Patent Application
20120167671
The present invention is related to a testing method and apparatus for the in vitro modelling of the release of the active ingredient from transdermal medicaments.
In vitro methods suitable for the modelling of biological events including the in vivo drug release and absorption-penetration phenomena enjoy distinguished interest in cosmetic as well as pharmaceutical research.
In vitro models have great importance during the development of dermal or transdermal formulations used in dermatology, since the absorption and fate of the active ingredient could only be determined in the skin by great difficulties. Quantitative characterization of the therapeutical effect is a complex task as well. General acceptance of the legal and ethical norms related to the forbearance and protection of animals result in sharp decrease in the use of animal models. Testing of the release of the active ingredient however, has great importance in the case of those formulations which are intended to the release of constant daily amounts of the active ingredient dermally.
Tests related to the release of the active ingredient possess distinguished importance in the following areas:
Testing of the penetration of absorbing ointments has increasing role in the formulation and preclinical evaluation of semisolid dosage forms since 1992.
During the therapeutical application of ointments or other dermal medicaments, three processes occur subsequently or simultaneously: (1) release of the active ingredient from the vehicle; (2) penetration of the active ingredient into the outer layers of the skin; (3) permeation following penetration into the living skin, which is sometimes followed by the absorption of the active ingredient into the circulation. The last process is usually not desired when the formulation is intended for topical or dermal use, but may play very important role when the formulation is designed for systemic effect.
In vitro models suitable for the modeling of the release of the active ingredient from transdermal preparations have been classified by several features. N
1. Methods without a membrane
1.1. Distribution between liquid having opposite polarity
1.2. Open tank method
1.3. Gel diffusion method (agar, gelatine)
2. Rate-controlled/membrane methods
The first group of the models is comprised of those methods wherein no membrane is used, while models wherein a natural or synthetic membrane is used between the sample and receptacle compartment, belong to the second group.
Systems without membrane are suitable for the modeling of the release and, penetration of the active ingredient.
There are three types of models wherein no membrane is applied: (1) testing the partition between phases having opposite polarity; (2) open-container method and (3) gel model of penetration, wherein the diffusion rate into a gelatine or agar gel is determined.
The latter testing method is based on the assay of the active ingredient diffusing into the recipient. The filter positioned above the test preparation serves as barrier rather than means for the control of diffusion.
Test methods applying a membrane are suitable for modelling all the three phases, i.e. release of the active ingredient, penetration and permeation. In the testing apparatus, the donor and acceptor phase are separated by a membrane. Usually the membrane is of apolar character suitable for modelling the biological barrier. The sample is contained in the donor phase. The acceptor phase is usually distilled water or an aqeuous solution (saline or a buffer optionally containing a surfactant or a transport proteing, e.g. albumine).
Methods wherein a membrane is used are usually classified according to the material of the membrane (e.g. human skin or a part thereof, other biological membranes, or an artificial membrane), the test compound (e.g. isotope-labelled active substance) or by the analytical method. In such a test system, the release and penetration of the active ingredient correspond to the entry into the membrane, while permeation is modelled by the diffusion into the aqeuous acceptor phase.
The release of the active ingredient from the formulation and subsequent biological events can be attributed to the following physical-chemical phenomena: (1) dissolution of the active ingredient in the vehicle; (2) diffusion of the dissolved substances; (3) partition between phases having different polarity.
Dissolution of the active ingredient is dependent primarily on the temperature, the concentration of the active ingredient and the dispersity thereof (particle size, shape, particle size distribution).
The distribution process is primarily controlled by the solubility of the active ingredient. Factors like the quality of the dissolving and distributing media, dissolution-improving auxiliary agents, the temperature and the method of dissolution can play important role in the process.
The diffusion process is primarily controlled by the viscosity of the medium, the gel structure and the physical-chemical structure and properties of the active ingredient and method of preparation thereof.
In the membrane apparatuses according to the state of the art, cells suitable for providing equilibrium diffusion are used. These were replaced later by flow cells, which are suitable for the best simulation of in vivo conditions.
The principle of the modelling of equilibrium diffusion resides in that the sampling and assay of the active ingredient after predetermined periods of time can be used for the determination of the amount of the released active ingredient. Similarly, it is possible to determine the proportion of the active ingredient which has diffused through the membrane. Thus studying the release and penetration of the active ingredient as a function of time become possible.
The flow cell model is based on the continuos stream of the acceptor phase by a pump. Said acceptor phase is contacted by the membrane and sampled after predetermined periods of time or the concentration of the active ingredient is monitored and assayed continuously online (e.g. using a spectrophotometer equipped with flow cell).
Among the in vitro models, the Microette™ transdermal diffusion cell designed and manufactured by Hanson is considered the most reproducible and in general, the most suitable for the modelling in vivo conditions. In this apparatus, the compartment containing the test sample (donor compartment) is separated by a special membrane from the acceptor phase. The position of the membrane is either vertical or horizontal and the volume and surface area of the stirred cell can be selected from several variants. It is possible to use several cells at the same time. Sampling and flow control of the acceptor phase is automated and simultaneous in each cell. The temperature of the cells can be kept constant due to the dependence of solubility and diffusion constant on temperature. Similarly, the flow of the acceptor phase is thermostated. Such cells are known from the art as Franz cells [Franz, T.: Curr. Probi. Dermatol. 7, 58-68 (1978)]. The structure of the known cell is shown in
The most important part of the equipment is the penetration cell, wherein the test ointment, gel, cream etc. is present in a closed compartment separated from the acceptor phase by a membrane. The assay of the active ingredient which passed the membrane is usually carried out by high-performance liquid chromatographic analysis in the acceptor phase.
The present invention is based on the recognition that applying the methods and using the apparatus known from the state of the art, the modelling of the behaviour of preparations applied to the skin is not possible. It has been perceived that the environmental factors influence the behaviour of preparations applied to the skin. Thus, the effect of the environmental variables can be modelled by a membrane model wherein the compartment containing the test preparation is open to the environment. Although there is disclosure in the art related to open, equilibrium diffusion apparatus and different kinds of membrane diffusion cells, the state of the art is silent about a penetration apparatus comprising a membrane diffusion cell having open sample compartment. The prior art also lacks disclosure regarding the use of an open sample compartment apparatus in conjunction with controllable environmental conditions.
Furthermore, it has been recognized that methods according to the state of the art do not consider the fact that the properties and composition of the test preparation are not constant during the testing period but they are changing as a function of several environmental factors. Such factors are the quality of the skin area where the test preparation is used (e.g. face or hands are usually exposed to light and air flow; the abdomen or groin are usually covered by clothing and thus isolated from air flow and light); the flow rate and humidity of the air flow in the vicinity of the exposed skin and the temperature difference of the skin compared to the surrounding air; intensity, duration and wavelength of the light exposition of the skin.
Thus it becomes possible to consider and model the effect of environmental conditions according to the body surface (e.g. face generally exposed to air flow and light; abdomen or groin isolated from air and light) where the use of the test preparation is intended.
In many cases, it is necessary to study these relationships in detail, e.g. during the development of the intended therapeutical application (whether a light-protecting, antiinflammatory cream is suitable for its function under extreme environmental or weather conditions, such as during skiing in cold, windy winter weather or during sunbathing in hot, stagnating air in the tropical summer) and in the development of formulation intended for special use (development of climate-withstanding formulations).
The objective of our research-development work was to develop a new testing apparatus and method, which is allows the testing of pharmaceutical formulations applied to the skin under variable environmental conditions using an open compartment membrane penetration method.
In this order, an apparatus and particularly an open sample compartment membrane penetration cell has been constructed.
The apparatus according to the present invention is suitable for the prediction of the in vivo properties of a transdermal pharmaceutical formulation. It is well suited for the approximation of the physiological conditions of the human skin and the transdermal pharmaceutical compositions can be tested under environmental conditions similar to those of the real-time application. Using the apparatus of the present invention, it becomes possible to study the surface effects during the application of transdermal preparation. According to the method of the present invention, testing and in vitro modeling of any transdermal preparation, including but not limited to compositions having high concentration of volatile components, e.g. gels, emulsions, solutions for external use, suspensions, powders, aerosols etc.
The systems and their connections of the apparatus according to the present invention are depicted in
According to a further aspect of the present invention, there is provided a membrane penetration cell having open sample compartment for the test formulation. The cell according to the present invention can be made of any suitable inert material known from the state of the art, considering the properties of the acceptor phase and the test preparation, e.g. steel. The membrane is located on the upper part of the cell body. The membrane is held in place by means suitable for fastening, e.g. a threaded fastening ring or an elastic fastening ring. The cell body, wherein a chamber for the acceptor phase is located, is provided with acceptor phase inlet and outlet and optionally a jacket is provided suitable for attaching a liquid thermostat for temperature adjustment and control (
In one embodiment of the apparatus according to the present invention depicted in the flow chart of
The temperature of the cell is controlled by a convective radiator (C3) made of nickel-plated brass, which is heated/cooled by a heat transfer medium delivered by a liquid thermostat (C4). The heat transfer medium is an antifreeze. The thermostat is electrically heated and if desired, cooling of the heat transfer medium is provided by an external cooling unit. The temperature can be set and controlled with 0.1° C. precision. The temperature sensor (C2) is located in the cell interior. The signal proportional to the cell temperature is delivered to a control circuit (
In the apparatus, a LABOR-MIM ultratermostat (C4, Labor MIM, Esztergom, Hungary) is used with 2 liters of glycerol-distilled water (50:50, v/v) heat transfer medium. The temperature sensor (C2) is a NIVELCO CTFP-121-1 (Nivelco, Budapest, Hungary) Pt/100/B platinum heat sensor, the temperature control (
Any type of membrane suitable for test purposes can be used in the apparatus according to the present invention. It is possible to use natural membranes (e.g. of human origin or obtained from mammals, e.g. swine, rat, rabbit skin or layers thereof, membrane obtained by means of cell propagation etc.) or artificial membranes made of biologically or synthetically obtained materials, e.g. polysiloxane (Silastic), cellulose or derivatives thereof, vinylacetate or acrylate polymers. The apparatus according to the present invention is suitable for the use with skin membranes or membranes comprised of layers of skin (e.g. epidermis, upper dermis, stratum corneum etc.) prepared by dermatomization, heat treatment, chemical or enzymatic treatment etc. Preparation of membranes suitable for the absorption-penetration studies is carried out by using methods known from the state of the art.
The sample of the test formulation is located on the upper surface of the membrane used for modelling of skin or other biological barriers. The amount of the sample is approximately 0.001-0.1 g/cm2 calculated for the area of the membrane.
The sample can be exposed according to the present invention to an air flow having controlled flow rate, temperature and if desired, controlled humidity. The apparatus according to the present invention is suitable to provide an air stream with controlled flow rate at a predetermined temperature and humidity by an air delivery system (compressed air cylinder or central compressor, ventillator, HVAC equipment etc), optionally air cleaning means, temperature controlling system and humidity controlling system. It is also possible to measure and record the heat content and humidity of the air leaving the apparatus according to method known from the art.
According to one embodiment of the present invention, the air flow is provided by a voltage-controlled, variable rpm, low voltage ventillator (A1). The temperature of the air stream is controlled by means of an electric heating unit, air temperature sensor (A2) and control system (
Cooling is possible by feeding the ventillator with pre-cooled air stream and heating thereof by the above-described method. Fast control rate of air temperature is possible by the variable pulse-width square wave controlled, low voltage direct heating element (time constant less than 30 sec).
Air flow rate is controlled by voltage control of the ventillator between 0.5 and 2.5 m/s. Air flow is calibrated as the function of control voltage over the membrane surface.
The temperature of the heating element (A3) is controlled by the signal of the temperature sensor (A2, NIVELCO CTFP-121-1 Pt/100/B platinum heat sensor). The controller (C) is an OMRON E5CSV-R1 T-500 unit. The air flow is provided by an INC A199411 ({hacek over (R)}=40 mm) ventillator controlled by an LM7815 voltage controller. The voltage of the ventillator can be continuously adjusted between 3 and 15 volts. In one embodiment, the relative humidity of the air entering the apparatus is identical to that of the ambient air. However, the air humidity can be controlled using any method known from the prior art.
The test sample applied to the membrane surface can be exposed to light. This facilitates the observation of physical-chemical changes occurring in the sample as well. According to one method, lighting is provided by a light-emitting diode (L1) having similar emission spectrum to sunlight (YOLDAL YZ-WS5S20, Sunny-White, max light intensity 11.000 mcd). The light exposure is measure by a sensor (L2) and the emission of L1 is controlled accordingly. Light intensity can be adjusted by frequency control of the excitation voltage of L1 using an in-house built controller. In this way, the emission spectrum of the LED does not depend on light intensity.
In those cases when the test preparation is subjected to light having different intensity or emission spectrum from that of the normal sunlight (e.g. when the test preparation is applied at high altitudes above the sea level where the intensity of ultraviolet radiation is significantly higher than at sea level), it is possible to substitute the light source with a different one having similar emission spectrum and intensity to that expected under the circumstances of the real-life use.
If desired, alterations of the test preparation resulting from the exposure to environmental factors can be recorded using an imaging method for subsequent evaluation simultaneously with or alternatively to visual inspection.
Penetration measurement is carried out by providing a stream of the acceptor phase with constant flow rate, composition and temperature, causing said stream of the acceptor phase flowing through the penetration cell and determining the concentration of the active or characteristic ingredient of the test preparation in the effluent stream leaving the membrane penetration cell (1) having open sample compartment as a function of acceptor phase volume or time (
Concentration of the active ingredient or that of a characteristic component of the test preparation can be carried out on-line by assaying the analyte concentration with an on-line analytical system (3), e.g. spectrophotometry using an apparatus equipped with a flow-through cuvette. Alternatively, the assay of said analytes can be carried out by sampling the effluent acceptor phase stream at predetermined periods of time or effluent volume and determining the concentration of the analyte using any analytical method (
During the sampling process for the purpose of on-line assay, it is important to keep the outlet of the cell at the same height to that of the membrane to prevent pressure buildup at the membrane.
The delivery of the acceptor phase is preferably carried out by pumping said liquid. For this purpose, any pump can be used which is suitable for the delivery of the acceptor phase at the required flow rate with the desired precision. The flow rate of the acceptor phase during the penetration testing experiments falls within the magnitude of the flow rate of body fluid, e.g. blood flow. However, the flow rate of the acceptor phase can be influenced by the pressure resistance of the membrane used during the testing. During the experiments, the flow rate of the acceptor phase is usually between 0.5 and 3 ml/mm, preferably 0.1 to 0.5 ml/min. The fluctuation of the flow rate must not exceed 1 percent relative to the actual flow rate. Preferably, a volume displacement pump can be used. The inlet and outlet ports of the cell may be provided with suitable threads in order to allow the use of low dead volume tubing and connectors developed for high-performance liquid chromatographic systems.
For example, components of a liquid chromatography system can be used for the delivery of the acceptor phase. An eluent tank can be used as a reservoir for the acceptor phase (E1). Preferably, a heat and chemically resistant glass bottle, e.g. a TORAX glass bottle can be used. The acceptor phase is delivered to the penetration cell by the high-pressure pump of the liquid chromatographic system. Pumps (E2) used in high-performance liquid chromatographic systems can be advantageously used due to their high precision and low flow fluctuation (
It is especially important to prevent any pressure buildup in the cell, since pressure difference disturb the membrane diffusion process. In this order, the cross sectional area of the inlet tubing is kept smaller than that of the outlet tubing, preferably the cross sectional area of the inlet tube is ¼ of the outlet tube.
The acceptor phase is usually a solution suitable for modelling physiological liquids. Suitable acceptor phases are purified water, saline, phosphate-buffered saline or a Ringer-solution.
The acceptor phase is degassed prior to use according to one of the methods known from the art, i.e. sonication or gas purging. Preferably, argon purge is used. If available, the on-line degassing module of a high-performance liquid chromatographic apparatus can be used.
The inventors of the present application used as eluent delivery module of a Shimadzu LC-6A Liquid Chromatograph or Agilent (Hewlett Packard) HP G 1311A high-pressure pump attached to an ERMA ERC-3312 or Agilent (Hewlett Packard) G 1322 A degassing unit are suitable for acceptor phase delivery.
Detectors (S1) having flow cells built for the purpose of liquid chromatography can also be used as means for on-line assay of the analyte (
The control of the apparatus optionally can be carried out by a computerized process control system including the measurement and control of critical parameters, data acquisition and analysis rather than using individual electronic or electromechanic control systems.
It is also possible to build a multitude of cells and sampling/analytical system into one apparatus thus facilitating simultaneous testing.
According to a further aspect of the present invention, there is provided a method for in vitro modelling the release of the active ingredient from a pharmaceutical or cosmetic test preparation, especially the modelling of the absorption-penetration processes.
The method carried out as following. The acceptor phase is filtered and degassed, the cell is degassed and the membrane is attached thereto. After stabilization of flow rate, temperature, air flow and light intensity (usually 1 to 24 hours), the test preparation is transferred to the membrane homogeneously in 1 to 3 seconds. The amount of the test formulation is preferably an amount applied under real-time conditions, or practically one dose unit of the preparation under testing.
Thereafter the flow of the acceptor phase is resumed and in case of on-line analysis, the concentration of the active ingredient of the preparation or that of a characteristic component of the same is recorded. The calculation of the actual concentration can be carried out by external calibration as a function of acceptor phase volume or the elapsed time. From these data, the rate of dissolution is determined. Alternatively, in the case of off-line analysis, fractions are collected and the analyte is assayed in each fraction by a suitable analytical method known from the art. From these data, the amount of the analyte present in the corresponding fraction is determined and the rate of dissolution is calculated.
The test preparation contains 5% troxerutin as active ingredient. In the test, 0.9 weight % sodium chloride solution is used as an acceptor phase. The flow rate of the acceptor phase is 1 ml/min. The membrane used in the testing was cellophane, 10 cm width by 10 cm length. The temperature of the cell is 34° C. The cell is exposed to natural daytime light. In the first (I) test, no artificial air flow is applied. In the second test set (II), the linear air flow rate is 2 msec. The concentration of the active ingredient is determined by ultraviolet spectrometry on-line at the wavelength of 349 nm.
The membrane together with the apparatus is allowed to stabilize for 60 minutes. Thereafter, an amount of approx. 300 mg of the test preparation measured by analytical precision is transferred homogeneously onto the membrane in 2 to 3 seconds. Thereafter the flow of the acceptor phase is resumed and the concentration of the dissolved active ingredient is recorded in the acceptor phase.
The amount of the active ingredient dissolved in test set (I) and (II) are shown in Table 1 (relative to the amount of the active ingredient applied to the membrane).
The test preparation contains 1% piroxicam as active ingredient. In the test, the acceptor phase comprises 0.9 weight % sodium chloride solution. The flow rate of the acceptor phase is 0.3 ml/min. During the first test series (I), a cellophane membrane, during the second test series (II), a human skin membrane was used. Temperature of the cell was kept at 34° C. During both test series, the cell was exposed to natural sunlight. No air flow was applied.
The membrane was allowed to stabilize for 60 minutes.
After the stabilization period, 300 to 400 mg of test preparation measured by analytical precision are applied to the membrane homogeneously in 2-3 seconds. The flow of the acceptor phase is resumed and effluent fractions for periods of 30 minute each are collected. The piroxicam and nipagin M concentration of each fraction is determined by high-performance liquid chromatography. Using the volume and concentration of each analyte, the amounts of piroxicam and Nipagin M are calculated for each fraction.
The high-performance liquid chromatographic analysis is carried out using external standard method in a reversed phase system. The separation is carried out using a Nucleosil C18 (250 mm×4.6 mm i.d.) column and a buffer-acetonitrile-methanol (1000:660:340, v/v/v) mobile phase. The separation is performed at the temperature of 40° C. Flow rate of the mobile phase is 1.0 ml/min. Detection is carried out by ultraviolet photodiode array detector in the wavelength range of 250 to 450 nm. The relative amount of the released piroxicam and Nipagin M (methyl-4-hydroxybenzoate) to the amount applied to the membrane in test series (I) and (II) is given in Table 2.
| Number | Date | Country | Kind |
|---|---|---|---|
| P0900073 | Feb 2009 | HU | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/HU10/00017 | 2/8/2010 | WO | 00 | 10/21/2011 |
