|Title of Invention||
"A FORMULATION PROVIDING ENHANCED ULTRASOUND CONTRAST IMAGES AND A METHOD FOR MAKING THE SAME"
|Abstract||The present invention relates to a formulation characterized in providing enhanced ultrasound contrast images, wherein the said formulation comprises microspheres comprising a poly(hydroxy acid) or copolymer or blend thereof and a hydrophobic compound wherein the microspheres are porous spheres with a honeycombed structure or sponge-like structure and having incorporated therein a perfluorocarbon that is a gas at body temperature, and the hydrophobic compound is a lipid incorporated with the polymer at a ratio of between 0.01 and 30% (weight lipid/weight polymer). wherein the dosage formulation comprises a dose of microspheres effective to provide enhanced ultrasound images for more than one minute in the myocardium when the microspheres are administered intravenously, and wherein the formulation can be reconstituted to yield a suspension having a microsphere concentration ranging from 1.0 x 10 to 3.5 x 109 microspheres/mL of suspension or a microsphere mass concentration ranging from 25 to 50 mg microspheres/mL suspension. The present invention also relates to a method of providing enhanced ultrasound images.|
|Full Text||The present invention relates to a dosage formulation providing enhanced ultrasound contrast images and a method for making the same.
Background of the Invention
The present invention is in the general field of diagnostic imaging agents, and is particularly directed to specific ultrasound contrast agent dosage formulations that provide enhanced images and images of long duration.
When using ultrasound to obtain an image of the internal organs and structures of a human or animal, ultrasound waves, waves of sound energy at a frequency above that discernable by the human ear, are reflected as they pass through the body. Different types of body tissue reflect the ultrasound waves differently and the reflections mat are produced by the ultrasound waves reflecting off different internal structures axe detected and converted electronically into a visual display.
For some medical conditions, obtaining a useful image of the organ or structure of interest is especially difficult because the details of the structure ate not adequately discernible from the surrounding tissue in an ultrasound image produced by the reflection of ultrasound waves absent a contrast-enhancing agent. Detection and observation, of certain physiological and pathological conditions may be substantially improved by enhancing the contrast in an ultrasound image by administering an ultrasound contrast agent to an ca-gan or other structure of interest. In other cases, detection of the movement of me ultrasound contrast agent itself is particularly important For example, a distinct blood flow pattern mat is known to result from particular cardiovascular abnormalities may only be discernible by administering the ultrasound contrast agent to the bloodstream and observing either blood flow or blood volume.
Materials that are useful as ultrasound contrast agents operate by having an effect on ultrasound waves as they pass through the body and are reflected to create the image from which a medical diagnosis is made. Different types of substances affect ultrasound waves in different ways and to varying degrees. Moreover, certain of the effects caused by contrast-enhancing agents are more readily measured and observed than others. In selecting an ideal composition for an ultrasound contrast agent, one would
prefer the substance that has the most dramatic effect on the ultrasound wave as it passes through the body. Also, the effect on the ultrasound wave should be easily measured. Gases are the preferred media for use as ultrasound contrast agents. The gas must be stabilized prior to usage as either surfactant stabilized bubbles or by encapsulating in liposomes or microparticles. There are three main contrast-enhancing effects which can be seen in an ultrasound image: backscatter, beam attenuation, and speed of sound differential.
A variety of natural and synthetic polymers have been used to encapsulate ultrasound contrast agents, such as air, hi an effort to make an ultrasound contrast agent that lasts longer following administration. Schneider et al, Invest. Radiol.. Vol. 27, pp. 134-139 (1992) describes three micron, air-filled, synthetic, polymer particles. These particles were reported to be stable in plasma and under applied pressure. However, at 2.5 MHz, their echogenicity was low. Another type of microbubble suspension has been obtained from sonicated albumin. Feinstein et al., J. Am. Coll. Cardiol... Vol. 11, pp. 59-65 (1988). Feinstein describes the preparation of microbubbles that are appropriately sized for transpulmonary passage with excellent stability in vitro. However, these microbubbles are short-lived in vivo, having a half-life on the order of a few seconds (which is approximately equal to one circulation pass) because of their instability under pressure. Gottlieb, S. et al., J. Am. Soc. Echo.. Vol. 3, pp. 328 (1990), Abstract; and Shapiro, J.R. et al., J. Am. Coll. Cardiol.. Vol. 16, pp. 1603-1607 (1990).
Gelatin-encapsulated microbubbles have also been described hi WO 80/02365 by Rasor Associates, Inc. These are formed by "coalescing" the gelatin. Gas microbubbles encapsulated within a shell of a fluorine-containing material are described in WO 96/04018 by Molecular Biosystems, Inc.
Microbubbles stabilized by microcrystals of galactose (SHU 454 and SHU 508) have also been reported by Fritzch et al. Fritzsch, T. et al, Invest. Radiol Vol. 23 (Suppl 1), pp. 302-305 (1988); and Fritzsch, T. et al., Invest. Radiol., Vol. 25 (Suppl 1), 1'60-161 (1990). The microbubbles last up to 15 minutes in vitro but less than 20 seconds in vivo. Rovai, D. et al., J. Am.
Coll. Cardiol.. Vol. 10, pp. 125-134 (1987); and Smith, M. et al., J. Am. Coll. Cardiol.. Vol. 13, pp. 1622-1628 (1989). EP 398 935 by Sobering Aktiengesellschaft discloses the preparation and use of microencapsulated gas or volatile liquids for ultrasound imaging, where the microcapsules are formed of synthetic polymers or polysaccharides. European Patent 458 745 by Sintetica discloses air or gas microballoons bounded by an interfacially deposited polymer membrane that can be dispersed in an aqueous carrier for injection into a host animal or for oral, rectal, or urethral administration, for therapeutic or diagnostic purposes.
WO 92/18164 by Delta Biotechnology Limited describes the preparation of microparticles by spray drying an aqueous protein solution to form hollow spheres having gas entrapped therein, for use in imaging. WO 93/25242 describes the synthesis of microparticles for ultrasonic imaging consisting of a gas contained within a shell of polycyanoacrylate or polyester. WO 92/21382 discloses the fabrication of microparticle contrast agents which include a covalently bonded matrix containing a gas, wherein the matrix is a carbohydrate. U.S. Patent Nos. 5,334,381, 5,123,414 and 5,352,435 to Unger describe liposomes for use as ultrasound contrast agents, which include gases, gas precursors, such as a pH activated or photo-activated gaseous precursor, as well as other liquid or solid contrast enhancing agents.
Others have looked at the effect of the gas which is encapsulated, and suggested the use of fluorinated gases to enhance imaging as compared to air. U.S. Patent No. 5,393,524 to Quay discloses the use of agents, including perfluorocarbons, for enhancing the contrast hi an ultrasound image. The agents consist of small bubbles, or microbubbles, of selected gases, which exhibit long life spans hi solution and are small enough to traverse the lungs, enabling their use in ultrasound imaging of the cardiovascular system and other vital organs. EP 554213 by Bracco discloses the use of fluorinated hydrocarbon gases to prevent collapse of microvesicles upon exposure to pressure in the bloodstream. WO 95/23615 by Nycomed discloses microcapsules for imaging which are formed by coacervation of a solution, for example, a protein solution, containing a perfluorocarbon. WO 95/03357
by Massachusetts Institute of Technology discloses microparticles formed of polyethylene glycol-poly(lactide-co-glycolide) block polymers having imaging agents encapsulated therein, including gases such as air and perfluorocarbons. As described in WO 94/16739 by Sonus Pharmaceuticals, Inc., while solids and liquids reflect sound to a similar degree, gases are known to be more efficient and are the preferred media for use as ultrasound contrast agents, hi fact, as shown by Example 12 of WO 94/16739, protein microcapsules were dismissed as raising safety concerns (as well as efficacy issues) when administered to mini-pigs. U.S. Patent Numbers 6,132,699 and 5,611,344 both describe methods of enhancing contrast using perfluorocarbon gases in synthetic polymeric shells. U.S. Patent No. 5,837,221 describes a method of making a porous polymeric microparticle having a hydrophobic agent incorporated into the polymer to increase echogenicity.
Several ultrasound contrast agents have been approved in either the United States or Europe for very limited cardiac applications. OPTISON® (Amersham, Mallinkrodt) consists of heat denatured human albumin microcapsules containing the gas octafluoropropane. Each mL of microsphere suspension contains 5-8 xlO8 microspheres with a mean diameter hi the 2-4.5 micron size range and 220 jag octafluoropropane. These microspheres have not been approved for myocardial blood flow assessment and have only been approved for ventricular chamber enhancement. At high bolus doses (5 mL suspension or 1100 ^g octafluoropropane), ventricular chamber enhancement lasts up to 5 minutes.
DEFINITY® (Bristol Myers Medical Imaging) consists of octafluoropropane containing lipid microspheres where the lipid shell is comprised of the phospholipids DPPA, DPPC, and mPEG-DPPE. Each mL of suspension contains 1.2 x 1010 microparticles having a mean diameter in the 1.1-3.3 micron size range and 1100 |ig of octafluoropropane. The agent is only approved for ventricular chamber enhancement and not myocardial blood flow assessment. At a bolus dose of 700 uL (for a 70kg person) or
5133 ug of gas, the agent has an enhancement duration in the ventricular chambers of approximately 3.4 minutes.
IMAGENT® (Photogen Inc.) consists of lipid microspheres containing pefluorohexane where the lipid shell is comprised of the phospholipid DMPC. Each mL of suspension contains 1.4 x 109 microparticles having a mean diameter less than 3 microns and 92 \ig of perfluorohexane. The agent is only approved for ventricular chamber enhancement and not myocardial blood flow assessment. At a bolus dose of 0.43 mL (for a 70kg person) or 40 (j.g of gas, the agent has a mean enhancement duration in the ventricular chambers of approximately 2.6 minutes.
In all cases, these commercial agents have limited utility and are not approved for applications other than ventricular chamber enhancement and provide mean image enhancement durations hi the ventricular chambers lasting for periods of 5 minutes or less. There is a lack of commercial ultrasound contrast agents which allow enhanced images of the cardiovascular system, particularly of the myocardium and the ventricular chambers, for long duration. The agents described in the prior art when administered as a bolus or short infusion result in images of the myocardium which last for significantly less time than the amount of tune required to conduct a complete examination of the heart. Typically, the prior art agents provide images that last for well below one minute for the myocardium. An agent which can provide enhanced image durations exceeding one minute in the myocardium and/or greater than 5 minutes hi the ventricular chambers is desirable.
It is therefore an object of the invention to provide a dosage formulation containing microparticles that provides enhanced images and unages of long duration, particularly for cardiac applications.
It is another object of the invention to provide a kit for administering the dosage formulation containing microparticles for use in ultrasound imaging techniques.
Summary of the Invention
Clinical studies have been conducted and specific dosage formulations developed using polymeric microparticles having incorporated therein perfluorocarbon gases that provide significantly enhanced images of long duration. The dosage formulation typically includes one, two or up to five doses, most preferably one or two doses, of microparticles formed of a biocompatible polymer, preferably including a lipid incorporated therein, and containing a perfluorocarbon that is a gas at body temperature. The microparticles are administered to a patient in a dose effective to enhance ultrasound imaging in the ventricular chambers for more than five minutes and/or in the mycocardium for more than a minute, and a dose ranging from 0.025 to 8.0 nig microparticles/kg body weight. Preferably the dose administered to a patient ranges from 0.05 to 4.0 mg microparticles/kg body weight. In a preferred embodiment, the ultrasound imaging is enhanced in the ventricular chambers for more than 9 minutes and/or in the myocardium for more than 2 minutes.
The dosage formulation typically is provided in a vial or in a syringe. In a typical formulation, the dosage formulation is hi the form of a dry powder that is reconstituted with sterile water prior to use by adding the water to the vial or syringe of the dry powder and shaking to yield an isosmotic or isotonic suspension of microparticles. In the preferred embodiment of this dosage formulation, the suspension contains 1.0 - 3.5 x 109 microparticles /mL of suspension or 25-50 mg microparticles/mL of suspension with the most preferred concentration yielding a suspension containing 1.5-2.8 x 109 microparticles/mL of suspension or 30-45 mg microparticles/mL of suspension, hi a preferred embodiment, the microparticles have a mean particle size less than 8 microns, most preferably a mean particle size of 1.8-3.0 microns.
In the most preferred embodiment, the gas is CF4, C2F4, C2F6, C3F6, CsFg, C4Fg, C4Fio, or SFe. In preferred embodiments, the gas is n-perfluorobutane (C4Fio) provided in an amount between 75-500 ug/mL of administered volume of microparticle suspension; preferably the n-
perfluorobutane is provided in an amount between 100-400 ug/mL of administered volume of microparticle suspension and most preferably between 150-350 jj,g/mL of administered volume of microparticle suspension; or the gas is n-octafluoropropane provided in an amount between 75-375 fig/mL of administered volume of microparticle suspension, most preferably between 120-300 ug/mL of administered volume of microparticle suspension.
In the most preferred embodiment, the microparticle is formed of a synthetic polymer such as poly(hydroxy acids) which include poly(lactic acid), poly(glycolic acid), and poly(lactic acid-co-glycolic acid), polyglycolides, polylactides, and poly(lactide-co-glycolide), polyanhydrides, polyorthoesters, pplyamides, polycarbonates, polyalkylenes such as polyethylene and polypropylene, polyalkylene glycols such as poly(ethylene glycol), polyalkylene oxides such as poly(ethylene oxide) polyvinyl alcohols, poly(yaleric acid), and poly(lactide-co-caprolactone), derivatives, copolymers and blends thereof and includes a hydrophobic compound incorporated with the polymer at a ratio of between 0.01 and 30% by weight of hydrophobic compound to weight of polymer, most preferably a lipid incorporated with the polymer at a ratio of between 0.01 and 30% (weight lipid/weight polymer). In a particularly preferred embodiment, the lipid is dioleoylphosphatidylcholine (DOPC), dimyristoylphosphatidylcholine (DMPC), dipentadecanoylphosphatidylcholine (DPDPC) dilauroylphosphatidylcholine (DLPC), dipahnitoylphosphatidylcholuie (DPPC), distearoylphosphatidylcholine (DSPC),
diarachidoylphosphatidylcholine (DAPC), dibehenoylphosphatidylcholine (DBPC), ditricosanoylphosphatidylcholine (DTPC), dilignoceroylphatidylcholine (DLGPC); or a phosphatidylethanolamine.
Most preferably, the synthetic polymer in the microparticles is poly(lactide-co-glycolide), with a lactide to glycolide ratio of 50:50 (i.e. 1:1) and a weight average molecular weight in the range 20,000-40,000 Daltons, and the hydrophobic compound in the microparticles is DAPC, in a ratio of 5 to 6.6% (weight DAPC/ weight polymer).
The dosage formulation may be provided as a vial or a syringe of dry powder containing microparticles or in a kit including a solution for resuspending the microparticles. Typically the vial or syringe of dry powder will also include excipients such as sugars or salts to make the solution isosmotic or isotonic after reconstitution. This dosage formulation is then administered to a patient to be imaged by injection, either as a bolus or an injection over a period of up to 30 minutes.
The microparticles are useful in a variety of diagnostic imaging procedures including ultrasound imaging, magnetic resonance imaging, fluoroscopy, x-ray, and computerized tomography. The microparticles were tested hi clinical trials for cardiology applications such as myocardial blood flow assessment and ventricular chamber enhancement.
Detailed Description of the Invention
Improved methods, microparticles, kits, and dosage formulations for ultrasound imaging are described herein. The microparticles are useful in a variety of diagnostic ultrasound imaging applications, particularly in ultrasound procedures such as blood vessel imaging and echocardiography such as myocardial blood flow assessment, myocardial blood volume assessment and ventricular chamber enhancement. I. Definitions
As generally used herein, the term "microparticle" includes "microspheres" and "microcapsules", as well as other microparticles, unless otherwise specified. Microparticles may or may not be spherical in shape. "Microcapsules" are defined herein as microparticles having an outer polymer shell surrounding a core of a gas. "Microspheres" as defined herein can be solid polymeric spheres, or porous spheres with a honeycombed structure or sponge like structure formed by pores throughout the polymer that are filled with a gas. Some microspheres may contain an outer polymer shell with a honeycombed structure or a sponge like structure formed by pores throughout the polymer shell and the pores are filled with gas. For this type of microsphere, this outer polymer shell surrounds an internal core of gas.
As generally used herein, the terms "dosage" and "dose" are used synonymously to refer to the amount of a substance that is given at one time or the amount of substance that is required to produce the desired diagnostic or contrast effect.
As used herein, the term "dosage formulation" refers to a vial or other container such as a syringe, containing one or more dosages of substance required to produce the desired diagnostic or contrast effect.
As generally used herein "region of a patient" refers to a particular area or portion of the patient. In some instances "region of patient" refers to regions throughout the entire patient. Examples of such regions are the pulmonary region, the gastrointestinal region, the cardiovascular region (including myocardial tissue or myocardium (i.e. heart muscle), ventricular chambers, atrial chambers, valve function), the renal region as well as other body regions, tissues, organs and the like, including the vasculature and circulatory systems, and as well as diseased tissue, including cancerous tissue. "Region of a patient" includes, for example, regions to be imaged with diagnostic imaging. The "region of a patient" is preferably internal, although it may be external.
As generally used herein "vasculature" denotes blood vessels (including arteries, veins, capillaries and the like).
As generally used herein "gastrointestinal region" includes the region defined by the esophagus, stomach, small and large intestines, and rectum.
As generally used herein "renal region" refers to the region defined by the kidney and the vasculature that leads directly to and from the kidney, and includes the abdominal aorta.
As generally used herein "region to be targeted" and "targeted region" are used interchangeably to refer to a region of a patient where delivery of an agent is desired.
As generally used herein "region to be imaged" and "imaging region" are used interchangeably to refer to a region of a patient where imaging is desired.
As generally used herein 'Ventricular blood flow or ventricular chamber enhancement" refers to the flow of blood through the ventricles of the heart hi one or more cardiac cycles.
As generally used herein "atrial blood flow" refers to the flow of blood through the atria of the heart in one or more cardiac cycles.
As generally used herein "myocardial blood flow" refers to the flow of blood in the vasculature of the heart muscle or myocardium, including the blood vessels in the heart, hi one or more cardiac cycles.
As generally used herein "myocardial blood volume" refers to the volume of blood in the vasculature of the heart muscle or myocardium.
As generally used herein "cardiac cycle" refers to a complete contractile period of the heart, and includes both the diastole and systole periods.
As generally used herein "increased brightness" refers to an increase in the brightness of an image compared to an image obtained without an ultrasound contrast agent.
As generally used herein "enhanced image" refers to an image which has increased brightness relative to an image obtained without an ultrasound contrast agent.
As generally used herein "duration" refers to the total time over which increased brightness of an image can be detected.
As generally used herein "coronary vasodilator" refers to a bioactive agent such as dipyridamole or adenosine which, when administered to a patient, causes dilation of the vasculature in the cardiovascular region. II. Microparticles
In the preferred embodiment, the microparticles contain a polymer, a lipid and a perfluorocarbon gas. Microparticles may consist of both microspheres and microcapsules, or only microspheres or microcapsules.
In the preferred embodiment, the microparticles are formed from synthetic polymers. Synthetic polymers produce microparticles that are biocompatible and are not contaminated by biological materials. Additionally, synthetic polymers are preferred due to more reproducible
synthesis and degradation both in vitro and in vivo. The polymer is selected based on the time required for in vivo stability, i.e., that time required for distribution to the site where imaging is desired, and the time required for imaging. Synthetic polymers may be modified to produce microparticles with different properties (e.g. changing molecular weight and/or functional groups).
Representative synthetic polymers are: poly(hydroxy acids) such as poly(lactic acid), poly(glycolic acid), and poly(lactic acid-co-glycolic acid), polyglycolides, polylactides, poly(lactide-co-glycolide) copolymers and blends, polyanhydrides, polyorthoesters, polyamides, polycarbonates, polyalkylenes such as polyethylene and polypropylene, polyalkylene glycols such as poly(ethylene glycol), polyalkylene oxides such as poly(ethylene oxide) polyvinyl alcohols, poly(valeric acid), and poly(iactide-co-caprolactone), derivatives, copolymers and blends thereof. As used herein, "derivatives" include polymers having substitutions, additions of chemical groups, for example, alkyl, alkylene, hydroxylations, oxidations, and other modifications routinely made by those skilled in the art.
Examples of preferred biodegradable polymers include polymers of hydroxy acids such as lactic acid and glycolic acid, polylactide, polyglycolide, poly(lactide-co-glycolide), and copolymers with PEG, polyanhydrides, poly(ortho)esters, polyurethanes, poly(butyric acid), poly(valeric acid), pory(lactide-co-caprolactone), blends and copolymers thereof. The most preferred polymer is poly(lactide-co-glycolide) with a lactide to glycolide ratio of 50:50 (i.e. 1:1) and the polymer having a weight average molecular weight hi the range 20,000-40,000 Daltons. The weight average molecular weight (Mw) of the polymer is the average molecular weight calculated on the basis of the mass of molecules with a given molecular weight within the distribution of individual polymer chains. Mw can be determined using gel permeation chromatography (GPC).
In the preferred embodiment, the polymer includes a hydrophobia compound, as described in U.S. Patent No. 5,837,221. In general,
incorporation of compounds such as lipids which are hydrophobic and in an
effective amount within the polymers, limits penetration and/or uptake of water by the microparticles and thus limits gas loss from the microparticles. This is effective in increasing the duration of enhanced imaging provided by microparticles that contain a lipid, a synthetic polymer and a gas encapsulated therein, especially fluorinated gases such as perfluorocarbons. Lipids which may be used to stabilize gas inside the polymeric microparticles include but are not limited to the following classes of lipids: fatty acids and derivatives, mono-, di and triglycerides, phospholipids, sphingolipids, cholesterol and steroid derivatives, terpenes and vitamins.
Fatty acids and derivatives thereof may include but are not limited to saturated and unsaturated fatty acids, odd and even number fatty acids, cis and trans isomers, and fatty acid derivatives including alcohols, esters, anhydrides, hydroxy fatty acids and prostaglandins. Saturated and unsaturated fatty acids that may be used include, but are not limited to, molecules that have between 12 carbon atoms and 22 carbon atoms in either linear or branched form. Examples of saturated fatty acids that may be used include, but are not limited to, lauric, myristic, palmitic, and stearic acids. Examples of unsaturated fatty acids that may be used include, but are not limited to lauric, physeteric, myristoleic, palmitoleic, petroselinic, and oleic acids. Examples of branched fatty acids that may be used include, but are not limited to, isolauric, isomyristic, isopalmitic, and isostearic acids and isoprenoids. Fatty acid derivatives include 12-(((7'-diethylaminocoumarin-3 yl)carbonyl)methylamino)-octadecanoic acid; N-[12-(((7'diethyiammocoumarin-3-yl) carbonyl)methyl-amino) octadecanoyl]-2-aminopalmitic acid, N succinyl-dioleoylphosphatidylethanol amine and palmitoyl-homocysteine; and/or combinations thereof. Mono, di and triglycerides or derivatives thereof that may be used include, but are not limited to molecules that have fatty acids or mixtures of fatty acids between 6 and 24 carbon atoms, digalactosyldiglyceride, 1,2-dioleoyl-sn-glycerol; l,2-dipalmitoyl-sn-3 succinylglycerol; and l,3-dipalmitoyl-2-succinylglycerol.
Phospholipids which may be used include but are not limited to phosphatidic acids, phosphatidyl cholines with both saturated and
unsaturated lipids, phosphatidyl ethanolamines, phosphatidylglycerols, phosphatidylserines, phosphatidylinositols, lysophosphatidyl derivatives, cardiolipin, and p-acyl-alkyl phospholipids. Examples of phospholipids include, but are not limited to, phosphatidylcholines such as dioleoylphosphatidylcholine (DOPC), dimyristoylphosphatidylcholine (DMPC), dipentadecanoylphosphatidylcholine (DPDPC), duauroylphosphatidylcholine (DLPC), dipalmitoylphosphatidylcholine (DPPC), distearoylphosphatidylcholine (DSPC),
diarachidoylphosphatidylcholine (DAPC), dibehenoylphosphatidylcholine (DBPC), ditricosanoylphosphatidylcholine (DTPC), dilignoceroylphatidylcholine (DLPC); and phosphatidylethanolamines such as dioleoylphosphatidylethanolamine or l-hexadecyl-2-paknitoylglycerophosphoethanolamine. Synthetic phospholipids with asymmetric acyl chains (e.g., with one acyl chain of 6 carbons and another acyl chain of 12 carbons) may also be used.
Sphingolipids which may be used include ceramides, sphingomyelins, cerebrosides, gangliosides, sulfatides and lysosulfatides. Examples of sphinglolipids include, but are not limited to, the gangliosides GM1 and GM2.
Steroids which may be used include but are not limited to cholesterol, cholesterol sulfate, cholesterol hemisuccinate, 6-(5-cholesterol 3p-yloxy) hexyl-6-amino-6-deoxy-l-thio-a-D-galactopyranoside, 6-(5-cholesten-3 p-tloxy)hexyl-6-amino-6-deoxyl-l-thio-a-D mannopyranoside and cholesteryl) 4'-tiimethyl 35 ammonio)butanoate.
Additional lipid compounds which may be used include tocopherol and derivatives, and oils and derivatized oils such as stearlyamine.
A variety of cationic lipids such as DOTMA, N-[l-(2,3-dioleoyloxy) propyl-N,N,N-trimethylammonium chloride; DOTAP, l,2-dioleoyloxy-3-(trimethylammonio) propane; andDOTB, l,2-dioleoyl-3-(4'-trimethyl-ammonio) butanoyl-sn-glycerol may be used.
The most preferred lipids are phospholipids, preferably DPPC, DAPC, DSPC, DTPC, DBPC, DLPC and most preferably DPPC, DSPC, DAPCandDBPC.
The lipid content ranges from 0.01-30% (w lipid/w polymer); preferably between 0.1-20% (w lipid/w polymer) and most preferably 1-12% (w lipid/w polymer).
When formed by the methods described herein, the size of the microparticles is consistently reproducible. As used herein, the terms "size" or "diameter" in reference to particles refers to the number average particle size, unless otherwise specified. An example of an equation that can be used to define the number average particle size (Xn) is shown below:
where n\ = number of particles of a given diameter (dj)-
As used herein, the term 'Volume average diameter" refers to the volume weighted diameter average. An example of equations that can be used to define the volume average diameter (Xv) is shown below:
where hj = number of particles of a given diameter (dj).
Particle size analysis can be performed on a Coulter counter, by light microscopy, scanning electron microscopy, transmittance electron microscopy, laser diffraction methods such as those using a Malvern Mastersizer, light scattering methods or time of flight methods. As used herein "Coulter method" refers to a method in which the powder is dispersed in an electrolyte, and the resulting suspension analyzed using a Coulter
Multisizer II fitted with a 50-um aperture tube. This method provides size measurements and particle concentrations.
In the preferred embodiment for the preparation of inj ectable microparticles capable of passing through the pulmonary capillary bed, the microparticles have a diameter less than eight microns. Larger microparticles may clog the pulmonary bed, and smaller microparticles may not provide sufficient contrast effect. The preferred microparticle size for an intravenously administered ultrasound contrast agent is between 0.75 microns and 5 microns and is most preferably between 1.8 and 3.0 microns.
In the preferred embodiment, the microparticles have a honeycombed structure or sponge like structure, formed by pores throughout the polymer or the microparticles have a polymeric shell with a honeycombed or sponge like, porous structure. In both cases the pores are filled with gas. These microparticles are formed by spray drying a polymer solution containing a pore forming agent such as a volatile salt as described below.
Ultrasound Contrast Imaging Agents
Examples of fluorinated gases include CF4, CaF^ CJ^e, CsFe, CsFs, C4Fs, C4Fio, and SFe- n-Perfluorobutane (C4Fio) is particularly preferred because it provides an insoluble gas that will not condense at the temperature of use and is pharmacologically acceptable.
The amount of gas contained with the microparticles will depend on the type of gas but is typically between 75-500 ng/mL of administered volume of microparticle suspension. For n-perfluorobutane, the preferred gas content is between 100-400 p.g/mL of administered volume of microparticle suspension and most preferably is between 150-350 ng/mL of administered volume of microparticle suspension. For n-octafluoropropane, the preferred gas content is between 75-375 |j,g/mL of administered volume of microparticle suspension, and most preferably between 120-300 fig/mL of administered volume of microparticle suspension. III. Methods for making Microparticles
The microparticles may be produced by a variety of methods, and are preferably produced by spray drying. A major criterion is that the polymer
must be dissolved or melted with the hydrophobia compound or lipid, prior to forming the microparticle. Solvents
During formation, the polymer is generally dissolved in a solvent. As defined herein, the polymer solvent is an organic solvent that is volatile or has a relatively low boiling point or can be removed under vacuum and which is acceptable for administration to humans in trace amounts, such as methylene chloride. Other solvents, such as ethyl acetate, ethyl formate, ethanol, methanol, dimethyl formamide (DMF), acetone, acetonitrile, tetrahydrofuran (THF), formamide, acetic acid, dimethyl sulfoxide (DMSO) and chloroform also may be utilized, or combinations thereof. In general, the polymer is dissolved in the solvent to form a polymer solution having a concentration of between 0.1 and 60% weight to volume (w/v), more preferably between 0.25 and 30% (w/v) and most preferably between 0.5-10% (w/v).
Microparticles are preferably produced by spray drying by dissolving a biocompatible polymer and lipid in an appropriate solvent, dispersing a pore forming agent as a solid or as a solution into the polymer solution, and then spray drying the polymer solution and the pore forming agent, to form microparticles. As defined herein, the process of "spray drying" a solution of a polymer and a pore forming agent refers to a process wherein the polymer solution and pore forming agent are atomized to form a fine mist and dried by direct contact with hot carrier gases. Using spray dryers available in the art, the polymer solution and pore forming agent may be atomized at the inlet port of the spray dryer, passed through at least one drying chamber, and then collected as a powder. The temperature may be varied depending on the gas or polymer used. The temperature of the inlet and outlet ports can be controlled to produce the desired products.
The size and morphology of the microparticles formed during spray drying is a function of the nozzle used to spray the polymer solution and the pore forming agent, the nozzle pressure, the flow rate of the polymer solution with the pore forming agent, the polymer used, the concentration of the
polymer in solution, the type of polymer solvent, the type and the amount of pore forming agent, the temperature of spraying (both inlet and outlet temperature) and the polymer molecular weight. Generally, the higher the polymer molecular weight, the larger the particle size, assuming the polymer solution concentration is the same.
Typical process parameters for spray drying are as follows: inlet temperature = 30-200°C, outlet temperature = 5-100°C, and polymer flow rate =10-5,000 ml/min.
A gaseous diagnostic agent may be encapsulated by emulsifying the gas with the polymer solution and the pore forming agent prior to spray drying. Alternatively, air filled microparticles can be produced during the spray drying step and subsequently the air replaced with the perfluorocarbon gas by applying a stream of the desired gas to the microparticles, or pulling a vacuum on the microparticles to remove the encapsulated air, then filling with the desired perfluorocarbon gas. A lyophilizer or vacuum chamber may be used if a vacuum step is used to exchange the gas.
Additives to Facilitate Microparticulate Formation
A variety of surfactants may be added during the formation of the microparticles. Exemplary emulsifiers or surfactants which may be used (0.1-15% w/ w polymer) include most physiologically acceptable emulsifiers. Examples include natural and synthetic forms of bile salts or bile acids, both conjugated with amino acids and unconjugated such as
taurodeoxycholate, and cholic acid.
Pore forming agents are included in the polymer solution in an amount of between 0.01% and 90% weight to volume of polymer solution, to increase pore formation. For example, in spray drying, a pore forming agent such as a volatile salt, for example, ammonium bicarbonate, ammonium acetate, ammonium carbonate, ammonium chloride or ammonium benzoate or other volatile salt as either a solid or as a solution in a solvent such as water can be used. The solid pore forming agent or the solution containing the pore forming agent is then emulsified with the polymer solution to create a dispersion or droplets of the pore forming agent in the polymer. This
dispersion or emulsion is then spray dried to remove both the polymer solvent and the pore forming agent. After the polymer is precipitated, the hardened microparticles can be frozen and lyophilized to remove any pore forming agent not removed during the polymer precipitation step. The preferred microparticle is formed using the polymer, poly(lactide-co-glycolide) with a lactide to glycolide ratio of 50:50 and having a weight average molecular weight in the range 20,000-40,000 Daltons, and the phospholipid, diarachidoylphosphatidylcholine ((1,2-diarachidoyl-,s«-glycero-3-phosphocholine (DAPC) ) at a ratio of 5-6.6 % (w DAPC/w polymer). The microparticles are further formulated in a solution of mannitol and TWEEN® 80 and processed to yield a dry powder of microparticles which are backfilled on a lyophilizer with n-perfluorobutane. The dry powder is reconstituted with 5 mL of sterile water prior to use by adding the water to the vial of the dry powder and shaking to yield a suspension of microparticles in isosmotic mannitol. The preferred properties of the suspension are a gas content of 150-350 jug/mL of n-perfluorobutane per administered volume of microparticle suspension, 1.5-2.8 x 109 microparticles/mL of administered volume of microparticle suspension, 30-45mg microparticles/mL of administered volume of microparticle suspension, and a mean particle size in the range 1.8-3.0 microns. IV. Applications for the Microparticles
1. Formulations for Administration to a Patient The microparticles may undergo further processing with excipients to create a dry powder. The excipients provide tonicity or osmolarity or ease of suspendability of the microparticles after reconstitution with a pharmaceutically acceptable carrier prior to administration to a patient. Excipients suitable for providing osmolarity or tonicity are sugars including but not limited to mannitol, dextrose or glucose and salts including but not limited to sodium chloride or sodium phosphate. Excipients suitable for providing ease of suspendability of the microspheres include any pharmaceutically acceptable wetting agent or surfactant including but not
limited to polysorbate 80'(TWEEN* 80), polysorbate 20 (TWEEN® 20), Pluronic or polyethylene glycol. Excipients suitable for providing osmolarity or tonicity or that can be used as wetting agents are described in references such as the Handbook of Pharmaceutical Excipients (Fourth Edition, Royal Pharmaceutical Society of Great Britain, Science & Practice Publishers) or Remingtons: The Science and Practice of Pharmacy (Nineteenth Edition, Mack Publishing Company). The dry powder of microparticles and excipients is created by suspending the microparticles in a solution of excipients. Further size fractionation steps may be used if needed. The microparticles in the solution of excipients are filled into vials or syringes, frozen, and lyophilized to create the dry powder formulation. At the conclusion of the lyophilization step, the microparticles are filled with the perfluorocarbon gas by backfilling the lyophilizer with the perfluorocarbon gas. The vials or syringes are then stoppered or capped and in the case of vials, crimped. This results in a perfluorocarbon headspace in the vial or syringe.
Alternatively, the microparticles can be dry blended with the pharmaceutical excipients and then filled into vials or syringes. The microparticles can be filled with the perfluorocarbon gas by applying a vacuum after loading the vials or syringes on a lyophilizer or in a vacuum chamber. The vials or syringes are then stoppered or capped and in the case of vials, crimped. This results in a perfluorocarbon headspace hi the vial or syringe.
2. Dosage Units
Different size dosage units of microparticles may be used. For example a small dosage unit may contain 25-75 mg of microparticles. An intermediate dosage unit may contain 75-150 mg. A large dosage unit may contain 150-250 mg of microparticles. An extra large dosage unit may contain 250-1000 mg of microparticles.
When the suspension of microparticles is formed following reconstitution, the mass concentration of microspheres hi the suspension typically ranges from 20 to 60 mg/mL. The preferred mass concentration of microspheres in the suspension is 25-50 mg/mL; and the most preferred mass
concentration of microspheres in the suspension is 30 to 45 mg/mL. The preferred concentration of microparticles in the suspension is 1.0-3.5 x 109 microparticles/mL of suspension; and the most preferred concentration of microparticles in the suspension is 1.5-2.8 x 109 microparticles/mL. The microparticles have a preferred mean particle size of less than 8 microns, most preferably in the range 1.8-3.0 microns.
Pharmaceutically acceptable carriers may include water for injection, sterile water, saline, saline containing glycerol, saline containing TWEEN® 20, saline containing TWEEN® 80, isosmotic dextrose (5%), 1A isosmotic dextrose (2.5%), isosmotic mannitol (5%), 1A isosmotic mannitol (2.5%), isotonic mannitol containing TWEEN® 20 and isotonic mannitol containing TWEEN® 80.
Kits for parenteral administration of the microparticles containing the perfluorocarbon gas may be provided. The kit contains at least two components. One component contains a dosage unit of the dry powder contrast agent in a vial or syringe, and the other component contains a pharmaceutically acceptable carrier in a vial or syringe. Prior to administration to a patient, the pharmaceutically acceptable carrier is added to the dosage unit of the dry powder contrast agent to form a suspension of gas filled microparticles that are usable as an ultrasound imaging contrast agent in diagnostic imaging by any route of administration.
4. Vials or Containers for microparticles
No specific vial or syringe or connection systems are required for the kits; conventional vials, syringes and adapters may be used with the microparticles. The only requirement for a vial is a good seal between the stopper and the container. The quality of the seal, therefore, becomes a matter of primary concern; any degradation of seal integrity could allow undesirables substances to enter the vial or allow the gas to escape. In addition to assuring sterility, vacuum retention is essential for products stoppered at reduced pressures to assure safe and proper reconstitution. As to the stopper, it may be a compound or multicomponent formulation based on an elastomer, such as poly (isobutylene) or "butyl rubber" and must be
impermeable to the gas used. The vial size is selected depending on the total dosage of dry powder in the vial. Preferred vial sizes are 5mL, 10 mL, 20 mL and 30 mL. The syringe size is selected depending on the total dosage of dry powder in the syringe. Preferred syringe sizes are 5mL, lOmL, 20mL, and 50 mL syringes.
5. Diagnostic Applications
The microparticle compositions may be used in a many different diagnostic applications including ultrasound imaging, magnetic resonance imaging, fluoroscopy, x-ray, and computerized tomography.
In the preferred embodiment, the microparticles are used in ultrasound procedures such as blood vessel imaging and echocardiography including but not limited to ventricular chamber imaging, myocardial blood flow assessment, myocardial blood volume assessment, diagnosis of coronary artery disease, and ejection fraction assessment.
The microparticles may be used hi vascular imaging, as well as in applications to detect liver and renal diseases, in detecting and characterizing tumor masses and tissues, and in measuring peripheral blood velocity. The microparticles also can be linked with ligands that minimize tissue adhesion or that target the microparticles to specific regions of the body in vivo. General Method of obtaining images
The microparticles in dry powder form are reconstituted with a pharmaceutically acceptable carrier prior to administration, then an effective amount for detection is administered to a patient using an appropriate route, by injection into a blood vessel (such as intravenously (i.v.) or intra-arterially (i.a.)), or orally. The microparticle composition may be administered intravenously to the patient as a bolus injection or short infusion (less than 30 minutes). Preferably the injection is administered over a time period ranging from 15 seconds to 20 minutes, most preferably ranging from 30 seconds to 15 minutes. Typically, a dose ranging from 0.025 to 8 mg/kg body weight per injection is administered intravenously to a patient, preferably the dose ranges from 0.05 to 4 mg/kg.
For diagnostic ultrasound applications, energy is applied to at least a portion of the patient to image the target tissue. A visible image of an
internal region of the patient is then obtained, such that the presence or absence of diseased tissue can be ascertained. Ultrasonic imaging techniques, including second harmonic imaging and gated imaging, are well know in the art and are described, for example, in Uhlendorf, IEEE Transactions on Ultrasonics, Ferroelectrics. and Frequency Control. 14(l):70-79 (1994) and Sutherland, et al. Journal of the American Society of Echocardiography. 7(5):441-458 (1994), the disclosures of each is hereby incorporated herein by reference in its entirety.
Ultrasound waves may be applied with a transducer. The ultrasound can be pulsed or it may be continuous, if desired. Thus, diagnostic ultrasound generally involves the application of echoes, after which, during a listening period, the ultrasound transducer receives reflected signals. Harmonics, ultraharmonics or subharmonics may be used. The second harmonic mode may be beneficially employed, in which the 2x frequency is received, where x is the incidental frequency. This may serve to decrease the signal from the background material and enhance the signal from the transducer using the imaging agents, which may be targeted to a desired site, for example, blood clots. Other harmonic signals, such as odd harmonics signals, for example, 3x or 5x, would be similarly received using this method. Subharmonic signals, for example, x/2 and x/3, may also be received and processed so as to form an image.
In addition, Power Doppler or Color Doppler may be applied. In the case of Power Doppler, the relatively higher energy of the Power Doppler may resonate the vesicles. This can create acoustic emissions which may be in the subharmonic or ultraharmonic range or in some cases, in the same frequency as the applied ultrasound.
Specific Imaging Applications
The microparticles described herein can be used in both cardiology and radiology applications. For cardiology applications, the microparticle compositions are administered to a patient and the patient is scanned using an ultrasound machine to obtain visible images of the cardiovascular region. Optionally the microparticle composition is administered in combination with a pharmacological stressor or a physical stressor. Suitable
pharmacological stressors include a coronary vasodilator such as dipyridamole or adenosine, an inotropic agent (i.e. increases the strength of heart contraction) such as dobutamine or a chronotropic agent (i.e. increases the frequency of contraction) such as dobutamine. Suitable physical stressors include physical exercise, such as by using a treadmill or a stationary bicycle.
For radiology applications, the microparticle compositions are administered to a patient and the patient is scanned using an ultrasound machine to obtain visible images of the region of a patient to be examined.
The microparticles can be used to assess the function of the cardiovascular system as well as to assess myocardial blood flow or myocardial blood volume or to diagnose coronary heart disease (coronary artery disease). For example the microparticles can enhance images of the ventricular chambers and thus assist in regional cardiac function analysis through wall motion analysis and assist in global cardiac function through ejection fraction measurements. The microparticles can also be used to assess myocardial blood flow to differentiate functioning cardiac tissue from either ischemic (blood flow deficient) cardiac tissue or infarcted (dead) cardiac tissue. The contrast signals detected in the myocardium can be used as an estimate of myocardial blood volume since ultrasound contrasts agents reside intravascularly following intravenous administration. The absence or reduction in contrast intensity or image brightness in a particular myocardial region over time is indicative of reduced blood flow (i.e. a defect).
Most often unless the patient has severe coronary heart disease, blood flow to the various regions of the heart as assessed by techniques such as ultrasound contrast will appear normal. In order to detect blood flow abnormalities hi patients without severe heart disease or to detect smaller myocardial blood flow defects, it is necessary to increase the blood flow requirements to the heart by inducing a state of stress. Stress can be induced by having the patient exercise or by administering a pharmacological compound such as a vasodilator, an inotropic agent or a chronotropic agent. During exercise or pharmacological stress, blood flow defects can be more easily detected because the ability to increase blood flow is reduced in
regions supplied by coronary arteries with stenosis. A comparison of ultrasound images of the myocardium following ultrasound contrast agent administration can be made both in the pre-stress state (i.e. rest state) and in the stress state. A myocardial region without enhanced brightness found during stress imaging but not during rest imaging is indicative of ischemia. A myocardial region without enhanced brightness found during stress imaging and during rest imaging is indicative of an infarct.
In one embodiment, the myocardial blood flow can be measured by
administering a first injection of a microparticle composition to a patient,
scanning the patient using an ultrasound machine imaging to obtain a
visible image of the cardiovascular region, (3) inducing a state of stress in
the patient using a pharmacological stressor or exercise, (4) administering a
second injection of the microparticle composition and continuing the
scanning, and (5) assessing differences in the images obtained hi steps (2)
and (4) either visually or using quantitative image analysis.
For radiology applications, the microparticles may be used to improve the capabilities of ultrasound imaging for radiology indications, including imaging of the kidney, liver and peripheral vascular disease, increasing the visibility of blood flow and blood flow patterns and by improving the detection of small lesions or structures deep within the body. The microparticles can be used for both macrovascular and microvascular indications. In macrovascular indications (the diagnosis of disease states and conditions of major arteries and veins of the body), the microparticles may aid in the detection of strokes and pre-stroke conditions through visualization of intracranial blood vessels, detecting atherosclerosis in large vessels such as the carotid arteries by assessing the degree of carotid artery stenosis, vascular graft patency and peripheral vascular thrombosis. For microvascular indications (the diagnosis of disease states and through analysis of patterns of small vessel blood flow), the microparticles may aid in identifying lesions, tumors or other diseases in the liver (e.g. adenomas or hemangiomas), kidneys, spleen (e.g. splenic artery aneurysms), breasts and ovaries and in other tissues and organs.
Diseased tissues in a patient may be diagnosed by administering the microparticle composition to the patient and scanning the patient using the ultrasound imaging to obtain visible images of any diseased tissues in the patient. Diseased tissues may manifest as a region of enhanced brightness or a region that does not show enhanced brightness.
Enhanced Images obtained using Microparticle compositions
The microparticles produce an enhanced image following administration. Enhanced images may be manifested by an increase in brightness in the image compared to when no ultrasound contrast agent is administered or by substantial elimination of artifacts in the image. Thus, hi connection with ultrasound imaging of the cardiovascular region, including the heart tissue and the vasculature associated therewith, an enhanced image may be manifested, for example, by increased brightness in the image of the cardiovascular region and/or a substantial elimination hi the occurrence of artifacts in the image of the cardiovascular region. The images following a single administration of the agent last for between 10 seconds and 60 minutes. The images preferably last for between 20 seconds and 30 minutes and most preferably last for between 30 seconds and 20 minutes, hi a preferred embodiment, the ultrasound imaging is enhanced hi the ventricular chambers for more than five minutes or in the myocardium for more than one minute.
The increase hi brightness in the image may be assessed either visually by the naked eye or using quantitative image analysis. With particular reference to the gray scale (about 0 to about 255 VDUs or gray levels) identified above, there is preferably an increase hi the level of brightness of at least about 10 VDUs (gray levels). More preferably, the image has an increased brightness of greater than about 10 VDUs, for example, about 15,20,25, 30, 35,40,45, 50, 55, 60, 65, 70,75, 80, 85, 90, 95, or 100 VDUs. In some embodiments, the increased brightness is greater than about 100 VDUs, for example, about 105,110,115,120,125,130,135, 140,145, or 150 VDUs. In other embodiments, the increased brightness is greater than about 150 VDUs, for example, about 155,160,165,170,175, 18-, 185,190, 195, or 200 VDUs. Alternatively, the increased brightness is
greater than about 200 VDUs, for example about 205,210, 215, 220,225, 230,235,240,245,250, or 255 VDUs.
The methods and compositions described above will be further understood with reference to the following non-limiting examples.
Acetic acid, ammonium bicarbonate, mannitol USP, and polysorbate 80 (no animal-derived components) were purchased from Spectrum Chemicals, Gardena, CA. Polymer (poly(lactide-co-glycolide) (PLGA) (50:50)) and diarachidoylphosphatidylcholine (l,2-diarachidoyl-5«-glycero-3-phosphocholine (DAPC)) were obtained from Boehringer Ingelheim (Ingelheim, Germany) and Avanti (Alabaster, AL), respectively. Methylene chloride was purchased from EM Science (EMD Chemicals, Gibbstown, NJ). Vials (30 ml tubing vials) and stoppers (20 mm, gray, single-vent, Fluro-Tec) were obtained from West Pharmaceutical Services (Lionville, PA). n-Perfluorobutane (DFB) gas was purchased from F2 Chemicals Ltd, Lancashire, UK. Analytical Methods
Quantitation of Mass Concentration of Microparticles
The mass concentration of microparticles in vials was quantitated using ICP-MS (inductively coupled plasma - mass spectrometry). The amount of polymer in the microparticles was determined by analyzing for tin by ICP-MS. The amount of polymer present hi the microparticles was determined based on a comparison of the amount of tin found in the microparticles to the amount of tin found hi the specific lot of polymer used to make the microparticles. The amount of phospholipid in the microparticles was determined by analyzing for phosphorus by ICP-MS. The amount of phosphorus present in the microparticles was determined based on the amount of phosphorous found hi the microparticles in comparison to the amount of phosphorus hi the phospholipid itself. The microparticle mass per mL of suspension was calculated by adding the amount of polymer and phospholipid per vial and then dividing that sum by the reconstitution volume (5 mL).
Particle Size Analysis
A sample of reconstituted microparticles was added to an electrolyte solution, and the resulting suspension analyzed for particle size and microparticle concentration using a Coulter Multisizer II fitted with a 50 urn aperture tube.
Gas Content of Microparticles
Vials of the dry powder were reconstituted with 5mL water and shaken to create the microparticle suspension. The resulting suspension was analyzed for DFB content by withdrawing a set of 0.3 mL aliquots through the stopper using a needle and syringe. These aliquots were injected into sealed headspace vials. The headspace vials equilibrated for at least 10 hours at room temperature. Samples were then heated then heated to 45°C for 20 minutes hi a headspace sampler oven. The headspace gas above the suspension was analyzed by gas chromatography using a purged packed inlet and a flame ionization detector. Quantitation was performed using an area based single point calibration.
The GC system parameters and temperature program are listed in Tables 1 and
Example 1: Production of Microparticles for Use as an Ultrasound Contrast Agent
.An organic solution was prepared by dissolving 176 g of PLGA, 10.6 g of diarachidoylphosphatidylcholine (l,2-diarachidoyl-.y«-glycero-3-phosphocholine (DAPC)), and 2.26 g of acetic acid in 5.88 L of methylene chloride at 25°C. An aqueous solution composed of 68.5 g of ammonium bicarbonate dissolved in 338 ml of water for injection was added to the organic solution and homogenized for 10 minutes at 4310 RPM in a 10L homogenization tank using a rotor-stator emulsifying mixer.
The resulting emulsion was spray dried using nitrogen as both the atomizing and drying gas. Emulsions were spray dried on a bench top, spray dryer using an air-atomizing nozzle from Spraying Systems (Wheaton, IL) and a glass drying chamber/cyclone system from Buchi (Brinkmann, Westbury, NY). Spray drying conditions were as follows: 40 ml/min emulsion flow rate, 30 L/min atomization gas rate, 46 kg/hr drying gas rate, and 12°C outlet temperature.
The spray dried product was further processed through dispersion, freezing, and lyophilization steps. An aqueous vehicle was prepared by dissolving 140 g of mannitol and 4.10 g of polysorbate 80 in 5.0 L of water. The spray dried microparticles were dispersed in the vehicle at a concentration of 25 mg/ml. The dispersion was deaggregated using a stainless steel, 800 series, flow-cell sonicator from Misonix Incorporated (Farmingdale, NY) and sieved through a 10" diameter vibratory sieve (RBF-
10) from Vorti-Siv (Salem, OH). The sonicator was jacketed at 4°C to prevent heating of the dispersion. The dispersion was sieved through 25 um and 20 jam screens in series at 150 mL/min. The sieved dispersion was filled into vials (10 ml fill in 30 ml vials), partially stoppered, and frozen by immersion in liquid nitrogen.
Following freezing, the vials were lyophilized. At the conclusion of lyophilization, the chamber was isolated, and n-perfluorobutane (DFB) was backfilled into the vials to a pressure of-5 kilopascals prior to stoppering.
The dry powder was reconstituted with 5 mL of sterile water prior to use by adding the water to the vial of the dry powder and shaking to yield a suspension of microparticles in isosmotic mannitol. The suspension contained 2.2 x 109 microparticles/mL of suspension, and 37 mg microparticles/mL of suspension and the microparticles had a mean particle size of 2.2 microns. Example 2: Rate of Gas Leakage from the Microparticles
The rate of gas leakage from two separate batches (Batch 1 and Batch 2) of microparticles as produced by the methods of Example 1 was assessed using gas chromatography (GC) as described in the analytical methods sections. A third lot of microspheres (Batch 3) was produced similar to the method of example 1, however, the phospholipid, diarachidoylphosphatidylcholine (1,2-diarachidoyl-.si«-glycero-3-phosphocholine (DAPC)) was omitted during the production of the microparticles. Table 3: Gas Content and Rate of Gas Leakage for Microparticles
The microparticles which contained DAPC lost approximately 10% of the starting gas content after 70 minutes whereas the microparticles which did not contain DAPC lost 87% of the starting gas content. Additionally, the microparticles which contained DAPC had a higher starting initial gas content relative to the microparticles without the DAPC. This indicates that the inclusion of DAPC is important to the formation of the internal porous structure of the microparticles during spray drying as well on retention of gas within the microparticles.
The total duration of intended use of an ultrasound contrast agent following administration to a subject is generally on the order of 30 seconds to 60 minutes depending on the type of cardiology or radiology ultrasound examination conducted. Thus gas loss from the microparticles containing the lipid DAPC is estimated to be insignificant over the period of the ultrasound examination
Example 3: Cardiac Image Enhancement as a Function of Microparticle Dose
Microparticles as produced by the method in Example 1 were studied in healthy human adults. The dry powder was reconstituted prior to use by adding 5 mL of sterile water to the vial and shaking the vial ten times. The final concentration of microspheres hi the resulting suspension was approximately 37 mg/mL. Subjects received a single dose of either 0.5mg/kg, 2.0mg/kg or 4.0 mg/kg body weight. Subjects underwent transthoracic ullrasound imaging using continuous harmonic imaging (frame rate 15 Hz and transducer frequency 2.1/4.2 MHz). Images were visually assessed for intensity and duration of enhancement
The duration of enhancement in the ventricular chamber exceeded 9 minutes at both the 2 mg/kg and 4 mg/kg doses. The contrast effect was still apparent in 13 out of 15 of the subjects at these two doses when the subjects were re-imaged at 30 minutes, indicating the long duration of enhancement provided by the microparticles.
The duration of ventricular chamber enhancement is summarized in the Table 4.
Table 4: Duration of Left Ventricular Image Enhancement
Example 4: Comparison of Microparticles to Commercial Product for Assessing Cardiac Images
A comparative cardiac ultrasound imaging study was conducted in two adult men matched for body weight and cardiac function. The first subject received a single administration of microparticles as produced by the method of Example 1. The dry powder was reconstituted prior to use by adding 5 mL of sterile water to the vial and shaking the vial ten times. The final concentration of microspheres in the resulting suspension was approximately 37 mg/mL and the gas content of the suspension was approximately 250 ug/mL suspension. The first subject received a dose of 4mg microparticle/kg which corresponds to a gas dose of 27ug/kg body weight. The second subject received a single dose of the marketed ultrasound contrast agent, OPTISON® (Amersham Health) which contains perfluoropropane containing albumin microspheres. The two subjects received the same total amount of gas (27ug/kg body weight) which is the acoustically active component. The two subjects underwent transthoracic ultrasound imaging using continuous harmonic imaging (frame rate 15 Hz and transducer frequency 2.1/4.2 MHz). Images were visually assessed for intensity and duration of enhancement.
The duration of ventricular chamber enhancement and myocardial enhancement is summarized in Table 5.
Table 5: Duration of Image Enhancement with Different Ultrasound
Contrast Agent and
Dose of Gas Administered (jug/kg)
Duration of Ventricular
Duration of Myocardial Enhancement (seconds)
Example #1 Microparticles (27ug/kg body weight)
OPTISON® (27ug/kg body weight)
The.microparticles produced using the method described in Example 1 provide enhanced images of both the ventricular chambers and the myocardium which are significantly longer than OPTISON® and which are of appropriate duration to conduct a complete cardiac exam by ultrasound.
Example 5: Assessment of Myocardial Blood Flow to Assess Ischemia Using Microparticle Formulations
Microparticles produced as per the method in Example 1 were administered to a subject being evaluated for coronary heart disease. The subject received two injections of the microparticles separated by 60 minutes. The first injection of the microparticles ("rest injection", 1.7 mg/kg) was used to assess the myocardium at rest. Prior to the second injection of the microparticles, the subject was pharmacologically stressed using the coronary vasodilator, dipyridamole (0.56 mg/kg). After the induction of stress, the subject received a second injection of the microparticles ("stress injection" 1.3 mg/kg) to assess the myocardium
The comparison of the rest and stress images over time post administration of the microparticles for the subject indicate a region of the myocardium which has minimal increase in image enhancement and this region becomes larger in size following the induction of the stress. This
indicates the zone of myocardial tissue has both infarcted and ischemic components. The detection of ischemia was confirmed using an alternate diagnostic technique, nuclear imaging. Rest and stress nuclear perfusion were conducted following the administration of 99Tc (MIBI) and the subject was imaged using a commercial gamma counter. The defects noted on the ultrasound rest and stress images were confirmed on the rest and stress nuclear perfusion images.
1. A formulation characterized in providing enhanced ultrasound contrast images, wherein the said formulation comprises microspheres comprising a poly(hydroxy acid) or copolymer or blend thereof and a hydrophobic compound wherein the microspheres are porous spheres with a honeycombed structure or sponge-like structure and having incorporated therein a perfluorocarbon that is a gas at body temperature, and the hydrophobic compound is a lipid incorporated with the polymer at a ratio of between 0.01 and 30% (weight lipid/weight polymer).
wherein the dosage formulation comprises a dose of microspheres effective to provide enhanced ultrasound images for more than one minute in the myocardium when the microspheres are administered intravenously, and
wherein the formulation can be reconstituted to yield a suspension having a microsphere concentration ranging from 1.0 x 109 to 3.5 x 109 microspheres/mL of suspension or a microsphere mass concentration ranging from 25 to 50 mg microspheres/mL suspension.
2. The formulation as claimed in claim 1 in the form of a dry powder of microspheres which can be reconstituted with sterile water.
3. The formulation as claimed in claim 1, wherein the microspheres are reconstituted with sterile water prior to use to form a suspension having a microsphere concentration ranging from 1.0 x 109 to 3.5 x 109 microspheres/mL of suspension or a microsphere mass concentration ranging from 25 to 40 mg microspheres/mL suspension.
4. The formulation as claimed in claim 3, forming a suspension having a microsphere concentration ranging form 1.5 x 10 to2.8 x109 microspheres/mL of suspension or a microsphere mass concentration ranging from 30 to 45 mg microsphere/mL suspension.
5. The formulation as claimed in claim 1 or 3 wherein the microspheres have a mean particle size of less than 8 microns.
6. The formulation as claimed in claim 5, wherein the microspheres have a mean particle size ranging from 1.9 to 2.6 microns.
7. The formulation as claimed in claim 1 or 5, wherein the gas is selected from the group consisting of CF4, C2F4, C2F6, C3F6, C3F8, C4F8, C4F10.
8. The formulation as claimed in claim 7, wherein the gas is n-perfluorobutane (C4F10) provided in an amount between 75 and 500 µg/mL of administered volume of microsphere suspension.
9. The formulation as claimed in claim 8 wherein the n-perfluorobutane (C4F10) is provided in an amount between 100 to 400 µg/mL of administered volume of microsphere suspension.
10. The formulation as claimed in claim 9 wherein the n-perfluorobutane (C4F10) is provided in an amount between 150 and 350 µg/mL of administered volume of microsphere suspension.
11. The formulation as claimed in claim 7, wherein the gas is n-octafluoropropane (C3F8) provided in an amount between 75 and 375 ug/mL of administered volume of microsphere suspension.
12. The formulation as claimed in claim 11 wherein the n-octafluoropropane (C3F8) is provided in an amount between 120 and 300 µg/m of administered volume of microsphere suspension.
13. The formulation as claimed in claim 1 or 5 wherein the microsphere is formed of a synthetic polymer selected from the group consisting of poly(hydroxy acids), polyanhydrides, polyorthoesters, polyamides, polycarbonates, polyalkylenes, polyalkylene glycols, polyalkylene oxides, poly(valeric acid), poly(lactide-co-caprolactone), and copolymers and blends thereof.
14. The formulation as claimed in claim 1 wherein the lipid is a phospholipid selected from the group consisting of dioleoylphosphatidylcholine (DOPC), dimyristoylphosphatidylcholine (DMPC), dipentadecanoylphosphatidylcholine (DPDPC), dilauroylphosphatidylcholine (DLPC), dipalmitoylphosphatidylcholine (DPPC),
distearoylphosphatidylcholine (DSPC), diarachidoylphosphatidylcholine (DAPC), dibehenoylphosphatidylcholine (DBPC), ditricosanoylphosphatidylcholine (DTPC), dilignoceroylphatidylcholine (DLGPC), and phosphatidylethanolamines.
15. The formulation as claimed in claim 14, wherein the polymer is poly (lactide-co-glycolide) with a lactide to glycolide ratio of 1:1 and a weight average molecular weight ranging from 20 to 40 kDa, and wherein the lipid is diarachidoylphosphatidylcholine incorporated with the polymer at a ratio of between 5 and 6.6 % (weight lipid/weight polymer).
16. The formulation as claimed in claim 1 or 5 wherein the microsphere is in the form of dry powder.
17. The formulation as claimed in claim 16 wherein the vial or syringe optionally comprises one or more excipients selected from the group consisting sugars, salts, and surfactants.
18. The formulation as claimed in claim 1 or 5 as and when used in a kit comprising a vial or syringe of dry microspheres and a vial or syringe of solution for resuspending the microspheres.
19. A method for making a formulation for ultrasound contrast imaging as claimed in claim 1 comprising:
suspending microspheres comprising a poly(hydroxy acid) or copolymer or blend
thereof and a hydrophobic compound in a solution optionally including excipients,
placing the suspension into a vial or syringe,
freezing the suspension,
lyophilizing the vial to create a dry powdered formulation in the vial or syringe, and
backfilling the lyophilizer with a perfluorocarbon gas,
to produce a formulation as defined by any one of claims 1 to 18.
|Indian Patent Application Number||7358/DELNP/2006|
|PG Journal Number||44/2011|
|Date of Filing||06-Dec-2006|
|Name of Patentee||ACUSPHERE, INC|
|Applicant Address||500 ARSENAL STREET, WATERTOWN, MA 02472, USA|
|PCT International Classification Number||A61K 49/22|
|PCT International Application Number||PCT/US2004/017813|
|PCT International Filing date||2004-06-04|