the C ₅ F ₁₂ were mixed into the 50㎕. Methanol was added to the mixture in the same amount as the phospholipid mixture and mixed. The phospholipid mixture was dried like a thin film by flowing nitrogen flux in a test tube for 1 to 1 and a half hours. After dissolving fat in PBS, it was left at 60 ℃ for about 10 minutes. The ultrasonic bath was sonicated at 70W intensity with a 90% duty cycle at 65 ° C. for 15 min. Tween 80 was added at 14% (v / v) of the total volume. Again, the ultrasonic bath was sonicated at 70W intensity with a 90% duty cycle at 65 ° C. for 15 min. 11 pumping cycles were repeated using films of cut-off (Φ) = 30 nm, 50 nm, and 100 nm, respectively, Φ = 30 nm (Example 4), 50 nm (Example 5) and 100 nm (Example 6), respectively. Phospholipid nanoparticles having a size of were prepared. 100 mM of Gd was added to each of the phospholipid nanoparticles and mixed. Gd was washed three times by filtration (cut-off 3K) by adding 10 times the volume of PBS.

Experimental Example  1: of the phospholipid nanoparticles of the present invention Gd Content and paramagnetic

For the phospholipid nanoparticles prepared in Examples 1 to 6, the content of Gd in the product was analyzed using ICP-MS (Inductively Coupled Plasma Mass Spectrometry), and paramagnetic properties were confirmed through a squid test.

Table 1 shows the results of the content analysis of Gd.

division [Gd] (mM) [phosphous] (mM) [Gd] / [P] Example 1 (Gd-PLN-30) 2.43 28.34 0.09 Example 2 (Gd-PLN-50) 4.39 36.57 0.12 Example 3 (Gd-PLN-100) 4.24 39.70 0.11 Example 4 (Gd-C ₅ F ₁₂ -PLN-30) 3.97 37.13 0.11 Example 5 (Gd-C ₅ F ₁₂ -PLN-50) 4.14 38.34 0.11 Example 6 (Gd-C ₅ F ₁₂ -PLN-100) 3.80 43.88 0.09

On the other hand, as a result of the paramagnetic check, it can be seen that the phospholipid nanoparticles of all examples have paramagnetic properties. Representatively, the result of the squid test of Gd-C ₅ F ₁₂ -PLN-100 in Example 6 shows a typical paramagnetic graph as shown in FIG.

Experimental Example  2: for the present phospholipid nanoparticles MTT assay

Mouse vascular endothelial cell line MS-1 was incubated at 90% bottom in 96 well plates. Gd-C ₅ F ₁₂ -PLN synthesized in Examples 4 to 6 was made of DMEM containing 1% FBS in a concentration range of 0-12 mM as a concentration of [P] and the vascular endothelial cell line for 1 hour in a culture environment. And treated with MS-1. The group treated with the same method by making serial dilutions of the cell-lysis buffer capable of destroying cells was used as a control. Toxicity according to the concentration of Gd-C ₅ F ₁₂ -PLN was analyzed by detecting the number of viable cells by color reaction using MTT (dimethylthiazolediphenyltetrazolium bromide) solution.

The results of testing the cytotoxicity of Gd-C ₅ F ₁₂ -PLN are shown in FIG. 3.

3, it can be seen that no cytotoxicity was detected in the concentration range of 0-12 mM Gd-C ₅ F ₁₂ -PLN in the MS-1 vascular endothelial cell line.

Experimental Example  3: of the present phospholipid nanoparticles HIFU  Strengthening effect evaluation

Synthesized Gd-C ₅ F ₁₂ -PLN-30 (Example 4), Gd-C ₅ F ₁₂ -PLN-50 (Example 5), Gd-C ₅ F ₁₂ -PLN-100 (Example 6) A polyacrylamide gel having a composition of Table 2 with or without 625 μM was prepared.

ingredient density(%) Egg white 0.30 Acrylamide / bis, 19: 1, 40% solution 9.92 Ammonium persulfate 0.05 N, N, N ', N'-tetramethylethylenediamine 0.2 Glycerol Anhydride (Glycerol, angydrous) 4.5 Total volume 20 ml

An in vitro HIFU evaluation system for testing candidates of HIFU agonists was constructed as shown in FIG. 4.

The evaluation system of FIG. 4 should be filled with degassed water between the transducer and the sample due to the characteristic that the ultrasonic wave does not pass through the air and is refracted and degassed to remove noise or to protect the transducer on the back of the sample. A sound absorbing plate capable of absorbing ultrasonic waves with water was placed.

HIFU was performed for 30 seconds at 5000 W / Cm ² , 1MHz, 100% duty cycle using the research HIFU equipment (TIPS, Philips). The HIFU strengthening effect was evaluated by measuring the intensity of the transparent egg white to opaque white by the HIFU effect.

As described above, egg white is opaque white due to high heat phenomenon by HIFU strengthening effect of Gd-C ₅ F ₁₂ -PLN-30, Gd-C ₅ F ₁₂ -PLN-50 and Gd-C ₅ F ₁₂ -PLN-100 The result of comparing each degree of change is shown in FIG. 5, it can be seen that a significant HIFU effect is shown in Gd-C ₅ F ₁₂ -PLN-50 and Gd-C ₅ F ₁₂ -PLN-100.

Experimental Example  4: of the present phospholipid nanoparticles In the bloodstream  Half-life investigation

Balb / c mice were injected intravenously with Gd-C ₅ F ₁₂ -PLN (0.1 mmoles P / kg). After 0, 0.5, 1, 2, 5, 12 and 24 hours, 0.1 ml of blood were collected from the tail blood vessel, respectively. The concentration of gadolinium in the blood was measured by ICP-AES to calculate the half-life of Gd-C ₅ F ₁₂ -PLN in the bloodstream.

As a result, Figure 6 shows the circulation time confirmed in mice according to the size of Gd-C ₅ F ₁₂ -PLN. In FIG. 6, half-life in blood flow of Gd-C ₅ F ₁₂ -PLN-30 (A), Gd-C ₅ F ₁₂ -PLN-50 (B) and Gd-C ₅ F ₁₂ -PLN-100 (C) It can be seen that 2.49 ± 0.27 hrs, 1.54 ± 0.29 hrs, and 1.58 ± 0.17 hrs, respectively, and these phospholipid nanoparticles have sufficient blood flow duration as HIFU agent.

Experimental Example  5: Evaluation of distribution in the body after injection of the phospholipid nanoparticles of the present invention

Balb / c mice were injected intravenously with Gd-C ₅ F ₁₂ -PLN (0.1 mmoles P / kg). After 24 hours, mice were sacrificed with carbon dioxide gas and muscle, kidney, liver and spleen were removed. The concentration of gadolinium in each organ was measured by ICP-AES to evaluate the distribution in the body 24 hours after injection of Gd-C ₅ F ₁₂ -PLN.

As a result, Fig. 7 shows the degree of body distribution of Gd-C ₅ F ₁₂ -PLN-30, Gd-C ₅ F ₁₂ -PLN-50, and Gd-C ₅ F ₁₂ -PLN-100. 7, it can be seen that each of the phospholipid nanoparticles are more distributed in the liver and spleen than muscle and kidney.

Experimental Example  6: Analysis of the distribution of tumor tissues with time after injection of the phospholipid nanoparticles of the present invention

One million CT-26 colorectal cancer cell lines were injected subcutaneously in the back of Balb / c mice and grown until they were 1 centimeter in diameter. The mice were divided into a treatment group and a control group, and the treatment group contained 0.1 mmoles P / kg of Gd-C ₅ F ₁₂ -PLN-50 and Gd-C ₅ F ₁₂ -PLN-100, which showed HIFU effect in the sample environment on the gel. Intravenous injection and physiological saline were given intravenously in the control group. 0, 0.5, 1, 2, 4, and 8 hours after injection, T1-weighted images of tumor tissues were obtained with TR / TE = 8.5 / 350ms, respectively, using magnetic resonance imaging equipment for experimental animals. Contrast intensity was measured from T1 weighted images to analyze the distribution of tumor tissue over time after Gd-C ₅ F ₁₂ -PLN injection.

The results are shown in Fig. 8, Td-weighted images of tumor tissue were obtained from Gd-C ₅ F ₁₂ -PLN-50 and Gd-C ₅ F ₁₂ -PLN-100, respectively, up to 8 hours after tail vein injection in a mouse tumor model. As a result of measuring the contrast intensity, the distribution of these phospholipid nanoparticles in tumor tissues increased with time after injection.

Experimental Example  7: phospholipid nanoparticles of the present invention on tumor tissue Thermal cauterization  Degree evaluation

One million CT-26 colorectal cancer cell lines were injected subcutaneously in the back of Balb / c mice and grown until they were 1 centimeter in diameter. The mice were divided into a treatment group and a control group, and the treated group was injected intravenously with Gd-C ₅ F ₁₂ -PLN (0.1 mmoles P / kg), in which the HIFU effect was confirmed in the sample environment on the gel in Experimental Example 2, Saline was injected intravenously in equal volumes. Mice were subjected to HIFU for 2 minutes in 3000 W / cm ² , 1.3 MHz, 50% duty cycle, 4 × 4 mm ² tumor tissues using a research HIFU instrument. After 24 hours, tumor tissues were extracted and fixed, and then paraffin-blocked, and histochemical HE staining was performed to evaluate the thermal catheterization of tumor tissues.

The results are shown in Fig. 9, it was found that the necrosis range of tumor tissues injected with Gd-C ₅ F ₁₂ -PLN-100 and HIFU was significantly increased as compared with the HIFU-only group.

Claims (14)

In phospholipid nanoparticles containing dodecafluoropentane (C ₅ F ₁₂ ) gas therein, the phospholipid nanoparticles form a uniform inner hydrophobic layer by hydrophobic bonding of a phospholipid fatty acid chain and a surfactant and PEG It is a surface-modified form of 350, dodecafluoropentane gas is contained in the hydrophobic inner region, T1 MRI contrast agent is bound to the hydrophilic surface, the phospholipid nanoparticles have a particle size of 10 to 100 nm Phospholipid nanoparticles.
The phospholipid nanoparticle of claim 1, wherein the phospholipid nanoparticle is used for high intensity focused ultrasound therapy.
The phospholipid nanoparticle of claim 1, wherein the phospholipid nanoparticle is used for image monitoring by MR.
The phospholipid nanoparticles of claim 1, wherein the phospholipid nanoparticles are used for high intensity focused ultrasound therapy and at the same time for image monitoring by MR.
The method of claim 1 wherein said phospholipid is 1,2-stearic five days - sn - glycero-3-phosphocholine (1,2-distearoyl- sn -glycero-3 -phosphocholine, DSPC), 1,2- Dia Sil- sn -glycero-3-phosphoethanolamine (1,2-diacyl- sn -glycero-3-phosphoethanolamine, DOPE), 1,2-dimyristoyl- sn -glycero-3-phosphatidylethanolamine ( 1,2-Dimyristoyl- sn -glycero-3- phosphatidylethanolamine, DMPE) and 1,2-di-stearic five days - sn - glycero-3-phospho-ethanolamine (1,2-distearoyl-sn-glycero -3-phosphoethanolamine , Phospholipid nanoparticles selected from the group consisting of DSPE).
The phospholipid nanoparticle of claim 1, wherein the T1 MRI contrast agent comprises gadolinium or iron oxide.
Preparing a phospholipid mixture solution by sonicating phospholipid and dodecafluoropentane in a solvent;
Preparing a phospholipid nanoparticle loaded with dodecafluoropentane gas by mixing a surfactant with the phospholipid mixture solution and performing ultrasonic treatment; And
A method for preparing the phospholipid nanoparticles according to claim 1, comprising coupling a T1 MRI contrast agent to the phospholipid nanoparticles loaded with dodecafluoropentane gas.
The method of claim 7, wherein the solvent uses methanol or chloroform.
The method of claim 7, wherein the phospholipid is 1,2-stearic five days - sn - glycero-3-phosphocholine (1,2-distearoyl- sn -glycero-3 -phosphocholine, DSPC), 1,2- Dia Sil- sn -glycero-3-phosphoethanolamine (1,2-diacyl- sn -glycero-3-phosphoethanolamine, DOPE), 1,2-dimyristoyl- sn -glycero-3-phosphatidylethanolamine ( 1,2-Dimyristoyl- sn -glycero-3- phosphatidylethanolamine, DMPE) and 1,2-di-stearic five days - sn - glycero-3-phospho-ethanolamine (1,2-distearoyl-sn-glycero -3-phosphoethanolamine , DSPE) method for producing at least one phospholipid nanoparticle selected from the group consisting of.
The method of claim 7, wherein the phospholipid is in the form of a polyethylene glycol (PEG) 350 bound.
The method of claim 7, wherein the sonication conditions are 50 to 80 W of ultrasonic waves at 50 to 70 ° C. for 10 to 40 minutes.
The method of claim 7, wherein the surfactant is polysorbate 80.
The method of claim 7, wherein the T1 MRI contrast agent is gadolinium or iron oxide.
8. The method of claim 7, wherein the T1 MRI contrast agent is 1,2-dimyristoyl- sn -glycero-3-phosphatidylethanolamine-diethylenetriaminepentaacetic acid (1,2-Dimyristoyl- sn -glycero-3- phosphatidylethanolamine-diethylenetriaminepentaacetic acid (DMPE-DTPA).

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