Many bacteria secrete a highly hydrated framework of extracellular polymer matrix on suitable substrates and embed within the matrix to form a biofilm. Bacterial biofilms are observed on many medical devices, endocarditis, periodontitis and lung infections in cystic fibrosis patients. Bacteria in biofilm are protected from antibiotics and >1,000 times of the minimum inhibitory concentration may be required to treat biofilm infections. Here, we demonstrated that shock waves could be used to remove Salmonella, Pseudomonas and Staphylococcus biofilms in urinary catheters. The studies were extended to a Pseudomonas chronic pneumonia lung infection and Staphylococcus skin suture infection model in mice. The biofilm infections in mice, treated with shock waves became susceptible to antibiotics, unlike untreated biofilms. Mice exposed to shock waves responded to ciprofloxacin treatment, while ciprofloxacin alone was ineffective in treating the infection. These results demonstrate for the first time that, shock waves, combined with antibiotic treatment can be used to treat biofilm infection on medical devices as well as in situ infections.
Shock wave is a high energy wave travelling at supersonic speed, which is characterized by an abrupt change in pressure, temperature and density of the traversing medium. Unlike pressure wave, a shockwave is a single event of energy dissipation thus; no frequency is associated with it. They are generated in nature whenever the different elements in a fluid approach one another with a velocity higher than the local speed of sound at the present temperature. The unique character has widened the landscape of shock wave applications. Shock waves initially utilized in Aerospace research have found importance in bioengineering where extracorporeal shock waves are used as a non-invasive therapy in lithotripsy, wound healing and for treating avascular necrosis1,2,3. Previously we have used shock waves for vaccination, bacterial transformation and for drug delivery4,5,6,7. A few reports suggest that laser generated and extracorporeal shock waves can cause damage to the biofilm in vitro8,9,10,11,12, however the effects of shock waves on biofilms and the use of these shock waves as a therapy has not been reported.
It is now recognised that many infections are initiated from biofilms13,14. The US Centers for Disease Control and Prevention and National Institutes of Health have estimated that between 65–80% of infections are caused from biofilms15. A biofilm is an accumulation of microorganisms embedded in a Polymeric substance matrix that is adherent to a solid biologic or non-biological surface13,14. Bacteria contained within biofilms show resistance to antibiotics that is non-intrinsic. When the bacteria are released from the biofilm for planktonic growth, these same bacteria may be inherently sensitive to concentrations 1,000–10,000-fold less than those required to kill bacteria contained with the biofilm16.
Biofilms can be formed on most medical devices including urinary catheters, central venous catheters, peritoneal dialysis catheters, intrauterine devices, endotracheal tubes, prosthetic joints, voice prosthesis, mechanical heart valves and pacemakers17,18,19,20 by a wide variety of bacteria including Escherichia coli, Pseudomonas aeruginosa and Staphylococcus aureus. Contamination could be avoided in some of the devices by providing maximal sterile condition during insertion21.
Many pathogenic bacteria can form biofilms in or on tissues; these in situ biofilms cause inflammation and tissue damage22. These biofilms may form on surface of tonsils23 and on respiratory tract surfaces e.g. the paranasal sinuses24 etc. Planktonic bacteria released from these biofilms can intermittently or continually disperse to cause chronic infections, or infections at sites distal to the biofilm.
Here, we have successfully demonstrated the use of two different shock wave generators for the disruption of biofilms formed in vitro as well as in vivo conditions. The biofilms formed by Salmonella, Pseudomonas and Staphylococcus on urinary catheter surfaces have been exposed to shock waves produced by a hand-held device. A diaphragmless shock tube has been used for in vivo treatment of Pseudomonas lung infection and Staphylococcus skin suture infection in mice. This is first time that, an in vivo study of shock wave treatment of biofilms has been presented. The shock waves generated for the in vivo study are low amplitude and repeatable. The studies show that, in combination with antibiotic therapy, shock waves have the potential to treat lung and skin infections caused by bacteria.
Biofilms were grown on different substrates including plastic tubes and urinary catheters, using Gram positive and Gram negative bacteria including Salmonella enteric serovar Typhimurium (S. Typhimurium), Pseudomonas aeruginosa (P. aeruginosa) and Staphylococcus aureus (S. aureus). The extent of biofilm formation on urinary catheters was determined using scanning electron microscopy (SEM) and crystal violet staining (Fig. 1). All the tested bacteria formed biofilms under the conditions used. Biofilms were grown in the presence of urine on urinary catheters as determined by SEM (Fig. 1a–d) and the increase in biomass attached to the catheter surface was seen by crystal violet staining for biofilms25 (Fig. 1e).
Generation of shock waves using hand-held device
For the in vitro studies, shock waves were generated using a hand-held shock wave generator (Fig. 1f)4,5,6. When the polymer tube is ignited at one end, a combustion front travels through the length of the tube and shock waves are generated at the other end (Fig. 1g). A typical shock wave pressure signal measured head on at a distance of 20 mm from the end of the tube is shown in (Fig. S1). The energy in the shock wave emanating from the open end of the polymer tube is estimated to be around 1.25 J (Table 1)26. The various parameters of the hand held shock wave generator are tabulated in table1. This mode of shock wave generation is ideal for in vitro study as it is a simple way to handle this portable device. The polymer tube was inserted to a 2 ml screw cap tube to generate shock waves and disrupt the biofilm.
Impact of shock waves on biofilms on tubes and catheters
The effect of a shock wave on biofilm maintenance was determined. The biofilms of S. Typhimurium (Fig. 2a), P. aeruginosa (Fig. 2b) and S. aureus (Fig. 2c) were initially grown in plastic screw cap tubes. SEM revealed that the biofilm grew efficiently on the plastic surface (Fig. 2a–c) but that examination of tubes with biofilms subjected to a shock wave revealed that the shock waves had greatly reduced the biofilm content, evidenced by SEM images (Fig. 2d–f) and in crystal violet assays (Fig. 2g). When P. aeruginosa (Fig. 2h) and S. aureus (Fig. 2i) biofilm were grown in urinary catheters similar reduction was observed upon exposure to shock waves (Fig. 2j,k). Manually calculating the areas in SEM images revealed that upon exposure to shock waves the biofilm was disrupted (Fig. 2l). While the shock wave reduced the biofilm, it did not reduce the viability of the bacteria (Fig. S2) and the bacteria were only released from the surface of the tube (Fig. S3). This data supports the observed reduction in the biofilm biomass by CV staining or SEM. Catheter biofilms grown in the presence of human or bovine urine showed equivalent levels of biofilm production, and reductions, through exposure to shock waves (Fig. S4).
Increased sensitivity of biofilm bacteria treated with shock waves to antibiotics
Urinary catheters with biofilms were exposed to shock waves and the bacteria released from the catheters into bacterial media or urine were enumerated by viable colony count (Fig. 3). These results revealed that increased numbers of bacteria were released into the media by shock wave mediated biofilm dispersal (Fig. 3a,b), independent of the source of urine used to grow the biofilm. To determine whether this enhanced dispersal led to increased sensitivity of the biofilm to antibiotic treatment, biofilms in microfuge tubes and catheters were exposed to shock waves, incubated with 4 μg/ml ciprofloxacin for 6 h, the biofilm fully dispersed using a bath sonicator, and plated for viable count. The results showed that, while biofilms were structurally resistant to the antibiotic, the bacteria became susceptible to antibiotic after treatment with the shock waves (Fig. 3c,d). The use of the shock wave increased the biofilm community’s sensitivity to antibiotic by 100 to >1,000-fold. These data were replicated using biofilms formed in microfuge tubes (Fig. S5).
Use of shock waves to reduce biofilm-mediated infection in vivo
P. aeruginosa pneumonia model
The extracorporeal shock waves generated using the hand-held shock wave generator are of high energy and are localized to a small area. Performing in vivo studies using the same device might cause tissue damage. This holds true even for other devices that are used to generate shock waves for biological applications, like lithotripters. Therefore, for the in vivo studies we have used a diaphragmless shock tube (DST) which generates low energy shock waves and the area of impact is larger so as to expose the entire body of the mouse to shock waves27. A conventional shock tube is a simple device having two sections, a driver section and driven section, separated by a metal diaphragm. In the case of DST, the metal diaphragm is replaced by a pneumatic cylinder (Fig. 4a,b).
The use of a pneumatic cylinder in place of metal diaphragms reduces the time between successive runs, as it does not require the replacement of a metal diaphragm for each run. Using the diaphragmless shock tube, shock waves of required strength (even as low as 0.8 bars over pressure which is required for our experiment) can be generated with high repeatability (Fig. 4c,e). Mice were housed in a perforated chamber that is mounted with a L-shaped bend at the end of the shock tube (Fig. 4a). The L-bend prevents the animals from entering into the shock tube. Also, the perforated chamber ensures that there are no reflections of the incident shock wave. The shock wave travelling through the L-shaped bend undergoes an attenuation of approximately 30% in strength28,29. The various parameters of this shock tube are shown in table 1.
For the biological experiments, the diaphragmless shock tube was operated with a driver section pressure (P4) of 5 bars and driven section (P1) kept at atmospheric pressure (1 bar). The pressure jump obtained behind the shock wave (P2) was ~ 0.8 bar at the end of the shock tube with high repeatability (Fig. 4c,e). This pressure is measured at the end of the shock tube before the L-shaped bend. The energy contained in the incident shock wave is calculated using the method suggested by Wang et. al.30. The energy in the incident shock wave is calculated to be 205 mJ/mm2. The mice in the perforated chamber experienced a peak overpressure of 0.48 bar (Fig. 4f). A specific impulse of 18.21 Pa.s/m2 was felt by the mice in the chamber, which is calculated by finding the area under the curve.
Mouse model of chronic pneumonia was used for Pseudomonas infection31. Mice (10 mice/group) were intranasally infected with 1 × 107 CFU P. aeruginosa per mouse. The mice were killed 3 days after infection and the number of bacteria in the lungs was determined using viable count of homogenised lung tissue (Fig. S6a). The presence of bacteria and the formation of biofilm in lung were confirmed by SEM (Fig. S6b).
Mice that were infected intranasally with P. aeruginosa were treated with ciprofloxacin alone, with shock waves alone, or with a combination of shock wave and ciprofloxacin for 3 days. The mice were killed after 3 days of treatment and the effect of treatment on lung tissue was examined by SEM. No bacteria were found in the uninfected mice, a clear biofilm formation was observed in the infected mice and reduced number of bacteria were found in the treatment group with shock wave and antibiotic (Fig. 5a,e). The numbers of bacteria in lung homogenates were determined by viable count (Fig. 5f). Though the number of bacteria observed in SEM of tissues from mice treated with shock waves alone (Fig. 5d) was greatly reduced compared with control mice (Fig. 5b), there was no reduction in the number of bacteria found in tissue homogenates by viable count (Fig. 5f). The viable count results showed that P. aeruginosa infection in mice, initiated by intranasally delivered agarose beads, was not sensitive to daily treatment with ciprofloxacin. In contrast, the combination of shock wave and ciprofloxacin treatments significantly reduced the number of bacteria in the lung, determined by viable count (Fig. 5f).
The impact of shock wave therapy on the survival of mice with P. aeruginosa pneumonia was also examined. At the end of the therapy (Day 0 in Fig. 5g), groups of 8 mice were examined twice daily to determine when they became moribund. Infected mice given shock wave therapy alone or left untreated died within 10 days whereas only 2 mice treated with ciprofloxacin alone survived. All mice provided ciprofloxacin therapy and shock wave treatment survived. From these data it is evident that shock waves generated from the diaphragmless shock tube can be used to treat lung biofilm infection without any damage to the lung tissue. Further detailed studies are required to confirm the safety of using shock waves in vivo for other organs.
S. aureus infected suture model
Anaesthetized mice (5 mice/group) were shaven of abdominal fur and provided surgical wire sutures. Sterile sutures removed after 3 days and examined by SEM did not carry obvious biofilms (Fig. 6a). Sterile suture exposed to shock waves did not show any defects or damage (Fig. 6b). Mice were also administered sutures that were pre-incubated in TSB broth containing S. aureus (Fig. 6c,f). After 3 days, the sutures were removed and the formation of biofilms on the sutures was observed by SEM. The excised S. aureus contaminated suture wires were treated ex vivo with ciprofloxacin (4 μg/ml for 6h) alone (Fig. 6d), shock waves alone (Fig. 6e), or a combination of shock wave treatment ciprofloxacin (4 ug/ml for 6h). The remaining sutures not used in SEM were homogenized and the number of bacteria determined by viable count (Fig. 6g). The results show that there is a significant reduction in the suture wires treated with ciprofloxacin compared with control infected sutures by SEM (Fig. 6d) and viable count (Fig. 6g). The biofilm associated with sutures was reduced further when the excised suture wire was treated with shock waves and ciprofloxacin (Fig. 6f,g). Shock wave therapy alone reduced the presence of bacteria as observed in SEM (Fig. 6e), but not by viable count (Fig. 6g).
To determine whether this combination of shock wave therapy and antibiotic treatment could reduce the biofilms associated with infected sutures in vivo, an abdominal incision was made and the incision closed with suture wire. The suture site was then infected with S. aureus and the mice were treated with ciprofloxacin intravenously with or without shock wave exposure using diaphragmless shock tube. After treatment for 3 days, the number of bacteria on the surgical wire and surrounded skin tissue were analysed by excising either the sutures or the adjacent skin, homogenising the sample, and plating the samples for viable count of the bacteria (Fig. 7). Control animals received no sutures and S. aureus infection without further treatment. The bacterial numbers associated with sutures (Fig. 7a) or surrounding skin (Fig. 7b) were equivalent in all mice, except those that received combination shock wave and antibiotic therapy.
In 1982, Chaussey developed extracorporeal shock wave lithotripsy (ESWL) by creating high pressure at a focal point by shock focusing32. To disintegrate the kidney stones, the shock wave should generate at least 80bar since the yielding stress of kidney stones is 80bar at maximum33.
Though shock waves have been used clinically for many years, the high pressure profile and cavitation effects of shock waves can lead to the damage of the tissues34. The extracorporeal shock waves are generated by focussing at a particular site and hence the energy is very high at the localized area and hence the tissue damage is possible. Tissue damage will depend on the shock wave energy density, number of shock waves and shock wave coupling. Hence the threshold limit should be used to avoid any tissue damage or bleeding35. Shock wave lithotripsy carried out in rabbits is found to cause haemorrhage, edema, congestion, inflammation, loss of normal structure and epithelial desquamation in all areas of the pleural tissue. The reason for the lung injury is attributed to the tissue-air interphase as lungs consist of alveolar sacs36. In 1987, lung hemorrhage was observed in dogs when they were exposed to shock waves with 100 bar overpressure but not with 20 bar37. The severity of the damage depends on several factors, such as shock wave energy density, type of tissue, number of shock waves, etc. In our experiments, the shock wave energy is distributed to the whole body, since, we have used unfocussed, low energy shock waves to disrupt the biofilm and we did not observe lung tissue damage caused using this method. Further detailed studies are necessary to understand the other deleterious effects of shock waves on other organs.
Biofilm formation occurs through different phases such as surface conditioning, attachment and colonization. Surface conditioning involves the adsorption of organic and inorganic nutrients, which facilitate bacterial attachment. Initial attachment of the bacteria to the surface may be reversible involving Brownian movement and weak forces between the surfaces or may involve ligands (e.g. bacterial fimbriae) binding to cognate receptors13,14. Regardless, the early interactions can soon become irreversible due to the production of extracellular polymeric substances (EPS)38. As the biofilm-associated bacteria grow and divide, the colony may form simple or complex tertiary structures39, which demonstrate increased resistance to antibiotics. There are multiple hypotheses to explain the phenotypic resistance observed including slow or incomplete penetration of the antibiotic into the biofilm, altered microenvironment through the depletion of nutrients or accumulation of waste products within the biofilm, and/or the formation of resistant phenotypes a result of an altered growth rate of the bacteria38.
Much of the recent research aimed at preventing biofilm formation is focused on using novel materials or catheters coated with antibiotics. Antimicrobial peptides coated implants have been developed to control the biofilm formation in these implants. While these approaches offer some promise, the architecture of biofilms where there is clear separation between the growing edge of the biofilm and the surface, may mitigate against success of this approach. Ultrasound has also been used to kill the biofilm mode of infection along with antibiotics10. Apart from this, photon-initiated photoacoustic streaming has been used to remove dental biofilm11.
We have used shock waves to disrupt biofilms in urinary catheters at physiological conditions, where the biofilms were grown in bovine or human urine. When the catheter-associated biofilms were treated with ciprofloxacin there was no reduction in the number of bacteria, whereas ciprofloxacin treatment together with shock wave therapy significantly reduced the number of bacteria that could be observed or detected by viable count. The shock waves were not antibacterial. It is hypothesized that the very brief exposure to the wave ruptured the polysaccharide matrix surrounding the biofilm, liberating bacteria and possibly increasing access to the antibiotic. Further experiments were carried out to determine the effect of shock waves on in vivo biofilms.
Mice intranasally administered P. aeruginosa developed biofilms in the lung after 3 days as seen in scanning electron microscopy (SEM) images. When these mice were treated with ciprofloxacin, there was no decrease in the bacterial counts in homogenised lung samples, but this bacterial burden was significantly decreased if the animals received antibiotic treatment combined with shock wave therapy. The shock wave therapy neither causes pathology to the lungs, as determined histologically (Fig. S6c–h) nor any weight loss (Fig. S6i). Very few mice survived without antibiotic treatment and they showed 10 to 20% weight loss, whereas, shock wave along with antibiotic treatment group mice recovered from initial 3 days of weight loss (Fig. S6i). Mice that received both antibiotic and shock wave therapy after challenge with agarose beads coated with P. aeruginosa survived, whereas animals that received antibiotics alone usually succumbed to infection.
Wound infections driven by biofilms associated with sutures and other closure devices are a major cause of nosocomial infection. It is estimated that 1–8% of the people who have undergone cardiac surgery develop wound site infections40. We have simulated this condition in mouse skin, where an incision was made and closed with surgical suture wire. The wire was either infected with S. aureus before insertion, or subsequently. SEM analysis that was a near complete disruption of biofilms formed on suture wires in vitro if the wires were excised and treated with shock waves ex vivo. If the animals carrying the sutures were subject to both shock wave and antibiotic therapy, and the degree of S. aureus infection of the suture wires, and the surrounding tissues, was reduced significantly. Consistent with observations that shock waves alone are not antibacterial, therapy using shock waves in the absence of antibiotics, like antibiotic therapy alone, was not effective in reducing the bacterial burden of suture sites contaminated with S. aureus. Here we have shown for the first time that a single shock wave pulse of 205 mJ/mm2 can be used to disrupt biofilm in vivo. Though, the energy in the shock wave is much higher than that of the shock wave generated by the hand-held device, the area over which the shock wave is spread is larger. Therefore, the energy per unit cross-section area is lower than that of the hand-held device. Also, the peak over-pressure of the shock wave is lower. The steady time duration of the shock wave is much longer in the case of the diaphragmless shock wave generator. All these parameters help in conducting the in vivo studies without injuring the different organs of the mice.
These results clearly indicate that shock waves can be used as an adjunct therapy to treat bacterial biofilm infection in medical devices and foreign body-associated infections. The data demonstrates, for the first time, that shock wave therapy can be used to treat biological biofilm infections in combination with antibiotic treatments. The combined use of shock wave and ciproflaxin, while yielding significant reduction in viable bacteria in in vivo tests, resulted in approximately 1 log in CFU reduction, leaving substantial viable bacteria, which might include resistant individuals. The effect of the shock wave on the generation of resistance is not known and requires further study.
The shock waves generated in the present study are completely different from the extracorporeal shock waves, which are routinely used for kidney stone disintegration in terms of the impulse and peak pressure amplitude. Since ESWL is being routinely practiced for treatment of unrelated medical conditions, shock wave assisted biofilm disruption could be used to treat especially recalcitrant biofilm infections in hospital settings. Since this methodology of shock wave generation and exposure to treat biofilm infections can easily be scaled up for human trials, the finding of this interdisciplinary study will have profound impact in therapeutic uses in the near future.
Bacterial strains and growth conditions
Salmonella enteric serovar Typhimurium (ATCC 14028s), Pseudomonas aeruginosa (PA01) and Staphylococcus aureus (ATCC 25923) were grown in Luria broth at 37 °C in a shaker at 180 rpm. The bacteria were maintained on Luria agar.
For S. Typhimurium biofilm formation, 1 × 104 stationary phase cells were inoculated into 2 ml of Luria broth without NaCl and kept at 25 °C in static condition in 2 ml screw cap tubes, with or without cholesterol coating (1 mg). 100 μl of cholesterol dissolved in anhydrous ether (10 mg/ml) was taken in the microfuge tubes and the ether was allowed to evaporate to coat 1 mg of cholesterol in the microfuge tubes. Cholesterol coating was used to mimic the physiological gall bladder stone condition41. For P. aeruginosa and S. aureus biofilm formation, 1 × 104 stationary phase cells were inoculated in 2 ml of tryptic soy broth and kept at 25 °C in static condition for better biofilm formation in 2 ml screw cap tubes.
Sterile cover slip or catheter (Foley catheters, Silicone coated latex, 8F–10F) (1 cm segment) was placed in a 24-well plate with either 1 ml of tryptic soy broth (TSB), bovine urine (filter sterilized) or human urine (filter sterilized). 1 × 104 stationary phase cells of S. Typhimurium, P. aeruginosa and S. aureus were inoculated in the 24-well plate and kept at 25 °C in static condition for 72 h. The respective media was changed every 24 h.
Overnight grown S. aureus culture in tryptic soy broth (TSB) were inoculated (1 × 107 bacteria) into 1 ml of fresh TSB in a 24 well plate. 5 mm sections of sterile surgical sutures (MersilkTM, NW5079–non-absorbable and made of fibroin protein, suture size: 5-0) were placed in the wells. The plates were incubated at 25 °C in static condition with regular change of fresh TSB at 24 h intervals.
Shock wave generation using hand held device
Shock waves were generated using high melt explosive [octahydro-1,3,5,7-tetranitro-1,3,5,7-tetrazocine] and traces of aluminium coated polymer tube4,5,6. Briefly, when the explosive coated polymer tube was ignited from one end of the tube, shock waves are produced at the other end of the tube (Fig. 1f,g). These shock waves are ideal for in vitro experiments but not for in vivo experiments as the dimensions of the specimen are bigger and the entire body of the mouse needs to be exposed to the shock wave (Table 1). Impulse per unit area (I) was calculated by using the formula,
Where, ‘T’ represents the steady time of the shock wave, ‘P (t)’ is the pressure experienced by the sample as a function of time.
Crystal violet (cv) staining of biofilms
Microfuge tubes containing biofilm on the inner walls of the tubes and biofilm on the surface of the catheters were confirmed by crystal violet staining25. After 72h of incubation at static condition, the tubes/catheters were washed with phosphate buffered saline (PBS) three times to remove the planktonic cells. The tubes/catheters were dried and stained with 1% (w/v) crystal violet for 15 minutes at room temperature. After three PBS washes, the bound crystal violet was solubilized with 200 μl of absolute ethanol. The optical density was determined at 600 nm (SpectraMax 340PC, Molecular Devices).
Shock wave assisted disruption of biofilms
After 72 h of incubation under static conditions, the tubes, catheters or sutures were washed three times with PBS to remove the planktonic cells. The tubes were filled with 1.5 ml of PBS and exposed to shock waves. In case of catheters and sutures, the samples were placed in 2 ml screw cap tube containing 1.5 ml PBS. 2 mm hole was made in the 2 ml screw cap in a sterile condition and the polymer tube was inserted without touching the liquid or sample and triggered for shock wave generation (Supplementary video 1). The generation of blast sound upon shock wave exposure assures that the materials were exposed to shock waves. The tubes, catheters and surgical suture wires were further analyzed by CV staining, scanning electron microscopy (SEM), CFU measurement and antibiotic sensitivity assay to validate the disruption caused by shock waves.
Scanning electron microscopy (SEM)
Catheters, surgical sutures and cover slips with biofilm were fixed with 2.5% (v/v) glutaraldehyde and the samples were dehydrated with increasing concentrations of ethanol for 2 min each. The samples were stored in vacuum until use. Prior to analysis by Field emission SEM (FEI-SIRION, Eindhoven, Netherlands), the samples were subjected to gold sputtering (JEOL JFC 1100E Ion sputtering device).
Antibiotic sensitivity assay
After biofilm shock wave treatment (as described earlier), the samples were exposed to 4 μg/ml of ciprofloxacin under shaking conditions at 180 rpm, 37 °C for 6 h, washed with PBS and homogenized by sonication for 10 minutes in a bath sonicator and plated on LA42. The untreated biofilm samples were used as controls.
Release of bacteria
After shock wave exposure to biofilm in tubes and in catheters, the media (PBS) containing the sample was transferred to a new microfuge tube, homogenized by sonication for 5 minutes in a bath sonicator and plated on LA to determine the number of bacteria released from the biofilm. The media (PBS) from the untreated biofilm samples were also processed similarly and used as controls.
P. aeruginosa lung infection mouse model
BALB/c mice bred and housed at the Central Animal Facility of Indian Institute of Science (IISc) were used for all the in vivo experiments. The mice used for the experiments were 6–8 weeks old. All procedures with animals were carried out in accordance with the Institutional rules for animal experimentation. The Institutional Animal Ethics Committee (Registration No: 48/1999/CPCSEA) approved all animal experimental protocols and the National Animal Care Guidelines were strictly followed. Chronic pulmonary infection in mice was induced by agarose bead infection method as described elsewhere31. Briefly, adult BALB/c mice were infected by intranasal injection of bacterial beads that were produced by mixing 1 ml of overnight culture of P. aeruginosa with 9 ml of PBS and 25 ml of 2% (w/v) agarose. The mixture was stirred continuously after adding 500 ml of mineral oil at 50 °C until the temperature reach RT. The agarose beads were washed once with 0.5% deoxycholic acid, sodium salt (SDS) in PBS, once with 0.25% SDS, and four times with PBS. The number of viable bacteria was enumerated and the beads were stored for not more than 48 h at 4 °C.
BALB/c mice (10 mice/group) were intranasally infected with 50 μl of 1:10 dilution bead slurry. On day 3 post infection, different cohorts of mice were treated with ciprofloxacin alone (2.5 mg/kg–intravenous injection–once per day), shock wave treatment alone (once per day), or shock wave (once per day) and ciprofloxacin treatment (2.5 mg/kg–intravenous injection–once per day) for 3 days. The mice were killed after 3 days, and the lungs was aseptically removed, weighed and homogenized in sterile PBS. The homogenate was plated using serial dilutions onto LB agar to determine the bacterial load. A small part of the lung was fixed with 2.5% (v/v) glutaraldehyde and processed with increasing concentrations of alcohol (10, 20 30, 50, 70, 80, 90 and 100%) and analysed with SEM as described. For survival assay, same treatment was given (n = 8 mice/group) for 5 days and the mice were monitored twice daily for 20 days for morbidity and mortality.
S. aureus skin suture infection mouse model
The abdominal fur of BALB/c mice (5 mice per group) was removed with a razor and the mice were anesthetized by intraperitoneal injection of a mixture of ketamine (100 mg/kg) and xylazine (10 mg/kg). A small incision was made in the abdomen, which was subsequently closed using surgical suture (MersilkTM, NW5079). 10 μl of overnight grown S. aureus culture (1 × 107) was applied to the site and allowed to dry. Three days after infection, different groups of mice were treated with ciprofloxacin alone (2.5 mg/kg–intravenous injection–once a day), shock wave treatment alone (once per day), or shock wave (once per day) ciprofloxacin treatment (2.5 mg/kg – intravenous injection–once a day), for 3 days. The mice were killed after 3 days, the suture wire and the surrounding skin was dissected and homogenized in sterile PBS. The homogenate was plated in serial dilutions on Vogel-Johnson agar to determine the bacterial load in the sample.
Diaphragmless shock tube for in vivo experiments
Experiments were carried out using a diaphragmless shock wave generator27. The diaphragmless shock tube has internal diameter of 50 mm and employs a fast acting pneumatic valve instead of aluminium diaphragms. The driver section volume is 0.0454 m3 and the driven section length is 6.064 m. Initially, the pneumatic cylinder is pressurized to facilitate the forward motion of the piston head. The piston head seals the junction between the driver and the driven section. The driver section is filled with a high pressure (P4) while the driven section is maintained at a low pressure (P1). When the gas at the rear end of the pneumatic cylinder is suddenly exhausted, the piston head moves back at a high speed (~5 ms) allowing the high pressure driver gas to enter the driven section. This generates a shock wave in the driven section with an overpressure P2. The amplitude of pressure P2 can be controlled by the initial pressure conditions in the driver and driven section i.e. P4 and P1.
When used with mice, the animals are housed in a perforated chamber that is mounted with a L-shaped bend at the end of the shock tube (Fig. S4a). Impulse per unit area (I) can be calculated by using the equation (1).
All the in vitro and in vivo experiments were performed in triplicates. One way ANOVA, Mann-Whitney tests and Log-rank test were performed using GraphPad Prism 5 software.
How to cite this article: Gnanadhas, D. P. et al. Successful treatment of biofilm infections using shock waves combined with antibiotic therapy. Sci. Rep. 5, 17440; doi: 10.1038/srep17440 (2015).
We thank the Electron microscopy facility, IISc for the help. We thank the Central Animal Facility, IISc for providing the mice. This work was supported by the grant Provision (2A) Tenth Plan (191/MCB) from the director of the Indian Institute of Science, Bangalore, India, and the Department of Biotechnology (DBT 311, NBA, sanctioned by the President), Life Science Research Board (LSRB0008) and DBT-IISc partnership program for advanced research in biological sciences and bioengineering to DC Infrastructure support from ICMR (Center for Advanced Study in Molecular Medicine), DST (FIST), and UGC (special assistance) is acknowledged. DPG, AD and JS are research scholars and ME is project assistant. CSS is a DBT RA post-doc fellow. RAS is supported by the AD acknowledges DBT for Senior Research Fellowship.
About this article
Journal of Molecular Medicine (2018)