1 September 2006 Fiberoptic surgery by ultrabright lamp light
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J. of Biomedical Optics, 11(5), 050509 (2006). doi:10.1117/1.2363354
We report the first realization of interstitial surgery by ultrabright lamp light, on the kidneys and livers of live animals. A high-flux optic concentrates lamp emissions into an optical fiber for power delivery inside the body. The trials reveal surgical efficacy comparable to corresponding laser fiber optic treatments, as well as pronounced delayed tissue death.
Gordon, Shaco-Levy, Feuermann, Ament, and Mizrahi: Fiberoptic surgery by ultrabright lamp light

Laser fiberoptic surgery is a minimally invasive technique for the rapid and localized necrosis of growths in internal organs. 1, 2, 3, 4 The considerable cost of laser surgical systems prompts the quest for less expensive noncoherent photonic alternatives, especially since the key essential laser characteristic often is immense power density rather than monochromaticity or coherence.

Recently, we demonstrated that highly concentrated solar radiation can generate the same degree, rate, and type of photothermal tissue damage as lasers.5 However, its value is restricted by the ephemeral nature of sunlight. Here, we demonstrate the first exploitation of artificial noncoherent light for photothermal surgery on live rats, with an inexpensive device as efficacious as many surgical lasers.

A compact tabletop optical system was developed6 [Fig. 1a ] that reconstitutes the power density from the radiant plasma of a commercial ultrabright lamp inside an optical fiber that delivers light inside the body [Figs. 1b and 1c]. The light source was a 150-W xenon short-arc discharge lamp,7 with a 2.0-mm electrode gap, which emits an approximately 6000-K graybody spectrum enhanced by strong xenon emission peaks at wavelengths from 800 to 1000nm . This source is suitable for photothermal surgery because 1. it subsumes visible and near-infrared wavelengths where tissue optical penetration is greatest,1, 2 and 2. its brightness is high enough to provide the required power density, a feat unattainable with other light sources such as light-emitting diodes or incandescent lamps.

Fig. 1

Optics, surgical procedure, and pathology on living rats. (a) Drawing of the compact high-flux optic that concentrates ultrabright lamp emissions into an optical fiber. Intense noncoherent (white) light being delivered to the center of (b) the kidney and (c) liver of a live anesthetized rat, with NADH-diaphorase stain pathology for sections from rats in the immediate and 24-h groups. Irradiation of 1.9W was applied for 60 and 90s to these kidneys and livers, respectively. Viable tissue stains blue (dark). Nonviable (necrosed) tissue appears transparent (color online only).


A dual-mirror compact aplanatic optic [Fig. 1a] concentrates lamp emissions into an optical fiber. The (silvered specular) reflector contours enable high-flux transfer by eliminating spherical aberration and coma for a relatively small light source [Fig. 1(a)], and are essentially achromatic. The analytic equations that describe the reflectors were reported in Ref. 8. A hemispherical mirror recycles lamp emissions and heightens delivered power by about 50%.

The fiber had a quartz core diameter of 1.0mm , a teflon cladding, and a numerical aperture (NA) of 0.66. The fact that high power density mandates high NA, i.e., large delivery angle, follows from the principle of phase space conservation,9 and limits effective lamp surgery to the fiber being inside the organ or maintained close to its surface. The largest NA value in commercially available fibers that are also transmissive over the lamp’s emission spectrum (350 to 2500nm ) is 0.66. A pragmatic benefit of large-angle fiber emission is that lamp surgery does not engender the risk of eye injury to the surgical team.

The fiber was fit snugly into a protective Pyrex sleeve, via which light was injected to the organs. A sleeve thickness of about 1mm separated the fiber tip from the irradiated tissue, such that the spot size on the tissue was around 2mm .

Recent ex-vivo lamp surgery experiments6 guided our choice of irradiation times and flux values for generating immediate necrosis of the order of hundreds of mm3 : a compromise between the large lesions often needed in human surgery and the small size of rat kidney and liver. Lamp surgery with irradiation times varying from 60 to 240s and radiative input from 1.7 to 2.1W was conducted on the livers and kidneys of 13 anesthetized healthy adult rats divided into groups for histopathology examination at 0 (immediate group), 24, and 48 (delayed group) hours after surgery. Input power was purposely limited toward minimizing the risks of carbonization while producing sizable necrosis with relatively short exposures. Optical losses from the light source to the net delivered radiative power were assessed by ray-trace simulation in Ref. 8. Given the additional inefficiency in converting electricity to utilizable visible and near-IR light of sufficient brightness,7 lamp nominal power ratings of around 100W and higher are needed for effective photothermal surgery.

Healthy adult rats of body mass 300 to 400g were used in all experiments. The targeted organs were exposed to view with a longitudinal midline scalpel abdominal incision. Experiments were approved by the Institutional Animal Care and Use Committee of the Soroka Medical Center, Ben-Gurion University, Beersheva, Israel, and the surgeons underwent the health protection program for handling research animals. All organs were irradiated in regions that would not interfere with large veins, thus avoiding major vascular thrombosis that could otherwise contribute to lesion size.

Both the thick and thin lobes of the liver were irradiated in all procedures. Only one kidney was treated in each of the rats in the delayed group to avoid complete renal failure. For rats in the immediate group, a single exposure was applied to both kidneys. Those animals intended for delayed pathology were revived, and functioned without complication.

Liver and kidney pathology for all procedures was investigated with NADH-diaphorase stain. Pathology for the 24 and 48h groups was also performed with haematoxylin-and-eosin (H and E) stain for independent confirmation. The H and E technique was constrained to the delayed group, because it was previously shown to lead to dramatic underestimates for immediate pathology, the shortfall being mitigated when histological examination is postponed for 24h or longer.10

Pathology revealed the coagulative and ablative tissue transformations characteristic of laser surgery 1, 2, 3, 4 [Figs. 1b and 1c]. Lesion volumes were calculated from the lateral and longitudinal cross sectional diameters observed in the pathology slides, and varied from 100 to 800mm3 with shapes that were roughly hemiellipsoidal for liver and fully ellipsoidal for kidney. In samples where the necrosis traversed the entire organ, lesion volume was estimated from the linear dimensions of the actual asymmetric coagulated region. The extent of necrosis was distinctly larger after 24h [Figs. 1b and 1c] but did not increase further at 48h .

For a given time after surgery, the volume of dead tissue was approximately proportional to both exposure time and input power. Surgical efficacy E (lesion volume per delivered light energy) is then a suitable figure of merit for assessing and comparing results. Since no significant differences were discerned between animals in the 24 and 48h groups, those results were lumped into a single delayed category.

We found Ekidney=1.4±0.4 and Eliver=1.0±0.2mm3J immediately after irradiation—values commensurate with corresponding results for laser fiberoptic 1, 2, 3, 4 and solar5 surgery. For the delayed groups, Ekidney=2.3±0.4 and Eliver=2.7±1.2mm3J . Some lesions traversed the entire liver lobe [Fig. 1c]. They represent a lower bound for surgical efficacy, and account for the relatively large variance in Eliver .

When induced photothermally, delayed tissue death is an athermal process of sizable degree. 11, 12, 13, 14 The phenomenon is only sparsely documented for livers, 10, 11, 12, 13 and the understanding of the underlying mechanisms is incomplete.12 There are no analogous results of which we are aware for kidneys.

The comparable efficacy of lamp and laser procedures stems from their sharing similar optical and biophysical properties. 1, 2, 3, 5, 6 As such, the virtues of lamp surgery relative to hot-wire techniques, radiofrequency ablation, and cryoablation should be the same as those for laser surgery compared to the same methods.14

The confluence of maximum-flux optics and the suitability of ultrabright lamp light for interstitial photothermal surgery bodes well for the feasibility of a photonic tool that is potentially far less expensive than corresponding laser surgical systems and offers comparable effectiveness.


1.  A. Katzir, Lasers and Optical Fibers in Medicine, Academic Press, San Diego (1993). Google Scholar

2.  A. J. Welch and M. J. C. van Gemert, Optical-Thermal Response of Laser-Irradiated Tissue, Plenum Press, New York (1995). Google Scholar

3.  R. M. Verdaasdonk and F. P. van Swol, “Laser light delivery systems for medical applications,” Phys. Med. Biol.0031-9155 10.1088/0031-9155/42/5/010 42, 869–894 (1997). Google Scholar

4.  J. Heisterkamp, R. van Hillegersberg, E. Sinofsky, and J. N. M. Ijzermans, “Heat-resistant cylindrical diffuser for interstitial laser coagulation: comparison with the bare-tip fiber in a porcine liver model,” Lasers Surg. Med.0196-8092 10.1002/(SICI)1096-9101(1997)20:3<304::AID-LSM9>3.0.CO;2-U 20, 304–309 (1998). Google Scholar

5.  J. M. Gordon, D. Feuermann, M. Huleihil, S. Mizrahi, and R. Shaco-Levy, “Surgery by sunlight on live animals,” Nature (London)0028-0836 10.1038/424510a 424, 510 (2003). Google Scholar

6.  D. Feuermann, J. M. Gordon, and T. W. Ng, “Photonic surgery with noncoherent light,” Appl. Phys. Lett.0003-6951 10.1063/1.2185630 88, 114104 (2006). Google Scholar

7. Hamamatsu Corp., Technical Brochures, Shimokanzo, Toyooka Village, Iwata-gun, Shizuoka-ken 438-0193, Japan (2004). Google Scholar

8.  D. Nakar, D. Feuermann, and J. M. Gordon, “Aplanatic near-field optics for efficient light transfer,” Opt. Eng.0091-3286 10.1117/1.2181088 45, 030502 (2006). Google Scholar

9.  R. Winston, J. C. Miñano, and P. Benítez, Nonimaging Optics, Elsevier Academic Press, Oxford (2005). Google Scholar

10.  R. Shaco-Levy, J. M. Gordon, D. Feuermannm, M. Huleihil, and S. Mizrahi, “On appropriate pathology for photothermal surgery,” Lasers Surg. Med.0196-8092 10.1002/lsm.20060 35, 28–34 (2004). Google Scholar

11.  Y. Fujitomi, K. Kashima, S. Ueda, Y. Yamada, H. Mori, and Y. Uchida, “Histopathological features of liver damage induced by laser ablation in rabbits,” Lasers Surg. Med.0196-8092 10.1002/(SICI)1096-9101(1999)24:1<14::AID-LSM4>3.0.CO;2-2 24, 14–23 (1999). Google Scholar

12.  M. Nikfarjam, V. Muralidharan, and C. Christophi, “Mechanisms of focal heat destruction of liver tumors,” J. Surg. Res.0022-4804 10.1016/j.jss.2005.02.009 127, 208–223 (2005). Google Scholar

13.  J. M. Gordon, R. Shaco-Levy, D. Feuermann, M. Huleihil, and S. Mizrahi, “Photothermally induced delayed tissue death,” J. Biomed. Opt.1083-3668 10.1117/1.2210948 11, 030504 (2006). Google Scholar

14.  J. T. De Sanctis, S. N. Goldberg, and P. R. Mueller, “Percutaneous treatment of hepatic neoplasms: a review of current techniques,” Cardiovasc. Intervent Radiol.0174-1551 21, 273–296 (1998). Google Scholar

Jeffrey M. Gordon, Ruthy Shaco-Levy, Daniel Feuermann, Jared Ament, Solly Mizrahi, "Fiberoptic surgery by ultrabright lamp light," Journal of Biomedical Optics 11(5), 050509 (1 September 2006). http://dx.doi.org/10.1117/1.2363354






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