In physical sciences, “plasma” refers to the forth state of matter, while in medicine and biology, plasma is known as the non-cellular component of blood (Fridman et al., 2008). Interestingly, the term “plasma” has been coined by Irving Langmuir to emphasize that the characteristics of ionic liquids ubiquitous in biology and medicine are analogous to plasma in the physical sciences (Fridman et al., 2008, Langmuir, 1928). Despite this historical connection, plasmas are mainly associated with the solid-state processing technology (Stoffels et al., 2003), while being rarely used in biomedical applications directly. This situation is however rapidly changing and multiple plasma applications in life sciences are recently emerging (Daeschlein et al., 2010, Vandamme et al., 2010, Kalghatgi et al., 2010, Kong et al., 2009, Nie et al., 2009, Kalghatgi et al., 2007).
The plasma state can be considered to be a gaseous mixture of oppositely-charged particles with a roughly zero net electrical charge (Denes&Manolache, 2004). Besides charged particles, plasmas also contain neutral atoms and molecules, excited atoms and molecules, radicals and UV photons. Generally, plasmas can be subdivided into 2 categories: thermal plasmas and non-thermal (or cold) plasmas (Denes&Manolache, 2004, Fridman et al., 2008, Bogaerts et al., 2002). Thermal plasmas are characterized by very high temperatures of electrons and heavy particles, both charged and neutral. In contrast, non-thermal plasmas are composed of low temperature particles (charged and neutral molecular and atomic species) and relatively high temperature electrons (Bogaerts et al., 2002, Denes&Manolache, 2004). Because the ions and the neutrals remain relatively cold, a non-thermal plasma does not cause any thermal damage to articles it comes in contact with. This characteristic opened up the possibility to use these non-thermal plasmas for the treatment of heat-sensitive materials including biological matter such as cells and tissues (Laroussi, 2009). Non-thermal plasmas are already routinely used in material processing applications, such as etching, activation and deposition (Borcia et al., 2006, Bruce et al., 2010, De Geyter et al., 2008, De Geyter et al., 2009, Morent et al., 2009a, Morent et al., 2009b, Maruyama et al., 2010). More recently, the biological and medical applications of these plasmas have witnessed a great interest from both plasma as well as medical research communities.
This review paper focuses on one specific fascinating application of non-thermal plasmas in biomedical science, namely the inactivation of bacteria, also called plasma sterilization (Stoffels et al., 2008). We need to stress that the term sterilization is somewhat ambiguous since this term is only used when all initial micro-organisms are killed, which is however not always the case when applying non-thermal plasmas to contaminated surfaces (Boudam et al., 2006). Conventional sterilization methods include the use of dry heat (oven), moist heat (autoclave) or chemicals like gaseous ethylene oxide, liquid formaldehyde and glutaraldehyde (Kelly-Wintenberg et al., 1998, Moisan et al., 2001, Moisan et al., 2002, Park et al., 2003). Some major drawbacks of these conventional techniques are the high processing temperatures (ovens and autoclaves) which makes it impossible to sterilize heat-sensitive materials like polymers, the use of toxic chemicals and the long sterilization times needed (approximately 12 hours in the case of ethylene oxide exposure) (Park et al., 2003, Moisan et al., 2001, Montie et al., 2000). Another interesting sterilization method is the use of gamma irradiation, but this is an expensive technique and may cause the material to undergo undesirable changes during sterilization (Moisan et al., 2001, Henn et al., 1996, Ishigaki&Yoshii, 1992). The limitations of these conventional methods have encouraged the search for new approaches and an alternative method of sterilization is treatment with a non-thermal plasma (plasma sterilization). These plasmas operate under moderate temperatures and use non-toxic gases, therefore, thermal and chemical damage to the substrate is limited (Philip et al., 2002, Sladek&Stoffels, 2005). Moreover, plasmas are not only capable of killing bacteria and viruses, they can also remove these dead micro-organisms from the surfaces of the objects being sterilized (Chau et al., 1996). This chapter on plasma sterilization is organized as follows: a first part will focus on the inactivation of bacteria on non-living surfaces, which has reached a state of maturity. In this first section, the kinetics of bacterial inactivation processes will be described, followed by the effects of various plasma-generated agents on bacterial cells. Afterwards, a brief review on the inactivation of bacteria on non-living surfaces by vacuum and atmospheric pressure plasmas will be presented. A second part of the chapter will deal with state-of-the-art applications of non-thermal plasmas in bacterial inactivation, namely the sterilization of teeth and human/animal tissue, which are both relatively new research topics.
2. Plasma sterilization on non-living surfaces
2.1. Survival curves to determine the inactivation efficiency
Plasma effects on micro-organisms can be evaluated using various methods, however, a commonly used approach is the determination of survival curves (Stoffels et al., 2008, Boudam et al., 2006, Moisan et al., 2002). These curves are plots of the logarithm of the number of surviving micro-organisms as a function of exposure time to the sterilizing agent. Although the precise procedures to obtain these curves may vary, usually a suspension containing a well-defined concentration of micro-organisms is placed on a substrate and let to dry. After plasma exposure, the remaining micro-organisms are let to inoculate for several hours before counting. Considering that counting large numbers of cells is troublesome, the number of colony forming units (CFU) is determined instead of counting individual cells after inoculation (Stoffels et al., 2008). For conventional sterilization methods, the survival curve is usually a unique straight line: the inactivation process is an exponential function of time (Moisan et al., 2002, Cariou-Travers&Darbord, 2001). In contrast, plasma sterilization can provide survival curves with different shapes depending on the type of micro-organism, the type of medium supporting the micro-organisms and the method of plasma exposure (direct or remote) (Laroussi et al., 2000, Laroussi, 2002). In some cases, the survival curves after plasma exposure are straight lines (similar to conventional sterilization methods) (Laroussi et al., 2000, Herrmann et al., 1999, Yamamoto et al., 2001), however, in most cases, two or even three different linear segments occur, each segment being a different inactivation phase (Kelly-Wintenberg et al., 1998, Moisan et al., 2002, Laroussi et al., 2000). This implies that the number of surviving micro-organisms is also an exponential function of time, but with different time constants. To characterize the slope of each segment, an interesting parameter has been extensively used by several researchers studying plasma sterilization: the so-called “D-value” (decimal value) (Moisan et al., 2002, Laroussi, 2002, Fridman, 2008). This parameter is the time required to reduce an original concentration of micro-organisms by 90 % (one log10 reduction) and is expressed in the unit of time.
Single-slope survival curves have been observed in atmospheric pressure plasma sterilization by Herrmann et al. (Herrmann et al., 1999), Laroussi et al. (Laroussi et al., 2000) and Yamamoto et al. (Yamamoto et al., 2001) and an example of such a single-slope curve is presented in Figure 1.
Herrmann et al. (Herrmann et al., 1999) employed a remote atmospheric pressure plasma jet in a helium/oxygen mixture to treat
Two-slope survival curves can occur in both vacuum and atmospheric pressure plasma sterilization and were observed for the first time in 1998 by Hury et al. (Hury et al., 1998). These authors reported on the inactivation of different
As previously mentioned, two-slope survival curves have also been observed in atmospheric pressure plasmas. Kelly-Wintenberg et al. (Kelly-Wintenberg et al., 1998) and Laroussi et al. (Laroussi et al., 2000) employed an atmospheric pressure glow discharge (DBD) for the inactivation of
Montie et al. (Montie et al., 2000) found similar survival curves for the inactivation of
Multi-slope survival curves with three (or more) linear segments have also been observed in both vacuum as well as atmospheric pressure plasma sterilization. Moreau et al. (Moreau et al., 2000), Moisan et al. (Moisan et al., 2002) and Philip et al. (Philip et al., 2002) found three inactivation phases when employing a low pressure (133-933 Pa) microwave discharge in argon/oxygen and N2/O2 mixtures (0.7-2 % oxygen) respectively for the inactivation of
These multi-slope survival curves were also recorded by Laroussi et al. (Laroussi et al., 2000) and Roth et al. (Roth et al., 2000) who employed atmospheric pressure plasma sources for sterilization, however, a clear elucidation for this type of survival curve is lacking for the moment. The explanation given earlier for low pressure plasma sterilization is most likely not applicable to atmospheric pressure plasmas, for which it has been shown that UV photons only play a secondary role in the killing process (Herrmann et al., 1999, Yamamoto et al., 2001, Kostov et al., 2010, Laroussi, 1996). Based on the above-mentioned bacterial inactivation kinetics, one can conclude that the mechanisms of sterilization by both vacuum and atmospheric pressure plasmas are very complex and far from understood at this moment.
2.2. Plasma species responsible for sterilization
As mentioned at the end of the previous section, plasma sterilization is a complex process since multiple plasma species, such as UV photons, excited species, reactive neutrals,… can interact with the bacterial cells being treated. This section tries to give an overview of the contributions of various plasma agents (heat, UV radiation, charged particles and reactive species) to the sterilization process.
2.2.1. Effect of heat
The first factor that usually comes to mind when discussing sterilization is the effect of heat. As previously mentioned, conventional sterilization methods are based on the use of either dry or moist heat. Moist heat (or autoclaving) is widely used for sterilization by subjecting objects to steam under pressure at temperatures of at least 120 °C for 15 minutes or longer (Gopal, 1978, Ratner et al., 1990). Dry heat sterilization requires even higher temperatures (close to 170 °C) with treatment times of about one hour (Laroussi, 2005). Most non-thermal plasmas operate at low temperatures (room temperature to approximately 70°C), therefore, no substantial thermal effects on bacterial cells are expected in plasma sterilization processes (Laroussi&Leipold, 2004). However, it should be noted that some non-thermal plasmas (like gliding arc discharges and dielectric barrier discharges) can be characterized by elevated temperatures in localized intervals in space or in time and for these discharges thermal effects should be sometimes also taken into account ( Fridman, 2008 ). However, in general, heat is not a major contributor to the sterilization effect in non-thermal plasmas.
2.2.2. Effect of UV radiation
Non-thermal plasmas are a source of UV with different wavelengths, however, only UV radiation in the 200-300 nm wavelength range with doses of several mJ/cm2 are known to cause lethal damage to cells (Fridman, 2008, Laroussi, 2005). This damage is mainly the dimerization of thymine bases in bacterial DNA strands, which inhibits the ability of bacteria to replicate properly (Fridman, 2008, Laroussi, 2005).
The presence of UV radiation in the plasma strongly depends on the operating pressure. It is well-known that vacuum plasma discharges are able to provide significant UV radiation in the range of wavelengths effective in sterilization. This can explain the important contribution of UV radiation in plasma sterilization at low pressures, as discussed in the previous section. In contrast, the great majority of papers published on the inactivation of micro-organisms by atmospheric pressure plasmas conclude that the contribution of UV radiation to the inactivation process is not important, when not at all relevant. By comparing the killing kinetics of UV radiation from a low pressure mercury-vapour lamp with that of a glow discharge plasma at atmospheric pressure, Laroussi et al. (Laroussi, 1996) concluded in 1996 that UV was not the main killing agent. In 1998, this claim was supported by Kelly-Wintenberg et al. (Kelly-Wintenberg et al., 1998) who exposed different types of micro-organisms to an atmospheric pressure glow DBD in air. These authors observed that there is no significant difference in the time needed to inactivate micro-organisms on polypropylene samples, whether exposed directly or sealed in bags. They concluded from this observation that UV is not a significant contributor to lethality since the opaque bags would have blocked much of the UV light (Kelly-Wintenberg et al., 1998). In the following years, several researchers (Laroussi, 2002, Laroussi, 2005, Choi et al., 2006, Laroussi&Leipold, 2004, Birmingham, 2004) have carried out various experiments that also supported the claim that UV plays a minor role in plasma sterilization. In 1999, Herrmann et al. (Herrmann et al., 1999) exposed
In contrast to the previous literature overview, some authors (Park et al., 2003, Heise et al., 2004, Lee et al., 2005, Trompeter et al., 2002) do mention the possible role of UV photons in plasma sterilization at atmospheric pressure, however, the arguments brought forward are quite often not fully convincing or incomplete (Boudam et al., 2006). For example, Trompeter et al. (Trompeter et al., 2002) employed an atmospheric pressure filamentary DBD in different gases and found that argon was the most efficient gas in terms of spore inactivation. As a result, they concluded that the inactivation process is purely due to UV radiation since argon is chemically inactive. Heise et al. (Heise et al., 2004) employed a similar discharge in argon and claimed that the inactivation of spores is partly due to UV-induced effects. Both Trompeter et al. (Trompeter et al., 2002) and Heise et al. (Heise et al., 2004) present their results as being performed in pure argon, nonetheless this is not the case since impurities are always present in the discharge gas (Boudam et al., 2006). This contamination can strongly reduce the UV emission (Boudam et al., 2006), therefore, the role of UV in the inactivation process might not be as large as mentioned by these authors. Recently, Boudam et al. (Boudam et al., 2006) subjected micro-organisms to an atmospheric pressure DBD operated in an N2/N2O2 mixture. These authors claim that they have proven that UV photons, under specific operating conditions, can be the dominant inactivation species. The role of UV in atmospheric pressure plasma sterilization is thus still open for debate and further research should be definitely conducted before the controversy can be resolved.
2.2.3. Effect of reactive species
According to several authors (Laroussi, 2002, Laroussi, 2005, Fridman, 2008 ), reactive neutral species (such as O, O2*, O3, OH•, NO and NO2) can make a significant contribution to the plasma sterilization process, especially at high pressures. To show the effect of these reactive species on the destruction of bacteria, Laroussi and Leipold (Laroussi&Leipold, 2004) employed an atmospheric pressure DBD in three different gases: pure helium, 97% helium-3% oxygen mixture and air to inactivate
When pure helium was used as discharge gas, the surviving spore population percentage was still much greater than 10% after 10 minutes of plasma treatment. In fact, in this case, the D-value was greater than 20 minutes. When a helium/oxygen mixture was employed, as shown in Figure 5, a D-value of 10 minutes was achieved. Laroussi and Leipold (Laroussi&Leipold, 2004) also showed that in the case of an air plasmas, the D-value could be even further decreased to approximately 20 seconds. According to these authors, this dramatic decrease in inactivation efficacy can thus be attributed to the presence of chemically reactive species such as NO, NO2, O, O3,… Besides Laroussi and Leipold, other authors (Herrmann et al., 1999, Moreau et al., 2000, Richardson et al., 2000) have also experimentally shown that discharges containing oxygen provide a strong germicidal effect. In particular, Herrmann et al. (Herrmann et al., 1999) compared results obtained by an atmospheric pressure plasma jet with and without oxygen. These authors found that the D-value in the case of absence of oxygen is higher than in the case when oxygen is added. Richardson et al. (Richardson et al., 2000) also showed that their resistive barrier discharge became more effective in killing
2.2.4. Effect of charged particles
In the discussion of the mechanisms of inactivation, a lot of attention is given to the effect of UV radiation and reactive species and most researchers have neglected to investigate the influence (if any) of charged particles. As a result, the exact role of electrons and ions is not yet fully resolved, but there are several indications of their importance. Fridman et al. (Fridman et al., 2007, Fridman, 2008) have stated that charged particles play an essential role in sterilization, especially in the case of direct plasma treatment, i.e. when the plasma is in direct contact with the micro-organisms. These authors employed an atmospheric pressure air DBD in direct mode and afterglow mode (so-called “plasma jet”) at similar discharge powers and with the same amount of UV radiation and the results comparing the direct and indirect effects of plasma sterilization are illustrated in Figure 6. From this figure, it can be clearly seen that direct application of plasma yields a better sterilization efficiency than the treatment by plasma afterglow. Although this high efficiency in the direct mode cannot be solely described to the role of charged particles (the concentration of reactive species is also lower in case of indirect exposure), it could be possible that charged-induced mechanisms contribute to the sterilization process in direct plasma exposure.
Mendis et al. (Mendis et al., 2000) also suggested that charged particles might play a significant role in the rupture of outer cell membranes. According to these authors, charge accumulation on the outer surface of the membrane induces an electrostatic force, which can overcome the tensile strength of the membrane causing its rupture. They also state that this mechanism is only effective for Gram-negative bacteria, which posses thin outer membranes and a thin murein layer. The scenario will probably not occur for Gram-positive bacteria, which lack an outer membrane but have a much thicker murein layer thereby providing these bacteria higher strength and rigidity. Their conclusions can be supported by several experimental observations. Kelly-Wintenberg et al. (Kelly-Wintenberg et al., 1999) employed an atmospheric pressure glow discharge for the inactivation of the Gram-negative
2.3. Vacuum plasmas
Glow discharge plasmas operated in vacuum have been successfully employed to sterilize surfaces for quite some time. Patents written by Ashman and Menashi (Ashman&Menashi, 1972) as well as by Gut Boucher (Gut Boucher, 1980) showed that an electrical discharge in an appropriate gas can lead to sterilization. In these patents, samples are inserted within a chamber which is subsequently evacuated with a pump to 1-5 Pa. Afterwards, this chamber is filled with gas set at the required pressure, typically 5-300 Pa. The gas discharge is then achieved by applying an RF field to the gas by means of a coil located on the outside of the chamber. Ashman and Menashi (Ashman&Menashi, 1972) used different discharge gases, such as chlorine, bromine, iodine, water vapour, oxygen and nitrogen, but only observed an effective sterilizing effect when halogens were used as discharge gas. Gut Boucher (Gut Boucher, 1980) added aldehyde vapours to different carrier gases (oxygen, argon or nitrogen) and observed the best results with oxygen as carrier gas. In 1987, Jacobs and Lin (Jacobs&Lin, 1987) employed a similar RF discharge in a two-step process: (1) injection and contact of hydrogen peroxide (H2O2) with the item being sterilized; (2) application of an RF discharge to ensure that no toxic residues remain on the sterilized item. It is however important to note that the previously mentioned systems are not really plasma-based sterilization systems due to the use of gas mixtures that contain components with germicidal properties (such as H2O2 and aldehydes) before the plasma is ignited (Laroussi, 2005). Nevertheless, some of these sterilization systems have been commercially available since the 1990s (Montie et al., 2000, Rutala et al., 1998, Vassal et al., 1998).
One of the first reports on plasma sterilization where gases were used with no germicidal properties on their own was published in 1976 by Fraser et al. (Fraser et al., 1976). These authors employed a low pressure RF discharge in different gases (argon, nitrogen, oxygen, helium,…) and obtained reductions in spore populations of 99% after 2 minutes of plasma exposure. However, it was not specified for which discharge gas this result was obtained. A few years later, in 1982, Bithell (Bithell, 1982) observed that articles placed in a porous envelope could be sterilized in a low pressure (40 Pa) oxygen RF plasma after a plasma exposure time of 60 minutes. In 1989, Nelson and Berger (Nelson&Berger, 1989) also claimed that an oxygen RF plasma is very effective as biocidal medium.
Different authors have examined which discharge gas would be the most efficient to inactivate bacterial spores. Hury et al. (Hury et al., 1998) compared the mortality of
Taking into account the high efficiency of oxygen-based plasmas, literature on low pressure sterilization has mainly focused on these kind of plasmas, nevertheless, inert gas plasmas are in some cases still employed for bacterial inactivation (Liu&Chen, 2008, Yang et al., 2009). Recently, many studies (Bol'shakov et al., 2004, Boscariol et al., 2008, Cvelbar et al., 2006, Liu et al., 2008, Nagatsu et al., 2003, Rossi et al., 2008, Singh et al., 2009, Vicoveanu et al., 2008) on the effects of pure oxygen vacuum plasmas on bacteria have been conducted. Bol'shakov et al. (Bol'shakov et al., 2004) published an interesting paper on the use of an oxygen RF plasma for sterilization purposes. The study was carried out for two operational modes: the inductively coupled mode and the capacitively coupled mode and it was found that the inductive mode offers a better efficiency in destroying bacterial cells. Rossi et al. (Rossi et al., 2008) also employed a low pressure oxygen RF discharge for the inactivation of
As can be seen, the size of the spores is significantly reduced after 2 minutes of plasma treatment. According to the analysis of a statistically relevant number of spores done on the SEM pictures, it was found that in these conditions the mean length of the spores was reduced from 1.73 to 1.35 μm. Similar results were obtained by Nagatsu et al. (Nagatsu et al., 2003) and Singh et al. (Singh et al., 2009), who employed a low pressure oxygen microwave discharge. They experimentally confirmed that the
Pure oxygen plasmas have also been employed by Cvelbar et al. (Cvelbar et al., 2006) and Vicoveanu et al. (Vicoveanu et al., 2008) for the inactivation of
Besides pure oxygen plasmas, also low pressure N2/O2 plasmas have been widely investigated for the inactivation of bacteria (Moisan et al., 2002, Philip et al., 2002, Moreau et al., 2000, Rossi et al., 2006, Villeger et al., 2003, Villeger et al., 2005). Moreau et al. (Moreau et al., 2000) and Moisan et al. (Moisan et al., 2002) carried out detailed studies on the effects of a low pressure N2/O2 microwave plasma with biological samples placed in the afterglow of the discharge. Total inactivation of
2.4. Atmospheric pressure plasmas
Although the use of vacuum plasmas can be considered as a significant improvement over existing sterilization methods, there are still several drawbacks, including the need for batch processing, long processing times and high costs. As a result, in the past decades, interest has grown in applying atmospheric pressure plasmas for sterilization purposes and several methods have been developed that allowed researchers to easily generate non-thermal plasmas at high pressures, up to one atmosphere (Laroussi, 2005). In the following sections, the most commonly used atmospheric pressure plasmas sources for sterilization purposes will be briefly discussed together with some important results obtained for each of these discharge types.
2.4.1. Dielectric barrier discharge (DBD)
A widely used atmospheric pressure discharge for bacterial inactivation is the dielectric barrier discharge (DBD). In most cases, the plasma is created between closely spaced parallel plates, where one or two plates are covered by a dielectric layer (Kogelschatz et al., 1997, Kogelschatz, 2003). DBDs are generally driven by AC high voltages with frequencies in the kHz range and power consumptions between 10 and 100 W (Stoffels, 2007). Usually, a DBD operates in the filamentary mode: the breakdown starts at many points, followed by the development of independent current filaments, named microdischarges (Kogelschatz et al., 1997, Kogelschatz, 2003). However, it has been demonstrated that a homogeneous discharge can be obtained under special, quite restrictive conditions [83,84]. DBDs can be used for bacterial inactivation, but the narrow spacing between the electrodes makes it difficult to introduce thick samples. For these samples, remote DBD treatment can however be employed.
Laroussi et al. (Laroussi et al., 1999) demonstrated that a homogeneous helium/air DBD is effective for the inactivation of
Besides DBDs in the homogeneous mode, also filamentary discharges have been employed for the sterilization of various bacteria (Kostov et al., 2010, Heise et al., 2004, Trompeter et al., 2002, Hahnel et al., 2010, Yasuda et al., 2008). Kostov et al. (Kostov et al., 2010) and Yasuda et al. (Yasuda et al., 2008) were able to achieve sterilization of
To enable the internal sterilization of complicated medical instruments, such as breathing circuits, catheders and endoscopes, different authors have developed special DBD configurations (Eto et al., 2008, Pointu et al., 2008, Sato et al., 2008). Eto et al. (Eto et al., 2008) developed a so-called “linear DBD” with a diameter of 0.2-3 mm and a length of 40 cm and found that 106
2.4.2. Atmospheric pressure plasma jets
Since the 1990s, an increasing interest in plasma jets for bacterial inactivation has been registered. Numerous plasma jets with different features have been developed and described in literature (Herrmann et al., 1999, Laroussi et al., 2006, Shimizu et al., 2008, Stoffels et al., 2006). These jets all differ in design, size, working gas, frequency of applied voltage,… but the principle is the same. The plasma is ignited inside a nozzle equipped with one or two electrodes and expands outside the nozzle via a gas flow. Atmospheric pressure plasmas jets are very practical due to their small size and light-weight plasma generation unit. They can be employed to treat small-sized objects, but can also be used for large-scale treatments by moving the jet over the selected area or by applying multiple nozzles next to each other. The following section will focus on the most important atmospheric pressure plasma jets employed for bacterial inactivation, however, it is important to mention that also other types of plasma jets have been developed for disinfection purposes (Shimizu et al., 2010, Chiang et al., 2010, Ikawa et al., 2010, Lee et al., 2005, Liu et al., 2010, Kim et al., 2009, Huang et al., 2007).
One type of plasma jet, which is actively employed for bacterial sterilization is the so-called “atmospheric pressure plasma jet (APPJ)”. The design and operation of the APPJ have been already discussed in detail elsewhere (Jeong et al., 1998, Park et al., 2000, Schutze et al., 1998) and are only briefly summarized here for completeness. The APPJ consists of two coaxial electrodes between which a feed gas (mixtures of helium, oxygen and other gases) flows at high rate (50-100 litres per minute gas flow) and is schematically presented in Figure 11. By applying RF power (50-100 W) at 13.56 MHz to the inner electrode, a spatially uniform discharge is ignited. The chemically active species, such as excited atoms, excited molecules and free radicals exit the nozzle at high velocity (jet length of 10 mm) and impinge on the substrate being sterilized. Due to cooling by the high gas flow, the effluent temperature can be kept at moderate levels (100 °C). The ions and electrons quickly recombine outside the jet and are most likely not active in the bacterial inactivation process. Herrmann et al. (Herrmann et al., 1999) used the APPJ in a helium-oxygen mixture to inactivate spores of
A miniature jet was recently developed by Laroussi et al. (Laroussi et al., 2006, Lu&Laroussi, 2006), who named their new plasma source “plasma pencil”. The plasma pencil is basically a 2.5 cm diameter dielectric tube where two disk electrodes of about the same diameter as the tube are inserted. The electrodes are separated by a gap that can be varied from 0.5 to 1.0 cm and consist of a thin copper ring attached to the surface of a centrally perforated dielectric disk. To ignite the plasma, sub-microsecond square high voltage pulses at repetition rates in the 1-10 kHz range are applied between the two electrodes and a gas mixture (such as helium/oxygen) is flown through the holes of the electrodes (flow rates between 1 and 10 litres per minute). When the discharge is ignited, a plasma plume with lengths up to 5 cm is launched through the hole of the outer electrode in the surrounding air. Figure 12 shows a photograph of the plume emitted by the plasma pencil. This plasma plume remains stable and maintains at room temperature for extended operating times. As a result, the plume can be touched by bare hands without any harm.
Preliminary experiments (Laroussi et al., 2006) have been recently carried out to test the effectiveness of the plasma pencil to inactive bacteria. In this study,
Recently, the biomedical team at the Eindhoven University of Technology has introduced another concept of a miniature atmospheric plasma jet: the “plasma needle” (Stoffels et al., 2002, Stoffels et al., 2006). The portable plasma needle consists of a metal wire (0.3 mm diameter) with a sharpened tip, confined in a Perspex tube (4 mm inner diameter). RF power at 13.05 MHz ranging between 10 mW and several watts can be applied to the needle resulting in the generation of a micro-plasma (0.1-2 mm glow size). In the 10-300 mW regime, the gas temperature is close to body temperature, while above 1 W, it can increase to 100°C and more (Stoffels, 2007). Because the voltage necessary to ignite the discharge is the lowest in helium, the plasma needle operates in helium-air mixtures. The Perspex tube is filled with helium at flow rates between 0.5 and 2.0 litres per minute, while the air content can be adjusted by pushing the needle in or out the Perspex tube: the more the needle protrudes from the tube, the more air can enter the plasma region (Sladek&Stoffels, 2005). A photograph of the portable plasma needle and a close-up of the metal wire inside the Perspex tube can be seen in Figure 14.
Sladek et al. (Sladek&Stoffels, 2005, Sladek et al., 2006 ) employed the plasma needle for the inactivation of
An atmospheric pressure plasma jet with a special design has been developed by Shimizu et al. (Shimizu et al., 2008) and applied for the inactivation of
3. Plasma sterilization of animal and human living tissue
3.1. Plasma sterilization in dentistry
Dental cavities, as the result of caries, are a common ailment and the improvement of current treatment methods is a major issue in dentistry (Sladek et al., 2004). Preparation of cavities prior to filling is done by removing necrotic, infected and non-remineralizable tissue by means of mechanical drilling or laser techniques (Banerjee et al., 2000). In both methods, heating takes place. Moreover, vibrations occur during mechanical drilling, which is usually quite painful for the patient since both heating as vibrations can stimulate the nerve (Banerjee et al., 2000). Moreover, these methods are often destructive: fractures can occur and an excess of healthy tissue must be removed to ensure that the cavity is free of bacteria (Sladek et al., 2004). A non-thermal atmospheric pressure plasma might offer a less destructive and less painful method to prepare dental cavities. These plasmas operate at room temperature and do not cause pain or bulk destruction of the tissue. Moreover, although the plasma is superficial, the active plasma species it produces can easily reach the inside of the cavity. Goree et al. (Goree et al., 2006b, Goree et al., 2006a) have employed the plasma needle to kill
More recently, Jiang et al. (Jiang et al., 2009) have developed a hollow-electrode-based, 100ns-pulsed plasma dental probe that generates a tapered cylindrical plasma plume at room temperature in ambient atmosphere. This plasma plume causes minimal heating of biological materials and can be touched with bare hands without causing burning sensation or pain. After the developing phase, Jiang et al. (Jiang et al., 2009) used the plasma dental probe to disinfect root canals from extracted human teeth. For this purpose, two teeth were placed 5 mm below the plasma dental probe nozzle. One tooth was exposed to the helium/oxygen plasma for 5 minutes, while the other tooth, serving as control, was exposed to a similar helium/oxygen flow for the same amount of time, but with the plasma switched off. After treatment, the treated and control tooth were longitudinally and transversely split with a dental burr and subsequently examined with SEM, as shown in Figure 16. It can be clearly seen that in the case of the control tooth, biofilms cover the entire root canal surface. However, in the plasma-treated root canal, a distinct zone without biofilms (1 mm in depth) can be observed. However, the plasma failed to reach the lower zone. Nevertheless, the authors state that greater sterilization depth can be achieved by optimizing the width and the length of the plasma plume. Another solution to a better killing efficacy in root canals was provided by Lu et al. (Lu et al., 2009), who constructed a cold plasma jet device which is able to generate plasma inside the root canal. It was found that this device efficiently kills
3.2. Plasma sterilization of human/animal skin
Another interesting state-of-the-art application of non-thermal plasmas is the sterilization of human or animal skin, however, this is a recently developed research topic and has up to now only been examined by the research group of Alexander Fridman. In a hospital setting, sterilization of living animal or human tissue with minimal damage to this tissue is of great importance. Nowadays, chemical sterilization is commonly employed, however, this technique does not always offer a solution. For example, it cannot be used for the sterilization of open wounds, ulcers or burns due to the extent of damage they cause to punctured tissues. Transporting chemicals for sterilization can also become a major logistics problem for example in a military field hospital (Fridman, 2008). Non-thermal atmospheric pressure plasma sources can offer an interesting alternative since it is quite a potent disinfecting and sterilizing agent, as extensively discussed in the previous sections. As previously mentioned, it is crucial that the living tissue does not get damaged during plasma treatment, therefore, the discharge current should be limited below values acceptable for treatment of living tissue. Moreover, the discharge itself should be homogeneous enough to avoid local damage and discomfort (Fridman, 2008). The creation of special atmospheric pressure discharges effectively solving these problems is an important challenge and until now, only a few researchers succeeded in developing a non-thermal plasma suitable for living tissue sterilization. Fridman et al. (Fridman et al., 2006) especially developed a discharge for this purpose: the so-called floating-electrode DBD (FE-DBD). Similar to the classical DBDs, the set-up consist of two electrodes: a dielectric-protected powered electrode and a second active electrode, which can be human or animal skin or an organ. This latter electrode is not grounded and remains at a floating potential. The discharge ignites when the powered electrode approaches the surface to be treated at a distance of less than 3 mm, depending on the form, duration and polarity of the driving voltage. Figure 17 shows a photograph of the FE-DBD with human tissue as floating electrode.
Recently, the FE-DBD has been further optimized to minimize the DBD non-uniformities and the related damaging effects. The best results were obtained when the FE-DBD was employed in the pulsed mode with pulse durations below 30-100 ns, resulting in sufficient uniformity and the possibility of non-damaging direct plasma treatment of living tissue (Ayan et al., 2009). Fridman et al. (Fridman et al., 2006) investigated human tissue sterilization by subjecting bacteria collected from cadaver skin containing
During the last decades, the plasma community has witnessed a burst of research activity on the germicidal properties of both low pressure as well as atmospheric pressure non-thermal plasmas. While vacuum-based plasma sterilization is an already well-established technology, the use of atmospheric pressure cold plasmas for the inactivation of bacteria is a relatively recent event. As a result, there are still a lot of issues in atmospheric pressure plasma sterilization that need more in-depth investigations. For example, there is still no complete understanding of the biological pathways that cold atmospheric pressure plasmas induce in cells and tissues during treatment. Although preliminary results are very promising, a lot of work requiring collaborative efforts between plasma scientists, microbiologists and biochemists remains to be done before plasma can establish itself as a technique being routinely and effectively used for sterilization purposes. Despite all these challenges, non-thermal plasmas have undoubtedly great potential as a novel method for low temperature sterilization. Due to the growing amount of information and expertise on this subject, it seems to be most likely that real life applications of non-thermal plasmas for sterilization purposes will become a reality in the near future.
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