21 September 2015 Trends in nanosecond melanosome microcavitation up to 1540 nm
Author Affiliations +
J. of Biomedical Optics, 20(9), 095011 (2015). doi:10.1117/1.JBO.20.9.095011
Abstract
Thresholds for microcavitation of bovine and porcine melanosomes were previously reported, using single nanosecond (ns) laser pulses in the visible (532 nm) and the near-infrared (NIR) from 1000 to 1319 nm. Here, we report average radiant exposure thresholds for bovine melanosome microcavitation at additional NIR wavelengths up to 1540 nm, which range from ∼0.159  J/cm2 at 800 nm to 4.5  J/cm2 at 1540 nm. Melanosome absorption coefficients were also estimated, and decreased with increasing wavelength. These values were compared to retinal pigment epithelium coefficients, and to water absorption, over the same wavelength range. Corneal total intraocular energy retinal damage threshold values were estimated and compared to the previous (2007) and recently changed (2014) maximum permissible exposure (MPE) safe levels. Results provide additional data that support the recent changes to the MPE levels, as well as the first microcavitation data at 1540 nm, a wavelength for which melanosome microcavitation may be an ns-pulse skin damage mechanism.
Schmidt, Kennedy, Noojin, Vincelette, Thomas, and Rockwell: Trends in nanosecond melanosome microcavitation up to 1540 nm

1.

Introduction

Recently, the American National Standards Institute (ANSI) revised the standards for the maximum permissible exposure (MPE) for safe use of lasers under Z136.1.1 The revisions included significant changes to the near-infrared (NIR) spectral region, and to the visible region in the nanosecond (ns) time regime. Our previous study reported NIR thresholds for ns-pulse melanosome microcavitation, which supported the changes made to the safety standards.2 However, there is still a need for additional microcavitation data in the ns time regime, in order to support future updates to the ANSI safety standards. Therefore, due to the lack of ns-pulse threshold data at other NIR wavelengths of interest, we have expanded this study to determine additional average radiant exposure thresholds for microcavitation of isolated bovine melanosomes using ns laser pulses at wavelengths in the 800 to 1064 nm region, as well as at 1540 nm. Two different laser sources were used in order to probe NIR wavelengths of interest.

Melanosomes are found within both human skin and retinal pigment epithelium (RPE) layers of the eye. They are the main ocular light energy absorbers in the visible and NIR. As laser wavelengths increase into the mid-IR, water absorption increases and melanosome absorption decreases, depositing more absorbed energy in the cornea and anterior segments of the eye, and less in the posterior retinal tissue. The formation of small gaseous bubbles around melanosomes in the RPE, a process known as microcavitation, is the threshold-level damage mechanism for ns-pulse ocular exposures.34.5.6

The objective of this study was to more clearly illustrate the wavelength dependence of single-melanosome microcavitation thresholds for ns-pulse exposures covering the entire NIR regime. Results of this study were compared to the 20141 and 20077 ANSI Z136.1 MPE values, as well as to in vivo ns-pulse retinal damage threshold data in the visible and NIR. These results support the recent changes to the National Laser Safety Standards. Furthermore, we report the first microcavitation threshold data at 1540 nm, a wavelength for which melanosome microcavitation may be an ns-pulse skin damage mechanism.

2.

Experimental Details and Procedures

Our procedure for bovine melanosome preparation followed the method of Dontsov et al.,8 and these details can be found in our previous report.2 In this study, additional wavelengths were investigated, including coherent emissions at 800, 900, 975, 1064, and 1540 nm. In order to observe the microcavitation events after exposure, a microscope containing two beam paths was used, a technique thoroughly described by Schmidt et al.2 Although the OPO described in our previous publication is stable and can generate wavelengths out to 2400 nm, there was not enough energy per pulse to create the microcavitation events above 1200 nm. Therefore, multiple lasers were required at longer wavelengths to generate enough energy per pulse to create the cavitation event with increasing wavelength. Microcavitation events at 1540 nm were determined using emissions from a Megawatt (high-peak power) Er-glass laser (Hilton Head Island, South Carolina) with a custom Q-switch, designed by Taboda Research Instruments (San Antonio, Texas). This laser has a reasonably Gaussian spatial distribution, with 35-ns pulse duration and 3.5 J maximum energy per pulse.9 The experimental setup for the 1540-nm data required changes from our previous report. Figure 1 is a schematic of the laser system and components.

Fig. 1

Schematic of the laser and illumination setup for observing microcavitation bubble formation from irradiated melanosomes at 1540 nm. BS indicates beam splitters. P1 is a reference energy meter (dashed line represents 10% reflectance used at P1) and an additional detector is used at the sample source to determine energy delivered to the sample. The focused illumination beam was approximately 1 mm in diameter.

JBO_20_9_095011_f001.png

The illumination beam was created by splitting (10%) and frequency doubling the 1540-nm laser beam, which resulted in 770-nm pulses. The 770-nm beam was launched into a 0.22 NA multimode 45-m fiber (FG105LCA Thorlabs), and focused at the sample surface, which optically triggered the CCD camera (Imperx Incorporated, Boca Raton, Florida). Time-resolved imagery of the microcavitation events was achieved by the 120-ns optical delay created by the fiber and free-space optical path differences. Previous research performed by Kelly6 indicated that microcavitation bubbles expanded and collapsed in approximately 250 ns, and a 125-ns delay postexposure was a sufficient stroboscopic delay to observe cavitation events. Based on this previous research, similar delays were used postexposure for the current studies. Microcavitation images were collected using a Bobcat CCD camera (Imperx Incorporated, Boca Raton, Florida). Pre- and postcavitation images were also collected and used for background subtract from the exposure image for improved image quality. Beam diameter measurements were determined prior to each data collection set using the knife-edge technique. In each case, the spot size consisted of a 1/e2 Gaussian beam, which results in an average radiant exposure value. The NIR exposures (800 to 1064 nm) had an average beam diameter of 183±18μm. The average beam diameter at 532 nm was 295±22μm. The average beam diameter at 1540 nm was 305±31μm. It is important to note that although there were slight differences in pulse width (8 to 50 ns) at the different wavelengths used, we do not expect this to influence the measured cavitation thresholds. Microcavitation is the primary threshold-level retinal damage mechanism for pulsed exposures over the entire ns-time regime. Significant thermal diffusion only occurs on microsecond time scales and all ns-pulse exposures are within the thermal confinement region. Therefore, the slight variances in ns-pulse widths should not change the outcome of the study.

3.

Results and Discussion

Probit analysis was the statistical method used to estimate the threshold (pulse) energy for laser-induced microcavitation (ED50).10,11 Binary (yes/no) data points were collected, the ED50 energy, slope, and fiducial limits (FL) were determined at the 95% confidence level, and the ED50 radiant exposure was calculated by dividing the energy per pulse by the beam diameter. The radiant exposure (H) is computed by Eq. (1)

(1)

H=4Q/πDL2,
where Q is the energy per pulse and DL is the 1/e2 Gaussian beam diameter. An estimated total uncertainty of the average radiant exposure threshold was 16%. Data collection occurred on several successive days and was combined in order to produce a single ED50 threshold value at each wavelength. Table 1 summarizes the combined bovine microcavitation average radiant exposure thresholds, upper and lower FL, and Probit slope, from 532 to 1540 nm. The upper and lower FL limits represent the 95% confidence intervals. Values denoted by wavelength numbera were determined in the previous study,2 and values denoted by wavelength numberb were determined in this study. Due to the significant water absorption in the mid-IR, the water layer above the melanosomes was taken into account to determine the microcavitation threshold of 4.5J/cm2 at 1540 nm. The actual radiant exposure was determined by calculating the transmission through our sample water layer of approximately 500μm. At 1540 nm, water transmission is 55.3% based on Hale and Querry data,12 with an absorption coefficient of 11.83cm1. Thus, the observed cavitation threshold, corresponding to the radiant exposure at the surface of the water layer, was multiplied by the transmittance in order to find the actual radiant exposure at the melanosome. Figure 2 is a plot of bovine microcavitation thresholds as a function of wavelength, on a log scale. Melanosome absorption coefficients were calculated from the threshold values in Table 1.

Table 1

Probit threshold data for the combined trials for single, ns pulses at all wavelengths. The reported ED50 is an average radiant exposure for bovine melanosome microcavitation, determined from the ED50 pulse energy divided by the spot size area. The upper and lower fudicial limits (FL) represent the 95% confidence intervals. The 1540-nm value was corrected for the absorption of the water layer.

Wavelength (nm)ED50 (mJ/cm2)Lower FL (mJ/cm2)Upper FL (mJ/cm2)Probit slopeNumber of shots
532a99.296.110210.9453
800b1591541649.1608
900b2031972098.63698
975b47146447818.2500
1000a51450452318.3706
1064b53151854817.9992
1100a60659261913.1847
1200a83381984818.5634
1319a26502610269013.41233
1540b45044261479215.2165

a

Values previously reported values from Schmidt et al.2

b

Values determined in this study.

Fig. 2

A comparison of radiant exposure thresholds of bovine melanosomes as a function of wavelength, on a log scale, from 532 to 1540 nm, at ambient temperature of 20°C. Error bars (smaller than the points as plotted) represent the upper and lower 95% fiducial confidence intervals.

JBO_20_9_095011_f002.png

As previously reported, a first-order estimate of the melanosome absorption coefficient, μm, as a function of threshold radiant exposure, Fth(T), measured at melanosome temperature T can be obtained using the following equation:5,13

(2)

TthT=[μmFth(T)]/[Cp/ρ],
where Cp is the melanosome specific heat, ρ is the melanosome density, and Tth is the threshold temperature for bubble formation. Melanosome specific heat and particle density are Cp=2.55J/gm-°C and ρ=1.41gm/cm3.13

Cavitation data were collected at an ambient temperature of 20°C, and an estimated threshold temperature of Tth=150°C was used based on the temperature-dependent, ns-pulse, melanosome microcavitation studies of Kelly6 and Neumann and Brinkmann.13 Using Eq. (2), one can solve for μm to determine absorption coefficients. Table 2 presents a comparison of the melanosome and RPE layer absorption coefficients, where the uncertainty in the melanosome data was estimated from both the experimental uncertainty of Fth and the threshold temperature (Tth) variability from the literature.5,13,14 The RPE layer data are from Birngruber, et al.15 As in Table 1, values denoted by wavelength numbera were determined in the previous study,2 and values denoted by wavelength numberb were determined in this study. Figure 3 shows the wavelength dependence of the absorption coefficients for melanosomes, water, and the RPE layer, on a log scale. Note that in the visible and NIR, melanosome absorption coefficients are roughly an order of magnitude higher than corresponding RPE layer values. The results show melanosome and RPE layer absorption coefficients decreasing with increasing wavelength at roughly the same rate.

Table 2

A comparison of the retinal pigment epithelium (RPE) and melanosome (μm) absorption coefficients as a function of wavelength. The RPE layer values were based on a fit to data extrapolated from Birngruber et al.15 The uncertainty was estimated by combining the experimental uncertainty of Fth and the threshold temperature (Tth) variability from Refs. 5, 13, and 14.

Wavelength (nm)RPE (cm−1)Melanosome (cm−1)Melanosome uncertainty (cm−1)
532a13814718±896
800b4042943±560
900b2552305±438
975b181993±188
1000a161925±176
1064b120881±167
1100a102763±140
1200a64558±106
1319a41176±33
1540b11.8104±29

a

Values previously reported values from Schmidt et al.2

b

Values determined in this study.

Fig. 3

Wavelength dependence of water, melanosome, and retinal pigment epithelium (RPE) layer absorption coefficients on a log scale. Although the melanosome absorption coefficients are roughly an order of magnitude higher than the RPE layer values, both coefficients decrease with increasing wavelength at approximately the same rate.

JBO_20_9_095011_f003.png

Figure 3 indicates that at 1540 nm, water and RPE layer absorption coefficients are similar (10cm1), even though the melanosome values are approximately an order of magnitude higher (102cm1). The difference in these absorption coefficients are probably due to the high water content and low melanin concentration in the RPE layer, as a simple first-order calculation can demonstrate. RPE cells are approximately 20 to 25μm in diameter, and the RPE layer is roughly 15μm thick. We can approximate the RPE cell as having a rectangular volume of 20μm×20μm×15μm, or 6000μm3. We can model the melanosome as a sphere 1μm in diameter, giving a melanosome volume of 0.524μm3. Finally, assuming 100 melanosomes per cell gives a melanin concentration of 0.87% (52.4/6000). The low melanin concentration minimizes the effect of the higher melanosome absorption coefficient on the total RPE layer absorption, keeping the latter close to the water value at this wavelength. As shown in Fig. 2, decreasing melanosome absorption in the mid-IR does cause a significant increase in the microcavitation threshold radiant exposure from 1319 to 1540 nm.

This paper reports the first melanosome microcavitation threshold values at 1540 nm. These data show that despite reduced melanin absorption in the mid-IR, it is possible to create melanosome microcavitation events at 1540 nm, assuming a sufficiently high-radiant exposure can reach the melanosome. For high-peak power, ns-pulse, 1540-nm skin exposures, resident dermal melanosomes could receive doses producing microcavitation that may damage skin. A previous 1540-nm, ns-pulse, threshold skin study by Lukashev et al.16 reported an ED50 value for minimal visible lesions (MVLs) of 3.0J/cm2. We should note that there are structural and chemical differences between retinal melanosomes and skin melanosomes, which will probably produce different microcavitation thresholds. This, in turn, might explain the difference between the measured, ns-pulse, MVL-ED50 for skin and the ns-pulse (retinal melanosome) microcavitation threshold reported in this study.

Whatever the threshold-level skin damage mechanism might be, microcavitation damage clearly will not occur for RPE melanosomes, since water absorption in the anterior portions of the eye would reduce 1540-nm ocular transmission to the retina to virtually zero. Only the cornea and lens would be damaged at this wavelength and these energies, so RPE microcavitation is not currently considered a likely ocular damage mechanism for ns-pulse mid-IR laser exposures. Very few corneal damage studies have been performed in the 1540-nm wavelength range for ns exposures. In one example, Lund et al.17 reported an MVL-ED50 corneal damage threshold of 21J/cm2 (1/e) at 1540 nm with a 50-ns single pulse.

As a final validation of our results, a comparison between melanosome microcavitation threshold radiant exposure values and total intraocular energy (TIE) values, corresponding to measured retinal damage thresholds in vivo, was performed for the extended microcavitation dataset, with the exception of 1540 nm. Prior to comparing the two datasets, however, the microcavitation radiant exposure thresholds had to be converted into their corresponding TIE values. The microcavitation TIE represents the energy delivered to the corneal plane, which should result in retinal damage due to RPE microcavitation. For this calculation, the threshold radiant exposure at the RPE layer was assumed to be equivalent to our single-melanosome thresholds, listed in Table 1. Next, the retinal radiant exposure threshold was combined with the estimated retinal spot size and ocular transmission values for the rhesus monkey, based on the model of Vincelette et al.,18 to back calculate the threshold energy at the cornea. The Vincelette model estimates retinal beam diameter based on focusing of a 3-mm diameter Gaussian beam entering an emmetropic rhesus eye. A rhesus eye model was chosen for this calculation so that our microcavitation TIE values could be validated by direct comparison to retinal MVL-ED50 TIE values measured for visible and near-IR ns-pulse exposures in the rhesus eye.

Table 3 lists the in vivo rhesus MVL-ED50 TIE values used for comparison to our microcavitation data. These represent a variety of ns-pulse experimental studies, for differing corneal beam diameters, over the wavelength range from 532 to 1319 nm.1920.21.22.23.24.25.26.27 Figure 4 compares the estimated microcavitation TIE thresholds, calculated for a 3-mm diameter Gaussian beam entering a rhesus eye, to the experimental in vivo TIE values of Table 3. These two datasets are also compared to the 20141 and 20077 ANSI Z136.1 MPE limits for 1 to 100 ns pulses, expressed in terms of permissible TIE. The TIE MPE is defined as the MPE given in terms of the corneal radiant exposure multiplied by the area defined by a 7-mm pupillary aperture.1,7 It is evident that the estimated TIE values from microcavitation radiant exposure thresholds mimic the trends in the MVL studies of various authors. Error bars for estimated TIE values represent 51% uncertainty, based on a ±0.25 diopter deviation from emmetropia, uncertainty in retinal transmission, and uncertainty in energy measurements.28 The uncertainty for the in vivo measurements corresponds to the upper and lower FL found in Table 3.

Table 3

Comparison of rhesus monkey in vivo ED50 total intraocular energy (TIE) values from 532 to 1319 nm in the nanosecond pulse regime and a range of corneal irradiance diameters.19–27 These data are plotted in Fig. 4, and compared with estimated microcavitation TIE thresholds in the same wavelength regime based on a 3-mm diameter (1/e2) Gaussian beam entering a rhesus eye.

Wavelength (nm)Pulse duration (ns)Corneal irradiance diameter (mm)Damage siteObservation timeED50TIE (μJ)Range (μJ)Reference
53242.5Retina24 h0.900.6 to 1.3519
5323.53Retina24 h0.510.38 to 0.6520
5323.56Retina24 h0.570.29 to 0.7921
694.3303Retina1 h16.9014.5 to 19.622
694.3504 to 5Retina1 h11.209 to 15.123
799.5164 to 5Retina1 h16.714.8 to 18.823
810.2124 to 5Retina1 h28.425.4 to 31.823
850.211Retina1 h9.107.8 to 10.724
850.21804 to 5Retina1 h129.5 to 15.123
850.3114 to 5Retina1 h8.57.26 to 9.9623
8677Retina2 h5.24.4 to 6.023
88014Retina1 h6.305.2 to 7.724
899.76Retina1 h4.33.4 to 5.323
899.9104 to 5Retina1 h6.625.69 to 7.723
90484 to 5Retina1 h15.214.2 to 18.723
91274 to 5Retina1 h6.545.57 to 7.6823
9127Retina1 h5.504.6 to 6.724
106473Retina1 h28.7022.3 to 39.325
106473Retina24 h19.1017.3 to 21.226
1319504.5Retina24 h1930017300 to 2120027
1319504.5Retina24 h2200020100 to 2460028

Fig. 4

Comparison of estimated and experimental total intraocular energy (TIE) thresholds with ANSI Z136.1-2007 and ANSI Z136.1-2014 maximum permissible exposure (MPE) limits for 1 to 100 ns pulses, expressed in terms of permissible TIE. The TIE MPE is defined as the MPE given in terms of the corneal radiant exposure multiplied by the area defined by a 7 mm pupillary aperture.1,7 Estimated (microcavitation) TIE thresholds are based on a 3-mm diameter (1/e2) Gaussian beam entering a rhesus eye. Experimental TIE data, for in vivo rhesus studies, are from referenced sources in Table 3.1920.21.22.23.24.25.26.27

JBO_20_9_095011_f004.png

4.

Conclusions

This work supplements and extends our previous study,2 which presented the first threshold data ever reported in the literature for ns-pulse melanosome microcavitation in the near-IR. Here, we report additional ns-pulse microcavitation thresholds, measured in the critical 800 to 1064 nm region, with the goal of more clearly illustrating the wavelength dependence of ns-pulse melanosome microcavitation over the entire near-IR regime. We also report the first microcavitation threshold data at 1540 nm, a wavelength for which melanosome microcavitation may be a ns-pulse skin damage mechanism. As before, the threshold radiant exposure data was used to estimate melanosome absorption coefficients and these were compared to absorption coefficients for water and the RPE layer, over the entire wavelength range from 532 to 1540 nm. The 1540-nm cavitation thresholds were significantly higher than 1319-nm values, indicating lower melanosome absorption coefficients and higher skin damage thresholds in the mid-IR. Finally, the microcavitation data was compared to ns-pulse ANSI MPE values and to in vivo ns-pulse retinal damage thresholds in the visible and NIR. Trends in the microcavitation data are consistent with those in MVL studies from the literature, and these results provide additional data to support the recently updated ANSI Z136.1.

Acknowledgments

This research was supported by the National Research Council Research Associateship at AFRL and Engility Corporation, Contract #FA8650-14-D-6519.

References

1. 

ANSI, American National Standard for Safe Use of Lasers, Laser Institute of America, Orlando, Florida (2014), ANSI Z136.1-2014.Google Scholar

2. 

M. S. Schmidt et al., “Trends in melanosome microcavitation thresholds for nanosecond pulse exposures in the near infrared,” J. Biomed. Opt. 19(3), 035003 (2014).JBOPFO1083-3668http://dx.doi.org/10.1117/1.JBO.19.3.035003Google Scholar

3. 

B. J. Lund, D. J. Lund and P. R. Edsall, “Damage threshold from large retinal spot size repetitive-pulse laser exposures,” Health Phys. 107(4), 292–299 (2014).HLTPAO0017-9078http://dx.doi.org/10.1097/HP.0000000000000121Google Scholar

4. 

B. S. Gerstman et al., “Laser-induced bubble formation in the retina,” Laser Surg. Med. 18, 10–21 (1996).http://dx.doi.org/10.1002/(SICI)1096-9101(1996)18:1<10::AID-LSM2>3.0.CO;2-UGoogle Scholar

5. 

R. Brinkmann et al., “Origin of retinal pigment epithelium cell damage by pulsed laser irradiance in the nanosecond to microsecond time regimen,” Lasers Surg. Med. 27(5), 451–464 (2000).LSMEDI0196-8092http://dx.doi.org/10.1002/1096-9101(2000)27:5<451::AID-LSM1006>3.0.CO;2-1Google Scholar

6. 

M. W. Kelly, “Intracellular cavitation as a mechanism of short-pulse laser injury to the retinal pigment epithelium,” PhD Dissertation, Tufts University (1997).Google Scholar

7. 

ANSI, American National Standard for Safe Use of Lasers, Laser Institute of America, Orlando, Florida (2007), ANSI Z136.1-2007.Google Scholar

8. 

A. E. Dontsov, R. D. Glickman and M. A. Ostrovsky, “Retinal pigment epithelium pigment granules stimulate the photo-oxidation of unsaturated fatty acids,” Free Radicals Biol. Med. 26(11–12), 1436–1446 (1999).FRBMEH0891-5849http://dx.doi.org/10.1016/S0891-5849(99)00003-9Google Scholar

9. 

J. Taboada et al., “100-megawatt Q-switched Er-glass laser,” Proc. SPIE 6100, 61000B (2006).PSISDG0277-786Xhttp://dx.doi.org/10.1117/12.646552Google Scholar

10. 

D. J. Finney, Probit Analysis, Cambridge University Press, New York (1971).Google Scholar

11. 

C. P. Cain, L. Manning and G. D. Noojin, “A comparison of various probit methods for analyzing yes/no data on a log scale,” AF Technical Report AL/OE-TR-1996-0120, USAF Armstrong Laboratory, p. 46 (1996).Google Scholar

12. 

G. M. Hale and M. R. Querry, “Optical constants of water in the 200-nm to 200-μm wavelength region,” Appl. Opt. 12(3), 555–563 (1973).http://dx.doi.org/10.1364/AO.12.000555Google Scholar

13. 

J. Neumann and R. Brinkmann, “Boiling nucleation on melanosomes and microbeads transiently heated by nanosecond and microsecond laser pulses,” J. Biomed. Opt. 10(2), 024001 (2005).JBOPFO1083-3668http://dx.doi.org/10.1117/1.1896969Google Scholar

14. 

J. Neumann and R. Brinkmann, “Nucleation dynamics around single microabsorbers in water heated by nanosecond laser irradiation,” J. Appl. Phys. 101(11), 114701 (2007).http://dx.doi.org/10.1063/1.2740348Google Scholar

15. 

R. Birngruber, F. Hillenkamp and V. P. Gabel, “Theoretical investigations of laser thermal retinal injury,” Health Phys. 48, 781–796 (1985).HLTPAO0017-9078http://dx.doi.org/10.1097/00004032-198506000-00006Google Scholar

16. 

A. V. Lukashev et al., “Morphological and histological changes on skin induced by 1540 nm laser irradiation,” Proc. SPIE 2974, 36–45 (1997).PSISDG0277-786Xhttp://dx.doi.org/10.1117/12.275252Google Scholar

17. 

D. J. Lund et al., “Ocular hazards of the Q-switched erbium laser,” Invest. Opthalmol. 9, 463–470 (1970).Google Scholar

18. 

R. L. Vincelette et al., “Thermal lensing in ocular media exposed to continuous-wave near-infrared radiation: the 1150–1350-nm region,” J. Biomed. Opt. 13(5), 054005 (2008).JBOPFO1083-3668http://dx.doi.org/10.1117/1.2978066Google Scholar

19. 

C. P. Cain et al., “Visible retinal lesions from ultrashort laser pulses in the primate eye,” Invest. Ophthalmol. Visual Sci. 36(5), 879–888 (1995).IOVSDA0146-0404Google Scholar

20. 

B. J. Lund, D. J. Lund and P. R. Edsall, “Laser-induced retinal damage threshold measurements with wavefront correction,” J. Biomed. Opt. 13(6), 064011 (2008).JBOPFO1083-3668http://dx.doi.org/10.1117/1.3013455Google Scholar

21. 

B. J. Lund, D. J. Lund and P. R. Edsall, Damage Threshold from Large Retinal Spot Size Repetitive-Pulse Laser Exposures, Laser Institute of America (2009).Google Scholar

22. 

G. D. Frisch, E. S. Beatrice and R. C. Holsen, “Comparative study of argon and ruby retinal damage thresholds,” Invest. Ophthalmol Visual Sci. 10(11), 911–919 (1971).Google Scholar

23. 

D. J. Lund and E. S. Beatrice, “Near infrared laser ocular bioeffects,” Health Phys. 56(5), 631–636 (1989).HLTPAO0017-9078http://dx.doi.org/10.1097/00004032-198905000-00005Google Scholar

24. 

D. J. Lund, E. S. Beatrice, S. T. Schuschereba, “Bioeffects data concerning the safe use of GaAs laser training devices,” in Combat Ocular Problems, , E. S. Beatrice, Ed., pp. 15–29, Letterman Army Institute of Research, San Francisco, California (1982).Google Scholar

25. 

C. P. Cain et al., “Thresholds for visible lesions in the primate eye produced by ultrashort near-infrared laser pulses,” Invest. Ophthalmol. Visual Sci. 40(10), 2343–2349 (1999).IOVSDA0146-0404Google Scholar

26. 

C. P. Cain et al., “Visible lesion thresholds from near-infrared pico and nanosecond laser pulses in the primate eye,” Proc. SPIE 2975, 133–137 (1997).PSISDG0277-786Xhttp://dx.doi.org/10.1117/12.275467Google Scholar

27. 

J. A. Zulich et al., “Ocular effects and safety standard implications for high-power lasers in the 1.31.4μm wavelength range,” USAF Technical Report No. AFRL-HE-BR-TR-2004-0187, pp. 1–16, AFRL/HEDO, San Antonio (2004).Google Scholar

28. 

D. H. Sliney et al., “What is the meaning of threshold in laser injury experiments? Implications for human exposure limits,” Health Phys. 82(3), 335–347 (2002).HLTPAO0017-9078http://dx.doi.org/10.1097/00004032-200203000-00006Google Scholar

Biographies for the authors are not available.

Morgan S. Schmidt, Paul K. Kennedy, Gary D. Noojin, Rebecca L. Vincelette, Robert J. Thomas, Benjamin A. Rockwell, "Trends in nanosecond melanosome microcavitation up to 1540 nm," Journal of Biomedical Optics 20(9), 095011 (21 September 2015). http://dx.doi.org/10.1117/1.JBO.20.9.095011
Submission: Received ; Accepted
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KEYWORDS
Absorption

Retina

Near infrared

Laser damage threshold

Skin

In vivo imaging

Eye

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