Patent Application
20240299547
The present invention relates to ultrasound-responsive polypeptide particles. The particles are useful in delivering drugs or diagnostic agents to target sites in the body. They are also useful themselves in the treatment or prevention of disease.
Ultrasound-responsive particles have been used for some time to assist delivery of therapeutic or diagnostic agents to the body. For instance, drug can be co-administered with microbubbles, which act as cavitation nuclei. The action of ultrasound on the microbubbles leads to a short burst of microstreaming caused by the cavitation effects. This can increase the delivery of the drug at the target site. Administration of ultrasound can also improve the permeability of physiological barriers such as the vasculature walls, and thereby increase drug delivery.
However, microbubbles provide only a very short duration of action, with cavitation lasting for no more than about 30 seconds. Moreover, the bubbles themselves are too large to exit the vasculature, which limits their effectiveness in delivery to the extravascular space.
Nanoparticulate cavitation agents have also been described (WO 2015/075442) which have the benefit of longer duration of action and are small enough to pass into the extravascular space. The particles described are formed by seed polymerisation to generate cup-shaped plastic particles, capable of holding a gas bubble in the cavity of the cup. These particles have been found to disseminate throughout a tumour mass, for example, on exposure to ultrasound for 30 seconds. However, the particles described are plastic and are non-biodegradable.
There is therefore a need for new ultrasound-responsive particles and/or new methods for ultrasound-responsive delivery of drugs and diagnostic agents to a target site, which address the problems discussed above.
The present inventors have developed biodegradable, ultrasound-responsive particles which generate inertial cavitation on response to ultrasound and can be made at submicron sizes. The particles have a good duration of action, having been found to generate cavitation for a period of around 10 minutes following ultrasound exposure. If desired, they can be manufactured at a size which is small enough to pass through the walls of the vasculature. Therefore, the particles themselves, and any co-administered therapeutic or diagnostic agent, can be effectively delivered to target sites outside of the vasculature (e.g. to tumours). The particles are also highly stable. The particles therefore provide an effective means of generating inertial cavitation in a therapeutic or diagnostic setting.
The present invention therefore provides the following aspect (1):
1. A polypeptide particle for inducing cavitation on exposure to ultrasound, the particle comprising:
The particles are useful in any method which involves generation of inertial cavitation. For example, they may be used as cavitation agents for therapeutic use, or to deliver drugs or diagnostics which are co-administered with the particles.
A particular advantage of the particles of the invention is that they can be effectively administered transdermally. Application of the particles of the invention to the skin, followed by applying ultrasound, generates an inertial cavitation effect sufficient to deliver the particles transdermally.
Also provided are the following aspects:
2. A polypeptide particle according to aspect 1, wherein the polypeptide shell comprises cross-linked polypeptide particles.
3. A polypeptide particle according to aspect 1 or aspect 2, wherein the polypeptide shell comprises one or more non-immunomodulatory polypeptides, preferably the polypeptide shell comprises at least 95% by weight non-immunomodulatory polypeptides.
4. A polypeptide particle according to any one of the preceding aspects, wherein the polypeptide shell consists essentially of one or more human blood proteins, preferably it is a human serum albumin shell.
4. A polypeptide particle according to any one of the preceding aspects, wherein the particle size is in the range of from 100 nm to 1000 nm, preferably from 200 nm to 700 nm.
5. A polypeptide particle according to any one of the preceding aspects, wherein the cross section of at least one surface indentation forms a conic section.
6. A polypeptide particle according to any one of the preceding aspects, wherein at least one surface indentation has a depth of at least 10 nm, and/or an opening size of at least 50 nm.
7. A polypeptide particle according to any one of the preceding aspects, wherein the particle comprises one or two indentations having an opening size which is 20% or more of the size of the particle.
8. A polypeptide particle according to any one of the preceding aspects, wherein the polypeptide shell is conjugated to one or more ligands selected from a peptide, a protein, a sugar, a nanoparticle and a nucleic acid.
9. A polypeptide particle according to any one of the preceding aspects, which particle is capable of generating inertial cavitation when the particle is suspended in water and subject to ultrasound at 1.2 MPa and 265 kHz, preferably the particle is capable of generating inertial cavitation when the particle is suspended in water and subject to ultrasound at 1 MPa and 500 kHz, more preferably the particle is 450 nm or less in size and is capable of generating inertial cavitation when the particle is suspended in water and subject to ultrasound at 1.5 MPa and 500 kHz.
10. A polypeptide particle according to any one of the preceding aspects, wherein the particle comprises:
As used herein, an ultrasound-responsive particle is a particle that produces a response, typically a cavitation response, when exposed to ultrasound. The particles of the invention which are suitable for inducing (i.e. capable of inducing, or adapted to induce) cavitation on exposure to ultrasound are ultrasound-responsive particles as described herein.
Cavitation occurs when a bubble in a fluid, e.g. a bubble associated with a particle of the invention, changes size or shape due to an external input, typically acoustic pressure. Typically, the particle generates an inertial cavitation response when exposed to ultrasound. Inertial cavitation is the effect which occurs when a bubble in a fluid, e.g. a bubble associated with a particle of the invention, grows following exposure to the acoustic pressure, and subsequently collapses. The bubble collapse may cause a shock wave and/or microstreaming in the surrounding fluid, and is accompanied by broadband (as opposed to tonal) acoustic emissions. Inertial cavitation may be detected by single- or multi-element detectors, including conventional hand held ultrasound arrays used for common medical diagnostics. Inertial cavitation may be assessed as the presence of broadband noise at a level clearly discernible from the background (e.g. at least 3 times the background root-mean-square noise) after excluding any tonal components. Particles are considered to generate an inertial cavitation response if broadband noise (e.g. measured as described above) is present on application of ultrasound (e.g. at 1.2 MPa and 265 kHz) to a suspension of particles in water. Preferably, the particles will generate an inertial cavitation response (i.e. broadband emission) when suspended in water and subject to ultrasound at 1 MPa and 500 kHz. More preferably, the particles will generate an inertial cavitation response (i.e. broadband emission) when suspended in water and subject to ultrasound at 1.5 MPa and 500 kHz. Inertial cavitation is demonstrated, for example as shown in
Particle size as defined herein is the maximum distance across a particle, i.e. the diameter in the case of a spherical particle. Although the particles defined herein are not necessarily spherical in shape, the particle size may be referred to herein as a particle diameter and both terms have the same meaning.
Particle size in the case of a composition containing a plurality of particles according to the invention is defined as the mean particle size. Mean particle size within a composition may be measured by a variety of techniques known to the skilled person (Malvern Nanosight, Beckman Coulter particle size, dynamic light scattering (DLS)). Typically the mean particle size is defined as the hydrodynamic diameter, as measured by dynamic light scattering (DLS). Particle size of an individual nanoparticle (s in
As used herein, an indentation is a surface feature causing a cavity or depression to arise in the surface of the particle. Indentations are also referred to herein as surface indentations. Typically, an indentation is capable of entrapping or holding a gas bubble. The indentation has a depth depicted as d in
A polypeptide particle which has one or more surface indentations typically refers to a particle wherein the surface indentations are formed in the polypeptide shell.
The shell thickness is the average thickness of the polypeptide shell and can be determined by SEM or TEM.
As used herein, the term “polypeptide” refers to a full-length protein, a portion of a protein, or a peptide characterized as a string of amino acids. Typically a polypeptide comprises at least 25, or 30, or 35, or 40, or 45, or 50 or 55 or 60 amino acids. For example, a polypeptide may contain 100 or more amino acids. As used herein, the term “protein” refers to a full length protein or a fragment of a protein.
The terms “fragment”, “fragment of a protein” or “fragment of a polypeptide” as used herein refer to a string of amino acids or an amino acid sequence typically of reduced length relative to the or a reference protein or polypeptide and comprising, over the common portion, an amino acid sequence identical to the reference protein or polypeptide. In some cases the fragments referred to herein may be between 8 or 9 and 20, or 25, or 30, or 35, or 40, or 45, or 50 amino acids.
A polypeptide shell refers to a shell which is formed from polypeptide. Typically the shell is a polypeptide shell which substantially consists of one or more polypeptides. A polypeptide shell which substantially consists of one or more polypeptides comprises at least 90% by weight, at least 95% by weight, preferably at least 98%, e.g. at least 99%, at least 99.5 or at least 99.9% by weight polypeptide. Typically, the shell comprises cross-linked polypeptide particles. Cross-linking the polypeptide particles enables a stable shell structure to be formed. Thus, the particles do not require any separate substrate onto which polypeptide is coated, and the polypeptide itself forms the basis of the particle. This can have the advantage of improved biodegradeability.
Reference herein to a polypeptide shell which comprises a particular type of polypeptide implies that the said polypeptide is cross-linked within the shell structure. For instance, a polypeptide particle which comprises a non-immunomodulatory protein such as a human blood protein comprises said protein cross-linked within the polypeptide shell, i.e. cross-linked to polypeptide particles in the shell (which may be other non-immunomodulatory proteins such as human blood proteins in the shell, or to other types of polypeptide particles in the shell). Similarly, a polypeptide particle which comprises serum albumin, insulin, globulin and/or haemoglobin, comprises a polypeptide shell in which the serum albumin, insulin, globulin and/or haemoglobin protein are cross-linked, i.e. cross-linked to other polypeptide particles in the shell.
The term volatile as used herein indicates that a substance has a vapour pressure at 25° C. greater than that of water (which has a vapour pressure about 3 kPa) at the same temperature. Typically, a volatile substance, or a volatile component, is capable of vaporising at room temperature (25° C.). A volatile component as used herein is thus a liquid, typically an organic solvent, which has a vapour pressure of at least 3 kPa, preferably at least 3.5 kPa, for example at least 5 kPa, at least 10 kPa or at least 15 kPa at 25° C.
Non-volatile indicates that a substance does not or substantially does not vaporise at room temperature (25° C.). Non-volatile components are thus typically liquids, e.g. oils, which have a vapour pressure at 25° C. which is no more than that of water (which has a vapour pressure about 3 kPa) at the same temperature. A non-volatile component as used herein typically has a vapour pressure at 25° C. of less than 3 kPa, preferably less than 2.5 kPa, e.g. less than 2 kPa.
As described herein, the particles are useful in methods of therapy or diagnosis of a subject. The subject is a human or animal subject. In one aspect, the subject to be treated is a mammal, in particular a human. However, it may be non-human. Preferred non-human animals include, but are not limited to, primates, such as marmosets or monkeys, commercially farmed animals, such as horses, cows, sheep or pigs, and pets, such as dogs, cats, mice, rats, guinea pigs, ferrets, gerbils or hamsters.
The term “treatment” as used herein includes therapeutic and prophylactic treatment. Administration is typically in a “prophylactically effective amount” or a “therapeutically effective amount” (as the case may be, although prophylaxis may be considered therapy), this being sufficient to result in a clinical response or to show clinical benefit to the individual, e.g. an effective amount to prevent or delay onset of the disease or condition, to ameliorate one or more symptoms, to induce or prolong remission, or to delay relapse or recurrence.
An immunomodulatory polypeptide (or immunomodulatory protein) is a polypeptide (or protein) which induces an immune response on administration to a subject. Typically, the subject is a human and the protein is one which induces an immune response on administration to a human subject. Typically, administration of an immunomodulatory polypeptide (or immunomodulatory protein) causes the subject to raise antibodies against the polypeptide (or protein), although alternative immune responses may arise as well as or instead of raising antibodies.
A non-immunomodulatory polypeptide (or non-immunomodulatory protein) is a polypeptide (or protein) which does not give rise to an immune response on administration. Typically, such a polypeptide or protein is one which occurs naturally within the subject. An example of a non-immunomodulatory protein in the case of a human subject is human serum albumin. More generally, human blood proteins are examples of non-immunomodulatory proteins, including insulin, globulin and haemoglobin.
The polypeptide particles of the invention are ultrasound-responsive particles. The particles are capable of generating a cavitation response when exposed to ultrasound in the presence of a fluid. Typically they generate inertial cavitation. Therefore, when the particles of the invention are present in a fluid, for example formulated into a gel or lotion, or present within the body, exposure to ultrasound will lead to inertial cavitation within that fluid.
The particles have one or more indentations (i.e. surface depressions, or cavities), which provides their ultrasound-responsive properties. Without being limiting on the invention, it is currently understood that the indentations or cavities in the particle surface are able to trap or hold a gas bubble. On exposure to ultrasound, the gas bubble grows and then collapses, causing an inertial cavitation effect. Thus, the particles have one or more indentations capable of causing inertial cavitation on exposure to ultrasound. In one aspect, the invention provides particles as described herein comprising a gas bubble entrapped at an indentation on the particle. The gas bubble may comprise air or oxygen, for example.
Typically, the particles are capable of causing inertial cavitation when suspended in water and subject to ultrasound at 1.2 MPa and 265 kHz. As described above, the ability of a particle to cause inertial cavitation can be assessed as the presence of broadband noise in the emitted signal. Preferably, the particles are capable of generating inertial cavitation when the particle is suspended in water and subject to ultrasound at 1 MPa and 500 kHz. More preferably, the particles are 450 nm or less in size and are capable of generating inertial cavitation when the particles are suspended in water and subject to ultrasound at 1.5 MPa and 500 kHz.
The particles typically have an average size of 8000 nm or less, e.g. 5000 nm or less, preferably they are nanoparticles having a particle size of 1000 nm or less. Preferably, the particles have a size of from 100 nm to 8000 nm, e.g. from 100 nm to 5000 nm, preferably from 100 nm to 1000 nm. For example, the particles may have a size of at least 200 nm, preferably from 200 nm to 700 nm, for example around 500 nm. In one aspect, the particles have a size which is 450 nm or less. Preferably, the mean particle size of a composition comprising one or more particles of the invention is from 100 nm to 8000 nm, e.g. from 100 nm to 5000 nm, preferably from 100 nm to 1000 nm, more preferably at least 200 nm, preferably from 200 nm to 700 nm, for example around 500 nm. In one aspect, the composition contains particles having a mean particle size which is 450 nm or less. Particle size can be controlled, for example, by size filtration of particles.
In one aspect, the particle size may be from 100 nm to 600 nm, preferably from 100 nm to 500 nm, e.g. from 300 nm to 500 nm, for example from 100 nm to 450 nm or 300 nm to 450 nm. Particles of this size are small enough to pass through the walls of the vasculature and can therefore accumulate at desired sites outside the bloodstream. In the case of a composition, the mean particle size may be 1000 nm or less, in particular from 100 nm to 600 nm, preferably from 100 nm to 500 nm, e.g. from 300 nm to 500 nm for example from 100 nm to 450 nm or 300 nm to 450 nm.
In an alternative aspect, the particles have a particle size of more than 500 nm, preferably more than 600 nm, for example from 600 nm to 8000 nm, e.g. from 600 nm to 5000 nm or from 700 nm to 1000 nm. In the case of a composition, the mean particle size may be more than 500 nm, preferably more than 600 nm, for example from 600 nm to 5000 nm or from 700 nm to 1000 nm.
Typically, the particles comprise a single indentation or comprise two indentations (in the latter case they are typically approximately toroid shaped, comprising two indentations, on opposite sides of the particle). Further smaller particle features, e.g. surface roughness wherein features have an opening size of 50 nm or less, preferably 20 nm or less, more preferably 10 nm or less, may also be present. Typically, however, the particle has one or two indentations having an opening size of 50 nm or greater.
The form of the indentation(s) may vary, as long as the indented particle is capable of causing inertial cavitation (e.g. the indentation(s) are capable of entrapping or holding a gas bubble within their cavity). Typically, an indentation capable of causing inertial cavitation has an opening size of at least 50 nm or at least 100 nm. The opening is, for example from 10 to 500 nm, e.g. from 50 to 300 nm or from 100 to 300 nm. The opening size of an indentation as referred to herein relates to the diameter of the opening at the surface of the particle, in the case of a circular opening. In the case of a cavity having a non-circular cross-section at the opening, the opening size is the maximum dimension across the opening at the surface of the particle.
The size of the opening of an indentation may vary dependent on the size of the particle. For instance, the opening of an indentation may have a size (a diameter) which is at least 10% of the size (diameter) of the particle, e.g. at least 20% of the size (diameter) of the particle, preferably at least 40% of the size (diameter) of the particle. The opening size (diameter) of an indentation or cavity in the particle (its absolute size or relative size compared to the particle size) may be determined by imaging, e.g. SEM or AFM.
Typically, an indentation capable of causing inertial cavitation has a depth of at least nm, e.g. at least 50 nm or at least 100 nm. For example, the one or more indentations may have a depth of from 10 nm to 250 nm. The depth of the one or more indentations may be, for example, at least 10% of the particle size, for example at least 20% or at least 25% of the particle size. The depth of an indentation or cavity in the particle (its absolute size or relative size compared to the particle size) may be determined by imaging, e.g. SEM or AFM.
Typically, the cross-section of at least one indentation forms a conic section.
In one embodiment, the particle has a core comprising a water-immiscible phase comprising one or a mixture of non-volatile, water-immiscible components (hereinafter a “water-immiscible core”). The content of non-volatile component (also referred to as a water-immiscible liquid) as a proportion of the particle may vary widely. For example, the particle may comprise from 0.1 to 70% by weight non-volatile component and from 30 to 99.9% by weight polypeptide shell. The non-volatile component is typically an oil. The nature of the non-volatile component is not particularly limited and any biocompatible, pharmaceutically acceptable oil or mixture thereof can be used. Suitable components include sunflower oil, olive oil, soybean oil, coconut oil, safflower oil, cotton seed oil, sesame oil, orange oil, limonene oil, polyethylene glycols.
In one aspect, the water-immiscible core consists essentially of, preferably consists of, one or more non-volatile components. For example, in one preferred embodiment, the water-immiscible core consists essentially of, preferably consists of, one or a mixture of pharmaceutically acceptable excipients which are biocompatible, pharmaceutically acceptable oils, typically the biocompatible, pharmaceutically acceptable oils listed above. In a more preferred embodiment, the water-immiscible core consists essentially of, preferably consists of sunflower oil, olive oil or a combination of these oils. In this context, the expression “consists essentially of” means that the water-immiscible core typically contains no more than 5% by weight (e.g. no more than 2%, or no more than 1% by weight, preferably no more than 0.5% by weight, more preferably no more than 0.1% or 0.01% by weight) of other substances, e.g. substances other than non-volatile components, with reference to the total weight of the core. Thus, the water-immiscible core may comprise at least 95% by weight, preferably at least 98%, 99% by weight, more preferably at least 99.5 or 99.9% and most preferably at least 99.99% by weight of one or more pharmaceutically acceptable excipients which are biocompatible, pharmaceutically acceptable oils. The biocompatible, pharmaceutically acceptable oils are typically non-pharmaceutically active, and are preferably selected from those oils set out above.
In one embodiment, the core of the particle does not contain any diagnostic or therapeutic component. In one embodiment, the core of the particle does not contain an adjuvant. Where the core does not contain a therapeutic or diagnostic component or an adjuvant, typically, such component is present in no more than a trace amount, i.e. it is present in an amount which is not sufficient to have any pharmaceutical effect. Typically, such component is present in an amount of no more than 0.1% by weight, e.g. no more than 0.01% by weight compared to the weight of the particle as a whole.
In one embodiment, the particle does not comprise a water-immiscible core, in other words, the core of the particle does not comprise water-immiscible liquid(s), or water-immiscible liquid is present only in a small amount. Typically, in this embodiment, the water-immiscible liquid is present in an amount of no more than 10 wt %, e.g. no more than 5 wt % compared to the total weight of the particle. In this embodiment, the core of the particle may be hollow. Alternatively the polypeptide shell may extend to the core of the particle (in other words, the polypeptide shell also forms the core of the particle; or the particle may be considered as having no separate core). In this instance, reference to the “core” of the particle indicates the central part of the particle, irrespective of whether that central part is hollow or is formed by the polypeptide shell extending to the centre of the particle.
The particles of this embodiment, having no, or a small amount of water-immiscible liquid, have been found to be particularly responsive to ultrasound. Thus, they effectively generate inertial cavitation when exposed to ultrasound.
In one aspect of this embodiment, the particle substantially consists of, or consists of, polypeptide (or it substantially consists of the polypeptide shell as described herein). “Substantially consists of” in this context indicates that the particle consists of at least 95% by weight, preferably at least 98%, 99% by weight, more preferably at least 99.5 or 99.9% and most preferably at least 99.99% by weight of polypeptide (or the polypeptide shell as described herein).
The particle has a polypeptide shell, which in some embodiments may surround the water-immiscible core. Where no water-immiscible core is present, the particle may, for example, have a hollow core, or the polypeptide shell may extend to the centre of the particle, i.e. the particle is formed only of the polypeptide shell. The nature of the polypeptide is not particularly limited and a wide range of different polypeptides can be used.
Typically, the polypeptide shell comprises a polypeptide having two or more cysteine residues. This enables the polypeptide to form disulphide cross-linking bonds in order to generate the polypeptide shell. Preferably, the polypeptide contains at least 4 cysteine residues, for example at least 10 cysteine residues. A greater number of cysteine residues, in particular cysteine residues which are accessible on the surface of the polypeptide, generates a greater degree of cross-linking in the polypeptide shell, which may in turn provide greater stability to the structure. Cysteine residues are naturally occurring in many proteins. However, cysteine residues may be introduced into the polypeptide chain, for example by genetic engineering techniques.
The polypeptide shell typically comprises a polypeptide having a molecular weight of at least 5 kD, preferably at least 10 kD. A wide range of polypeptides having varying molecular weights can be used to form the polypeptide shell. Typically, therefore, the molecular weight of the polypeptide is from 5 to 80 kD, preferably from 10 to 50 kD.
Typically, the polypeptide shell comprises a protein. The particle of the invention typically retains the function of the one or more proteins from which it is formed. Thus, for example, a polypeptide comprising haemoglobin has an ability to carry oxygen and a polypeptide comprising insulin retains the ability to alter glucose metabolism. This further means that, after completion of the cavitation process, the whole particle may be metabolised.
The polypeptide shell may comprise a human blood protein (including fragments thereof). Examples of suitable proteins include albumin, insulin, globulin and haemoglobin. Of these, albumin, insulin and globulin are preferred. In one embodiment, the polypeptide shell comprises a serum albumin protein, preferably human serum albumin. Human serum albumin, and other blood proteins, are non-immunomodulatory, i.e. they do not give rise to an immune response on administration to a human. They are therefore beneficial for use in cavitation agents where an immunomodulatory response is not desired.
In one embodiment, the polypeptide shell comprises one or more non-immunomodulatory polypeptides, typically one or more non-immunomodulatory proteins, i.e. one or more polypeptides or proteins which do not give rise to an immune response on administration to a human. In this embodiment, preferably the polypeptide shell contains no more than 5% by weight preferably no more than 1% by weight immunomodulatory polypeptide, more preferably the polypeptide shell does not comprise an immunomodulatory polypeptide. In this embodiment, preferably the polypeptide shell consists essentially of, preferably it consists of, one or more non-immunomodulatory polypeptides. A polypeptide shell which consists essentially of one or more non-immunomodulatory polypeptides comprises at least 95% by weight, preferably at least 98%, e.g. at least 99%, at least 99.5 or at least 99.9% by weight non-immunomodulatory polypeptide, or fragments thereof.
Preferably, in this embodiment, the polypeptide shell comprises a human blood protein, in particular serum albumin, insulin, globulin and/or haemoglobin. The shall may preferably comprise at least 95% by weight, preferably at least 98%, e.g. at least 99%, at least 99.5 or at least 99.9% by weight of one or more human blood proteins, preferably serum albumin, insulin, globulin and/or haemoglobin. Typically, no more than trace amounts of other proteins are present in the shell, such that the shell consists essentially of, in particular consists of, one or more human blood proteins, in particular it may consist essentially of, in particular consists of, one or more of serum albumin, insulin, globulin and/or haemoglobin.
Preferably, in this embodiment, the polypeptide shell comprises human serum albumin. More preferably, the polypeptide shell is a human serum albumin shell. A human serum albumin shell typically comprises at least 95% by weight, preferably at least 98%, e.g. at least 99%, at least 99.5 or at least 99.9% by weight human serum albumin, or fragments thereof. Typically, no more than trace amounts of other proteins are present in the shell, such that the shell consists essentially of, in particular consists of, human serum albumin.
In an alternative embodiment, the polypeptide is immunomodulatory. The immunomodulatory polypeptide may be, for example, an immune checkpoint modulator, an antibody, a vaccine antigen, an adjuvant or an anti-inflammatory polypeptide. Further examples of immunomodulatory polypeptides useful in the present invention include macrophage colony stimulating factor (M-CSF), tumour necrosis factor (TNF, e.g. TNF-alpha), granulocyte macrophage colony stimulating factor (GM-CSF) and interferons.
Examples of suitable immune checkpoint modulators include anti-PDL-1 (aPDL1), anti-PD1 (aPD1), anti-CTLA4 (aCTLA4), bi specific T-cell engagers (BiTE), cytokines and chemokines such as interleukins (e.g. IL-1, IL-2, IL-4, IL-5, IL-6, IL-7, IL-10, IL-12, etc.).
Examples of suitable antibodies include aPDL1; aPD1; aCTLA4; BiTE antibodies; anti-growth factor antibodies that also trigger antibody dependent cellular cytotoxicity (ADCC) such as anti-EGFR antibodies (e.g. cetuximab and Herceptin); antibodies having anti-inflammatory effect such as anti-TNF (adalimumab, Humira); and JAK-inhibitor antibodies.
Examples of suitable antigens include vaccine antigens. For instance, the polypeptide shell may comprise at least one pathogenic antigen protein. The pathogenic antigen protein may be a full length protein or a fragment thereof. Examples of suitable antigen proteins include fragments of viral proteins or of parasitic proteins. The antigen may from a pathogen selected from Cal09 (flu), a coronavirus (e.g. Beta-coronaviridae or SARS-CoV-2), hepatitis B, Bordatella pertussis (whooping cough), Streptococcus pneumoniae, a meningococcus bacterium, human papilloma virus (HPV), or Plasmodium sporozoites (malaria parasite). In this embodiment, preferably the polypeptide shell comprises the polypeptide capable of generating an immune response (e.g. at least one pathogenic antigen) in an amount of no less than 1% by weight compared to the total polypeptide in the shell, e.g. about 10% by weight.
In one preferred aspect, the antigen protein is a viral spike protein, preferably a spike protein of the SARS-CoV-2 protein (e.g. SARS-CoV-2, S1 subunit protein (RBD)). In another aspect, the antigen is a circumsporozoite protein (CSP), a secreted surface protein of the sporozoite parasite. In a further aspect, the antigen is HepB surface antigen protein (HBsAg). In a further aspect, the antigen is associated with the influenza virus and is selected from haemagglutinin and/or an influenza neuraminidase. In another aspect, the antigen is filamentous haemagglutinin (pertussis). In another aspect, the antigen is pneumococcal surface protein A (PspA). In another aspect, the antigen is selected from Neisserial adhesin A (NadA), Neisserial Heparin Binding Antigen (NHBA) and/or factor H binding protein (fHbp). In another aspect, the antigen is an HPV-16 E6/E7 fusion protein. Fragments or genetically modified versions of any of these proteins may also be used.
Examples of suitable adjuvants include non-human albumin proteins (e.g. bovine serum albumin, mouse serum albumin, ovalbumin), sFLT ligand, cytokines and chemokines such as interleukins (e.g. IL-1, IL-2, IL-4, IL-5, IL-6, IL-7, IL-12, etc), macrophage colony stimulating factor (M-CSF), tumour necrosis factor (TNF), granulocyte and macrophage colony stimulating factor (GM-CSF).
Examples of suitable anti-inflammatory agents include adalimumab (Humira).
In one aspect, the polypeptide shell comprises an iron transfer protein (e.g. transferrin).
In one aspect, the particles do not contain an antigen, e.g. they do not contain a pathogenic antigen protein.
The polypeptide shell may comprise a single polypeptide, or a mixture of two or more different polypeptides. Preferably, the polypeptide shell comprises a single polypeptide (i.e. the polypeptide shell contains a single type of polypeptide, including fragments thereof, and does not contain a combination of two or more different polypeptides).
The polypeptide shell is optionally conjugated to one or more ligands. For example, the polypeptide shell may be conjugated to one or more ligands selected from a peptide, a protein, a sugar, a nanoparticle and a nucleic acid. Labelling moieties may also be conjugated to the polypeptide shell. Conjugation to proteins is commonly used for a variety of reasons. For example, the properties of the protein may be modified by conjugation to glycans (sugars) or to further proteins (e.g. antigens) having specific desired properties. Labelling moieties may be provided to enable imaging of the particles, for example as part of a diagnostic assay.
A common technique for conjugation to proteins, which can be employed in the present invention, is to target lysine residues on the protein surface. Thus, ligands having a group reactive with amine (e.g. NHS) may be conjugated to lysine on the polypeptide shell. However, alternative conjugation chemistries may be employed.
The ligands may be conjugated to the polypeptide shell after particle formation. Alternatively, the ligand may be conjugated to the polypeptide before formation of the particle.
The shell thickness of the polypeptide particle is typically at least 10 nm, preferably at least 20 nm, for example about 30-40 nm. For example, the polypeptide shell thickness may be from 10 to 100 nm, preferably from 20 to 60 nm. The thickness of the polypeptide nanoparticle shell can be determined by cryo-slicing and TEM imaging.
The particles of the invention are highly stable and can be stored as a suspension in aqueous solution or in solid form. For instance, the particles can be stored for at least a period of several months at 4° C.
The polypeptide particles of the invention can be made by a two step process which involves (a) obtaining particles having a polypeptide shell and a water-immiscible core comprising one or more volatile components and optionally one or more non-volatile components, and (b) removing the volatile component from the core in order to create the desired indented particle having ultrasound-responsive properties.
The invention therefore provides a method of producing a polypeptide particle according to the invention, comprising:
The particles are typically produced by first creating a biphasic composition comprising (1) a water-immiscible phase comprising one or more volatile components optionally together with one or more non-volatile components; and (2) an aqueous phase comprising the polypeptide or mixture of polypeptides which is to be present in the polypeptide shell. The aqueous solution typically comprises at least about 0.05% w/v of polypeptide, for example at least about 0.5%, preferably at least about 1% w/v polypeptide. Typically the polypeptide concentration is no higher than about 25% w/v, e.g. no higher than about 15% w/v, preferably no higher than about 10% w/v. Thus, suitable concentrations of polypeptide in the aqueous phase are from 0.5 to 15% w/v, preferably from 1 to 10% w/v, more preferably about 5% w/v.
The volumetric ratio of water-immiscible phase to aqueous phase in the biphasic mixture is typically about 1:5 to 3:1, for example from 1:4 to 1:1, e.g. about 1:3.
The water-immiscible phase comprises one or more volatile components. The nature of the volatile component(s) is not particularly limited, but is typically selected so that the or each volatile component is (a) water-immiscible, typically it is a volatile organic component, e.g. a volatile organic solvent, and (b) easily removed in the reduced pressure step. Typically, therefore, the or each volatile component has a vapour pressure at 25° C. which is greater than that of water at the same temperature. Typically, the or each volatile component has a vapour pressure at 25° C. of at least 3 kPa, preferably at least 3.5 kPa, for example at least 5 kPa, at least 10 kPa or at least 15 kPa. at 25° C. Suitable volatile components include cyclohexane, hexane, chloroform, ethyl acetate, propyl acetate and toluene, for example hexane, chloroform, ethyl acetate, propyl acetate and toluene. Cyclohexane is a preferred volatile component. Mixtures of two or more of these components can be used.
The biphasic mixture may be held at elevated temperature for a period of time prior to the next step. For instance, the biphasic mixture may be incubated at around 37° C. for up to 2 hours, for example for about 1 hour.
The biphasic mixture comprising the water-immiscible phase and aqueous phase is then subject to conditions which cause the cysteine residues in the polypeptide to cross-link. The conditions used may also emulsify the mixture. Typically, for example, cross-linking is achieved by homogenising the bi-phasic mixture e.g. by applying high pressure and/or high shear stress conditions. Preferably, homogenisation is carried out by use of ultrasound. In another preferred embodiment, homogenisation is carried out by high shear mixing. The high shear stress causes cross linking of the polypeptide, in particular by connecting cysteine groups within the polypeptide chains. It is understood that the homogenisation conditions may oxidise the sulfhydryl groups on a cysteine residue, or disrupt existing disulphide bonds, thereby allowing new disulphide bonds to form and generating the cross-linked shell structure. Water-immiscible phase remains physically trapped within the cross-linked polypeptide shell, providing the desired core-shell structure. The particles produced by the homogenisation step are generally substantially spherical in shape.
One example of a method for achieving homogenisation is to place an ultrasound horn at the interface of the aqueous and water-immiscible phases, and apply low-frequency ultrasound. Ultrasound may be applied at around 50% amplitude. For example, ultrasound may be applied for at least 1 minute, e.g. about 3 minutes. For example, particle formation has been achieved using a QSonica Q125 ultrasound probe (frequency: 20 kHz; power: 125 watts) at 50% amplitude for 3 minutes.
An alternative method for achieving homogenisation is to use hydrodynamic cavitation, which uses high pressure to pump a liquid through a narrow orifice. The increase in flow velocity as the liquid passes through the orifice, and subsequent decrease in velocity once past the orifice, causes cavitation nuclei to grow and then collapse. Applying hydrodynamic cavitation to the biphasic mixture may cause cross-linking of cysteine residues and/or emulsification, leading to formation of particles. Hydrodynamic shearing is a further alternative method which may produce the same reactive oxygen species that reduce/oxidise cysteine residues that lead to particle formation. For instance, the method may comprise forming a pre-emulsion by high shear mixing, then passing the pre-emulsion through a hydrodynamic shearing microfluidizer, for example at pressures ranging from 7000 PSI to 40,000 PSI (about 50 to about 275 MPa), typically from 10,000 to 30,000 PSI (about 70 to about 200 MPa), for example from about 20,000 PSI (about 140 MPa). Other methods of sonication may also be used. For example a tumour homogeniser may be used.
Spherical particles having a water-immiscible core and a polypeptide shell, which are produced by such homogenisation methods, are known in the art, and methods for their synthesis have been previously described (see Suslick K. S. and M. W. Grimstaff, Journal of the Americal Chemical Society, 1990, 112(21), p7807-7809, the contents of which are incorporated herein by reference). The particles of the invention may be made by such techniques or other methods of sonication, such as those described in U.S. Pat. No. 5,439,686, the contents of which are incorporated herein by reference.
Following the creation of the polypeptide shell, the particles of the invention undergo a step in which the volatile component(s) are removed, causing deformation of the particle and thus the desired indented structure. Removal of the volatile component(s) can be done under reduced pressure conditions. For instance this step can be carried out using a vacuum protein concentrator such as a Speed Vac™ (Thermo Scientific), but other instrumentation such as a rotary evaporator can be used. Reduced pressure conditions are typically applied for at least 30 minutes, preferably at least an hour. For instance, reduced pressure may be applied for from 2 to 16 hours. Lyophilisation (freeze-drying) may be used as an alternative method for removing volatile solvent. In some embodiments, a combination of these methods is employed.
The step of removing volatile component removes all or part of the volatile component(s) present. Preferably at least 50%, more preferably at least 80%, 90% or 95% by volume of the volatile component are removed. More preferably substantially all (e.g. at least 98%, 99% or 99.5% by volume) of the volatile components are removed. Removal is sufficient to create an indented structure.
The nature and amount of volatile component which is present in the water-immiscible phase affects the particle size and may be used as a factor in controlling the size of particle produced. The amount of volatile component also affects the deformation of the particle and thus the size of any indentation. In general, the greater the amount of volatile component, the greater the size of the indentation which is expected to be produced. Variation in the size of the indentation may also be relevant to the cavitation effects generated by the indented particle, due to the change in the potential for gas bubbles to be trapped within the cavity of the indentation.
Where both volatile and non-volatile components are used in the water-immiscible phase, the amount of volatile component can be varied by changing the relative amount of non-volatile and volatile component in the water-immiscible phase. Typically, the water-immiscible phase contains from 20 to 95% by volume volatile, preferably from 30 to 70% by volume volatile, most preferably from 45 to 55% by volume volatile, e.g. about 50% by volume volatile. Correspondingly, the ratio of volatile to non-volatile component in the water-immiscible phase is typically from about 1:20 to 20:1, preferably from about 1:4 to 15:1, e.g. about 1:3 to 3:1, more preferably about 0.5:1 to 2:1 (1:2 to 2:1), most preferably about 1:1. A minimum volume ratio of at least 1:20 of volatile to non-volatile component (about 5% by volume volatile component) is typically needed to achieve indentation in the particle on removal of the volatile component from the core. A volatile content of at least 40% by volume, preferably from 45 to 55% by volume in the water-immiscible phase, preferably around 50% by volume (or 1:1), has been found to provide improved cavitation properties.
In an alternative preferred embodiment, the ratio of volatile to non-volatile component in the water-immiscible phase is typically from about 1:20 to 20:1, preferably from about 1:4 to 15:1, e.g. about 1:1 to 15:1, more preferably about 5:1 to 10:1.
Alternatively, the water-immiscible phase may comprise substantially no non-volatile component, or non-volatile component may be absent. Thus, there may be no more than 5% by volume, for example no more than 2%, 1% or 0.5% by volume non-volatile component, for example no more 0.1% or 0.01% by volume non-volatile component. In this embodiment, the water-immiscible phase typically consists of, or substantially consists of, the one or more volatile components. “Substantially consists of” in this context means that the water-immiscible phase comprises at least 95% by volume, preferably at least 98%, 99% by volume, more preferably at least 99.5 or 99.9% and most preferably at least 99.99% by volume of the one or more non-volatile components.
Where the water-immiscible phase comprises no, or substantially no non-volatile component, the core of the particle once produced may be hollow. Alternatively, the polypeptide shell may be compressed into the middle of the particle on removal of the volatile components, such that the shell extends into the centre of the particle; in other words, the shell extends into, and also forms, the core of the particle.
The method of the invention may further comprise the steps of:
The drying step may be carried out by evaporation, e.g. under reduced pressure and/or with mild heating. For instance this step can be carried out using a rotary evaporator set to a temperature of up to about 40 C. Typically, the drying step is combined with the step of evaporation of volatile component, but continuing the reduced pressure (and optionally mild heat) conditions for a longer period of time and by use of mild heating, in order to evaporate water to provide a solid product. Thus, for instance, removal of volatile component and drying may be carried out by applying reduced pressure conditions and heating at up to 40 C until a solid is produced.
The particles are then preferably re-suspended in a liquid medium, typically water or an aqueous solution such as a buffer. Re-suspension may provide improved long term stability to the particles and they are therefore preferably re-suspended prior to storage. However, particles may alternatively be stored in solid form and re-suspended prior to use. Drying and re-suspension may assist in trapping gas bubbles in any indentations on the particle, which provides improved inertial cavitation response.
The method may alternatively or additionally comprise:
Lyophilisation may be used to both remove volatile solvent and dry the particles, in a similar manner to that described above for rotary evaporation, for example. Thus, lyophilisation is used as an alternative to method to solvent removal/drying, as discussed above). Alternatively, lyophilisation may be carried out after the solvent has been removed by another means and optionally after drying as described above.
Typically, the particles are re-suspended in a liquid medium, typically water or an aqueous solution such as a buffer. Re-suspension may provide improved long term stability to the particles and they are therefore preferably re-suspended prior to storage. However, particles may alternatively be stored in solid (lyophilised) form and re-suspended prior to use. Lyophilisation and re-suspension may further assist in trapping gas bubbles in any indentations on the particle, which provides improved inertial cavitation response. A particularly improved cavitation response has been demonstrated with particles which have been both dried and re-suspended, and subsequently lyophilised and re-suspended.
The steps of drying and/or lyophilisation may be carried out with any of the particles described herein. However, in a preferred embodiment, where the particle is produced by use of only volatile component(s) in the core (i.e. the final particle after evaporation of volatile component does not comprise a water-immiscible core), or where the particle is produced using a low proportion, typically about 10% by volume, less than 10% by volume, preferably less than 5% by volume, e.g. less than 1% or less than 0.1% by volume, of non-volatile component in the water-immiscible phase (such that the final particle has a core comprising a small amount of non-volatile component, e.g. about 10% by volume, less than 10 wt %, preferably less than 5 wt % compared to the total particle), it is preferred that the particles are dried and/or lyophilised. Most preferably, these particles are dried, re-suspended and then lyophilised. Yet more preferably, these particles, are dried, re-suspended, lyophilised and again re-suspended.
The particles can be purified by suitable means and/or subject to size filtration. For example, particles can be separated from residual oil, solvent and protein by any suitable means, for example, by dialysis e.g. through a dialysis filter having a molecular weight cut off of appropriate size (e.g. 1M Da). Size filtration and/or centrifugation may also be used to limit the maximum size of the particles. Purification may be carried out following evaporation of the volatile component, following drying and re-suspension, or following lyophilisation and re-suspension.
The particles may be suspended in a liquid medium for storage or use, e.g. water, or an aqueous solution, optionally a buffer solution.
The present invention provides a composition, typically a pharmaceutical composition, comprising one or more polypeptide particles according to the invention. The composition may comprise a plurality of the polypeptide particles alone, or the particles may be provided together with one or more pharmaceutically acceptable carriers or diluents. Typically, compositions provided together with a carrier or diluent contain up to 85 wt % of a particle of the invention. More typically, such a composition contains up to 50 wt % of a particle of the invention. Preferred pharmaceutical compositions are sterile and pyrogen free.
The compositions of the invention may comprise one or more different types of particle according to the invention. For instance, the composition may comprise first particles having a first type of polypeptide shell and second particles having a second (different) type of polypeptide shell. Typically, the compositions of the invention comprise a single type of particle.
The particles in the composition may be substantially monodisperse. For instance, they may have a polydispersity index of 0.20 or less, e.g. 0.19 or less, 0.18 or less, 0.17 or less, 0.16 or less, or 0.15 or less. Greater monodispersity of the particles may provide a greater control over cavitation and thus improved acoustic tuning. Polydispersity may be determined by DLS.
The particles of the invention may be administered by any suitable route, depending on the nature of the treatment, e.g. orally (as syrups, tablets, capsules, lozenges, controlled-release preparations, fast-dissolving preparations, etc); topically (as gels, creams, ointments, lotions, nasal sprays or aerosols, etc); by injection (subcutaneous, intradermal, intramuscular, intravenous, intratumoural, intrathecal etc.), transdermally (e.g. by application of a patch, gel or implant) or by inhalation (as a dry powder, a solution, a dispersion, etc). In one aspect, the particles are administered parenterally, e.g. by infusion or by injection, preferably by intravenous, intramuscular, intradermal or subcutaneous administration. In another aspect, the particles are administered by transdermal administration. Preferably, the particles are administered parenterally, e.g. by injection (preferably intravascularly, or intrathecally), or transdermally.
For example, solid oral forms may contain, together with the particles of the invention, diluents, e.g. lactose, dextrose, saccharose, cellulose, corn starch or potato starch; lubricants, e.g. silica, talc, stearic acid, magnesium or calcium stearate, and/or polyethylene glycols; binding agents; e.g. starches, arabic gums, gelatin, methylcellulose, carboxymethylcellulose or polyvinyl pyrrolidone; disaggregating agents, e.g. starch, alginic acid, alginates or sodium starch glycolate; effervescing mixtures; dyestuffs; sweeteners; wetting agents, such as lecithin, polysorbates, laurylsulphates; and, in general, non toxic and pharmacologically inactive substances used in pharmaceutical formulations. Such pharmaceutical preparations may be manufactured in known manner, for example, by means of mixing, granulating, tableting, sugar coating, or film coating processes.
In one embodiment, a composition provided together with a carrier or diluent is a liquid dispersion. Typically, water (preferably sterile water) is used as diluent for a liquid dispersion. Liquid dispersions for oral administration may be syrups, emulsions and suspensions. Suspensions are preferred. The syrups, emulsions and suspensions may contain as carriers, for example, saccharose or saccharose with glycerine and/or mannitol and/or sorbitol. Glucose is a preferred carrier. For example, the particles may be provided as a suspension in a glucose solution, for example a glucose solution comprising up to 10 wt % glucose, e.g. about 5 wt % glucose.
Suspensions and emulsions may contain as carrier, for example a natural gum, agar, sodium alginate, pectin, methylcellulose, carboxymethylcellulose, or polyvinyl alcohol. The suspensions or solutions for parenteral administration, e.g. intramuscular injection, may contain, together with the active compound, a pharmaceutically acceptable carrier, e.g. sterile water, olive oil, ethyl oleate, glycols, e.g. propylene glycol, and if desired, a suitable amount of lidocaine hydrochloride.
Particles for administration in suspension form may be provided as lyophilised particles, for reconstitution in a suitable carrier (e.g. sterile water) prior to administration.
A gel for transdermal administration may comprise a diluent selected from an alcohol such as ethanol or propanol, glycerine, propylene glycol or polyethylene glycol. The gel may also comprise preservatives and may comprise water or a buffer solution. Permeation enhancers such as fatty acids, fatty alcohols, urea, sulphoxides, azone, pyrrolidones, essential oils, terpenes and terpenoids may be incorporated. Alternatively the gel for transdermal delivery may be formulated as a proniosome or microemulsion gel.
As discussed above, the particles of the invention can be administered via a variety of routes of administration. Once administered, ultrasound is provided at the target site in order to generate the inertial cavitation response of the particles.
Ultrasound is typically delivered at a frequency of from 100 to 3000 kHz, for example from 100 to 1000 kHz, for example from 200 to 600 kHz and optionally a duty cycle (DC) of from 1% to 20%, e.g. from 2% to 15%. Typically, the ultrasound delivered has a pulse repetition frequency (PRF) of from 0.01 to 100 Hz, e.g. from 0.1 to 50 Hz, preferably from 0.1 to 20 Hz. Typically, the ultrasound is provided at a peak negative pressure (PNP) of 0.5 MPa to 7.0 MPa, e.g. from 0.5 to 3.0 MPa, e.g. from 1.0 to 2.5 MPa, for example at least 1.5 MPa or from 1.5 to 2.5 MPa.
Particularly preferred ultrasound conditions are from 1.0 to 2.0 MPa and 100 to 600 kHz.
The ultrasound parameters may be varied depending on the mode of administration. For instance, for transdermal delivery, the ultrasound may be delivered at a frequency of from 100 to 500 kHz, for example from 200 to 300 kHz and optionally a duty cycle (DC) of from 5% to 20%, e.g. from 5% to 15%. Typically, the ultrasound delivered has a pulse repetition frequency (PRF) of from 0.1 to 100 Hz, e.g. from 1 to 50 Hz, preferably from 5 to 20 Hz. Typically, the ultrasound is provided at a peak negative pressure (PNP) of 0.5 MPa to 2.0 MPa, e.g. from 1.0 to 2.0 MPa, 1.5 MPa to 2.0 MPa or 1.5 to 1.8 MPa.
For parenterally administered, e.g. injected, particles, ultrasound is typically delivered at a frequency of from 200 to 3000 kHz, for example from 200 to 1000 kHz, for example from 400 to 600 kHz and optionally a duty cycle (DC) of from 1% to 10%, e.g. from 2% to 10%. Typically, the ultrasound delivered has a pulse repetition frequency (PRF) of from 0.01 to 50 Hz, e.g. from 0.1 to 10 Hz, preferably from 0.1 to 1 Hz. Typically, the ultrasound is provided at a peak negative pressure (PNP) of 1.0 MPa to 7.0 MPa, e.g. from 1.0 to 3.0 MPa, e.g. from 1.5 to 2.5 MPa.
Ultrasound may be applied for a duration of from 10 seconds to 15 minutes, typically from 30 seconds to 10 minutes, preferably from 1 to 5 minutes. Particularly preferred treatment time in the case of transdermal delivery is from 1 to 3 minutes, most preferably about 2 minutes.
Exposure of the particles to ultrasound after administration causes an inertial cavitation effect in the fluid in which the particles are contained. For instance, if the particles are administered systemically, e.g. intravascularly or intra-arterially, exposure of the particles to ultrasound at a target site causes inertial cavitation within the vasculature. This may lead to a shock wave and/or miscrostreaming in which the particles themselves, and any co-administered therapeutic or diagnostic agents, may be transported to a target site. In this way, inertial cavitation can be used to selectively target chosen sites of administration.
Similarly, application of ultrasound to a formulation of particles applied to the skin may cause inertial cavitation within the formulation, assisting in the transdermal delivery of the particles, and any co-administered diagnostic or therapeutic agent. Ultrasound has previously been used to assist transdermal delivery of drugs. However, previous work has focussed on the use of ultrasound to permeabilise the skin and particles for delivery have been administered with additional means, for example via ballistic delivery. In contrast, the present invention enables particles to travel through the skin solely by applying the particles in a suitable formulation, such as a gel, and providing ultrasound at the site. The combination of the small size of the particles, and the microstreaming effect caused by inertial cavitation, pushes the particles, together with any co-delivered agent, through the relatively impermeable stratum corneum, thus providing effective transdermal delivery.
The examples provided herein demonstrate the successful administration via transdermal delivery of DNA encoding luciferase, by transdermal administration together with particles according to the invention. Luminescence measurements (providing an indication of the degree of successful administration of DNA, see
The particles of the invention can be used in any situation in which inertial cavitation is desired such as histotripsy, thermal ablation, sonochemistry, sonofusion and waste water treatment. Due to their biodegradeability, they are particularly useful in methods of treatment or diagnosis of the human or animal body which involve generation of inertial cavitation. For example, they can be for use in methods that involve using inertial cavitation to cause localised tissue ablation and/or removal in order to achieve a therapeutic outcome. Such methods include for example the treatment of tumours and removal of cardiac tissue in treatment of heart disease. In this aspect, the particles of the invention are advantageous due to their small size, stability, and biodegradeability. The particles may be administered transdermally and are therefore also useful (either alone or in combination with one or more further therapeutic agents) in the treatment of diseases or disorders of the skin.
The use of inertial cavitation to accumulate nanoparticles in selected sites has previously been demonstrated by Kwan et al in Small, 2015 October; 11(39): 5305-5314. The particles of the present invention, having the ability to generate inertial cavitation effects in vivo, similarly can be accumulated at a selected target site, such as a tumour.
The present invention therefore provides particles and compositions as described herein for use in a method of diagnosis or therapy. The method typically comprises administering a particle or composition as described herein and applying ultrasound. In particular, the particle or composition is for use in generating inertial cavitation in the subject. Inertial cavitation can be generated at a chosen target site. Also provided is a method of treatment of a subject, the method comprising administering an effective amount of a particle or composition as described herein and applying ultrasound. The method may generate inertial cavitation in the subject. Also provided is the use of a particle or composition as described herein in the manufacture of a medicament for use in treatment by therapy or diagnosis, the method comprising administering the particle or composition and applying ultrasound. In particular, the medicament is for use in generating inertial cavitation in the subject.
The particles of the invention can be used as delivery vehicles for other agents, such as a drug or a diagnostic agent (e.g. an MRI contrast agent such as a Gd-based MRI contrast agent, or a fluoroscopy contrast agent). Thus, the particles of the invention can be used to deliver other agents to a target in vivo by administering the nanoparticle and the other agent in combination. The particles or compositions of the invention can therefore be administered together with one or more further therapeutic or diagnostic agents. The invention therefore also provides a combination of a particle according to the invention and a further therapeutic or diagnostic agent. In one aspect, the further therapeutic or diagnostic agent is not a vaccine.
The particles of the invention may be administered in a single composition with the separate agent, or as a separate composition. Where two compositions are used, these may be administered simultaneously or separately. Simultaneous or substantially simultaneous administration is preferred.
Application of ultrasound following administration of the nanoparticle and a separate agent causes cavitation to occur. This enhances transport of the agent into cells. A particular advantage of using cavitation to enhance transport of an active agent into cells in this way is that ultrasound can be applied at selected locations, leading to the active agent being transported into cells only in those selected locations. Furthermore, the use of inertial cavitation to enhance transport may increase the amount of both the particles themselves, and any co-administered agent, at the target site. The particles of the invention are therefore useful in increasing delivery of an agent to a target site.
The invention therefore provides particles for use in enhancing transport of a further therapeutic or diagnostic agent to a target site. The invention also provides a method for enhancing transport of a further therapeutic or diagnostic agent to a target site. Also provided is the use of a particle or composition as described herein in the manufacture of a medicament for use in enhancing transport of a further therapeutic or diagnostic agent to a target site. Such enhanced transport increases the extracellular or intracellular concentration of the further therapeutic or diagnostic agent. The enhanced transport is achieved via the microstreaming effect of inertial cavitation. Particles are physically driven through natural holes between cells, for example natural holes in the endothelium. This therefore provides an improved method of transporting therapeutic or diagnostic agent compared with, for example, methods which increase the permeability of the endothelium.
In one aspect of the invention, the separate agent is encapsulated in an ultrasound-responsive liposome. Such an ultrasound-responsive liposome can release the agent in the presence of inertial cavitation. The particles of the present invention may therefore be administered concurrently with the liposome and ultrasound applied in order to cause cavitation at the desired location, and correspondingly cause release of the active agent at the desired location.
Where the particles of the invention are to be used to deliver agents to an extravascular location, e.g. to a tumour, the particles preferably have a size of up to 500 nm, typically from 100 nm to 500 nm. More preferably the particles have a size of from 100 to 300 nm. Such particle sizes may, for example, be desired in order to improve accumulation in tumour tissue by the enhanced permeability and retention (EPR) effect. Tumour tissues may contain neovasculature having abnormal form and architecture, leading to abnormal molecular and fluid transport dynamics. That can cause nanoparticles of around 100 to 500 nm, e.g. 100 to 300 nm in size to accumulate in tumour tissue much more than they do in normal tissues. Nanoparticle sizes of 100 to 500 nm, e.g. 100 to 450 nm or 100 to 300 nm may therefore be preferred, in particular for use in treating tumour. In a preferred embodiment, where the nanoparticles are for use in treating tumour, the particle size is 450 nm or less.
Suitable therapeutic agents which may be used in combination with the particles of the invention are therapeutic agents for use in treating tumour, for example chemotherapeutic drugs. Examples of suitable chemotherapeutic drugs include 5-fluorouracil, 6-mercaptopurine, cytarabine, gemcitabine, methotrexate, actinomycin-D, bleomycin, daunorubicin, doxorubicin, docetaxel, estramustine, paclitaxel, vinblastine, etoposide, irinotecan, teniposide, topotecan, prednisone, methylprednisolone, and dexamethasone.
When used in combination with other agents the nanoparticles can also provide real time tracking and mapping of drug distribution in vivo, for example using conventional ultrasound imaging or passive acoustic mapping of inertial cavitation (WO 2010 052494).
The subject of any diagnostic or therapeutic treatment is typically a mammal, preferably a human.
The dose of particles of the invention may be determined according to various parameters, especially according to the substance used; the age, weight and condition of the individual to be treated; the route of administration; and the required regimen. A physician will be able to determine the required route of administration and dosage for any particular individual. The dose may be provided as a single dose or may be provided as multiple doses, for example taken at regular intervals, for example 2, 3 or 4 doses administered hourly. Typically polypeptide-based treatments are administered in the range of 1 pg to 1 mg, more typically 1 pg to 10 μg for particle mediated delivery and 1 pg to 1 mg, more typically 1-100 pg, more typically 5-50 pg for other routes. Generally, it is expected that each dose will comprise 0.01-3 mg of polypeptide.
Ultrasound-responsive particles were prepared according to protocol A as follows:
3 ml of a 50 mg/ml solution of protein is overlaid with 1 ml of a water immiscible solution to produce a biphasic solution. The biphasic mixture is sealed in a glass vial and placed in an incubator at 37 C for 1 hour.
An ultrasound horn is then placed at the interface of the two layers and low frequency ultrasound at 50% amplitude is applied for 3 minutes at 125 watts using QSonica Q125 at 50% amplitude. This produced an emulsion of particles comprising a core containing the water immiscible mixture and a protein shell.
The volatile solvent component of the particle core is then removed under reduced pressure using a SpeedVac™ protein concentrator to provide a solution containing the particles.
The particles are then separated from residual oil, solvent and protein by dialysis in a 1M Da molecular weight filter for 24 to 48 hours.
Particles were also produced according to a modified protocol B. Protocol B is identical to protocol A with the exception that the protein was at a lower concentration of 0.5 mg protein in 666 ul of water which was then overlaid with 333 ul of the oil/volatile solvent layer.
Particles were also produced according to a modified protocol C:
3 ml of a 50 mg/ml solution of protein is overlaid with 1 ml of a water immiscible solution to produce a biphasic solution. The biphasic mixture is sealed in a glass vial and placed in an incubator at 37 C for 1 hour.
An ultrasound horn is then placed at the interface of the two layers and low frequency ultrasound at 50% amplitude is applied for 3 minutes at 125 watts using QSonica Q125 at 50% amplitude. This produced an emulsion of particles comprising a core containing the water immiscible mixture and a protein shell.
The volatile solvent component of the particle core is then removed under reduced pressure by rotary evaporation at 40 C for 48 hours to provide solid particles.
Particles are re-suspended in water. Some particles are then freeze-dried for 48 hours, followed by re-suspension in water once again.
The following particles were produced:
Bovine serum albumin (BSA) used was ≥99% purity, Sigma A7638.
IgG was non-specific IgG isolated from human blood ((≥99% Sigma, I4506).
Covid spike protein was SARS-CoV-2, S1, RBD, Cambridge Bioscience, 230-30162-1000.
Particles were analysed by dynamic light scattering (DLS), scanning electron microscopy (SEM) and via spinning disc confocal microscopy following conjugation of the particle to fluorophores.
The particles can be seen to have an indented structure, consistent with the ability of the particle to trap a gas bubble in the indentation. The particles have either one or two major indentations.
This experiment also confirms that upon forming particles, the protein retains the ability to undergo standard protein conjugation reactions, in this case reaction with chemistry targeting lysine residues. The particles became fluorescent following conjugation of two different lysine reacting dyes.
The nature of the volatile component was varied in Examples 3 to 6, in order to determine the effect on the particle size. Results are depicted in
Variation of the protein to incorporate a variety of different proteins into the particle was achieved as set out in Examples 14 to 19.
All measurements of inertial cavitation were carried out at a frequency of 0.5 MHz, 1000 cycle pulse length, and 100 ms pulse repetition period, with varying driving pressures as set out below.
First, to characterise the cavitation ability of particles across a range of sizes, particles produced according to Example 1 above were filtered through 200 nm and 450 nm filters and then assessed for inertial cavitation. The passive cavitation detection (PCD) level was assessed at driving pressures of 0.5 MPa, 1.0 MPa, 1.5 MPa and 2.0 MPa. Time averaged PCD levels over a 30 second exposure are provided in
Inertial cavitation was also demonstrated, using particles produced according to Example 18 above. Particles were exposed to 1.2 MPa peak pressure for 5 minutes.
Inertial cavitation was also demonstrated using particles produced according to Example 20 above. Particles were exposed to 1.4 MPa, 1.7 MPa and 2.1 MPa for at least 300 seconds. Particles were studied both before and after freeze-drying. Water was used as a control. Cavitation was observed under all conditions for all particles. At 1.4 MPa, cavitation was observed for less than 20 s for dried but non-freeze-dried particles, but for over 150 s for freeze-dried particles. At 1.7 MPa, cavitation was observed for around 100 s for dried but non-freeze-dried particles, but for over 150 s for freeze-dried particles. At 2.1 MPa, cavitation was observed for around 200 s for dried but non-freeze-dried particles, but for over 300 s for freeze-dried particles.
Examples 11 to 13 above describe the production of particles in an identical manner to Example 1 but using differing amounts of the volatile component, hexane. Experiments were conducted to establish if varying the ratio of volatile solvent (and as such the potential depth of the indentation in the particle) can affect the cavitation ability of the particle. Cavitation was studied in the same manner as set out above and the results are set out in
In vivo transdermal particle cavitation in the experiments described below was carried out by using a source transducer (117D-01, Sonic Concepts, USA) to initiate cavitation. The transducer was fitted with a Perspex coupling cone (used to efficiently transmit ultrasound from the source to the therapy target), filled with degassed water and covered with an acoustically transparent Mylar plastic. The coupling cone shape was designed to align with the outer envelope of the focused ultrasound beam. A formulation holder, containing particle solution, was placed on the murine skin and the source transducer was placed on top of this, with the Mylar plastic acoustic window positioned to prevent air entering the acoustic path. A single element spherically focused ultrasound transducer acting as passive acoustic detector (PCD) was coaxially located inside the source transducer, to allow the cavitation signal to be recorded. The PCD signal was passed through a 2.0 MHz high pass filter and amplified with a gain of 25 by a pre-amplifier (SR445A, Stanford Research Systems, USA). The signal was then digitised and monitored in real time by an 12-bit digital oscilloscope (Handyscope HS3 100 MHz, TiePie Engineering, The Netherlands) and the data was saved on an external hard drive (Portable SSD T5, Samsung, Korea) (
Particles according to the invention were applied to mice to study the transdermal delivery of the particles. Immune response to the protein delivered was used to assess successful delivery of particle via transdermal administration followed by ultrasound.
8 mice were used in the experiment, and each mouse received two separate particle preparations, one applied to each flank. Thus, 16 experiments were carried out in total as follows:
Following administration of the particles in the designated manner for each group, immune response to BSA protein was determined by carrying out ELISA analysis to study immune response to BSA following delivery.
Results are depicted in
Particles according to the invention, or polymer particles produced in accordance with WO 2015/075442, were applied to a mouse flank. 8 mice were used in the experiment, and each mouse received two separate particle preparations, one applied to each flank. Thus, 16 experiments were carried out in total as follows:
Protein particles used were particles produced in accordance with Example 1 above. Polymer particles were produced in accordance with WO 2015/075442. All samples were provided in MilliQ water. Protein particles were provided as 9 mg protein in 1.8 ml MilliQ water. All samples contained 50 g of DNA encoding luciferase. The particles/DNA were administered to each mouse by direct application to the mouse flank (with or without application of ultrasound). Ultrasound (US) was applied using the method described in “In Vivo Cavitation Ultrasound Methodology” above, for the indicated exposure time.
Successful transdermal delivery was assessed by the generation of luciferase following administration.
Transdermal administration of DNA using the particles of the invention as cavitation delivery agent produced comparable or significantly greater luminescence in all cases when compared to current gold standard cavitation agent (polymer particles).
Particles according to Example 20, together with luciferase pDNA, were also administered transdermally by the same method.
In vivo transdermal particle cavitation in the experiments described below were carried out using a source transducer (117D-01, Sonic Concepts, USA) to initiate cavitation. The transducer was fitted with a Perspex coupling cone (used to efficiently transmit ultrasound from the source to the therapy target), filled with degassed water and covered with an acoustically transparent Mylar plastic. The coupling cone was designed to align with the outer envelope of the focused ultrasound beam. A Perspex holder was placed on the coupling cone, which incorporated the formulation holder and provided space for the anaesthesia nose cone and mouse. The coupling cone was filled with degassed water and the bed would be lowered on the coupling cone. The scruff of the mouse was secured with a bobby pin and the skin flap placed over the formulation holder. The skin flap was secured with an acoustic absorber placed on top of this flap. A single element spherically focused ultrasound transducer acting as passive acoustic detector (PCD) was coaxially located inside the source transducer, to allow the cavitation signal to be recorded. The PCD signal was passed through a 1.8 MHz high pass filter and amplified with a relative gain of 23 by a pulser-receiver (DPR300 ultrasonic pulser/receiver, JSR Ultrasonics, Imaginant, USA. The signal was then digitised and monitored in real time by an 12-bit digital oscilloscope (Handyscope HS3 100 MHz, TiePie Engineering, The Netherlands) and the data was saved on an external hard drive (Portable SSD T5, Samsung, Korea) (
Four experiments (01 to 04 below) were carried out in order to optimise conditions for transdermal delivery of particles. In each case, the particles of the invention were particles according to Example 20, which have been freeze-dried and resuspended. Particles were applied to a mouse scruff under varying conditions as specified. DNA luciferase was co-administered in order to study effective delivery.
All samples were provided in MilliQ water. Protein particles were provided as 90 mg protein in 1.8 ml MilliQ. All samples contained DNA encoding luciferase at the indicated concentration. The particles/DNA were administered to each mouse by direct application to the mouse scruff (with or without application of ultrasound), or by intradermal administration, as indicated. Ultrasound (US) was applied using the method described in “Protocol 2 for ultrasound methodology” above, for the indicated exposure time and at the specified pressure.
Luminescence was assessed after approximately 24 hours with an In Vivo Imaging System (IVIS, PerkinElmer, USA). 100 μL of 15.8 mg/mL Pierce™ D-luciferin (ThermoFisher Scientific, USA) was injected into the tail vein. The mice were imaged 3.5 minutes after injection and imaged for 30 seconds. The images were processed with Living Image® (PerkinElmer®, USA). The treatment area was digitally selected and the total flux (photons/sec) and the average radiance (photons/sec/cm2/sr) were determined.
Reference to CMV-Luc in the examples below is pDNA (pGL4.50[luc2/CMV/Hygro] Vector (Promega, USA)). For injection the full 142 ug DNA was delivered, whereas for the transdermal administration, only a fraction of this dose was delivered.
US=ultrasound delivery using specified conditions and ID is intradermal delivery
Successful transdermal delivery and DNA expression was assessed by the generation of luciferase following administration.
Successful transdermal delivery was assessed by the generation of luciferase following administration.
The cavitation signal, detected by the PCD, was analysed to determine the total acoustic sensor energy (TASE), defined as:
To summarise, the root mean square of the voltage measured in the time window was calculated. To calculate the total power, the root mean square of the voltage was squared and divided by the impedance, estimated at 500. This was multiplied with the actual pulse time to estimate the total energy of each pulse. The estimated energy of each pulse was summed to get the total acoustic sensor energy (TASE). This showed sustained cavitation could be detected for at least up to 10 minutes (
Successful transdermal delivery and DNA expression was assessed by the generation of luciferase following administration.
Each mouse was treated with US on the right-hand side of their scruff and intradermally injected in their flank. Mice were culled after 24 hours.
Particles were Produced According to a Modified Protocol D:
6 ml of a 50 mg/ml solution of protein was overlaid with 2 ml of a water immiscible component to produce a biphasic solution. The nature and ratio of volatile/non-volatile components are indicated in the table below.
A pre emulsion was formed using a high shear mixer and then passed through a hydrodynamic shearing microfluidizer device at a pressure of 20,000 PSI (138 MPa).
Particles were then freeze-dried for 48 hours, followed by re-suspension in water once again. The following particles can be produced according to protocol D:
Particles produced according to example 21 were administered to mice via transdermal administration, as described above for examples 01 to 04. Conditions of treatment were:
Experiments were carried out to determine the amount of BSA which is delivered following transdermal administration of particles to mice. Particles according to Example 20, which have been freeze-dried and resuspended, or particles according to Example 21, were applied to a mouse scruff under varying conditions as specified below.
All samples were provided in MilliQ. All solutions applied to the skin contained 90 mg BSA (1.8 mL of 50 mg/mL solution). DNA encoding luciferase was co-administered as indicated. The particles/DNA were administered to each mouse by direct application to the mouse scruff, with application of ultrasound using the method described in “Protocol 2 for ultrasound methodology” above, for the indicated exposure time and at the specified pressure.
BSA was detected in the skin at either 2 minutes or 24 hours after treatment. Results are shown in
The protein is not significantly cleared after 24 hours.
Particle Synthesis of further Cavitation Agents
Ultrasound-responsive indented particles, synthesised from a range of immunomodulatory and non-immunomodulatory proteins, were prepared according to a modified version of protocol D as follows:
6 ml of a solution of protein having the concentration indicated below was overlaid with 2 ml of a 50/50 mix of hexane/cyclohexane to produce a biphasic solution.
A pre emulsion was formed using a high shear mixer and then passed through a hydrodynamic shearing microfluidizer device at a pressure of 20,000 PSI (138 MPa).
Particles were then freeze-dried for 48 hours, followed by re-suspension in water once again.
The following particles were produced:
Inertial cavitation was demonstrated in vitro for particles of examples 31 to 39 above. Particles were exposed to 1.4 MPa peak pressure for 30 seconds with cavitation energy detected by PCD (
| Number | Date | Country | Kind |
|---|---|---|---|
| 21386010.9 | Feb 2021 | EP | regional |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/GB2022/050250 | 1/31/2022 | WO |
