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Review

Femtosecond Laser Processing of Biodegradable Polymers

by
Mitsuhiro Terakawa
1,2
1
Department of Electronics and Electrical Engineering, Keio University, Yokohama 223-8522, Japan
2
School of Integrated Design Engineering, Keio University, Yokohama 223-8522, Japan
Appl. Sci. 2018, 8(7), 1123; https://doi.org/10.3390/app8071123
Submission received: 12 June 2018 / Revised: 2 July 2018 / Accepted: 9 July 2018 / Published: 11 July 2018
(This article belongs to the Special Issue Biomimetic Laser Processing)
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Abstract

:
Biodegradable polymers have attracted increasing attention in tissue engineering and drug delivery systems owing to their high biocompatibility and biodegradability. Among the various methods for shape forming and modification of biodegradable polymers, laser processing has advantages in a dry processing approach that can process complex-shaped surfaces without using toxic chemical components. This review provides an overview of femtosecond laser processing of biodegradable polymers, especially in the last decade. The interaction mechanism of femtosecond laser pulse and biodegradable polymers, e.g., bond dissociation after laser irradiation, affects the degradable property of biodegradable polymers, which has the potential to control the degradation and sustainability of a structure. Applied studies on controlling cell behavior, tissue scaffolding, and drug release are also described.

1. Introduction

Cells, growth factors, and scaffolds are essential elements for the regeneration of a three-dimensional (3D) structure in tissue engineering. Tissue scaffolds play a role as a matrix for cell proliferation until the tissue is regenerated. Consequently, biodegradable polymers are considered promising materials for tissue scaffolding because of their degradable properties. Repeated surgery for the removal of the scaffold is not necessary after tissue regeneration if the degradation of the scaffold in a body can be controlled for an appropriately sustained period of time. The biocompatibility of biodegradable polymers is comparably high, which realizes the translation of the materials into practical medical applications such as bone fixation material and sutures. To maximize the utility and potential of biodegradable polymers, technologies to fabricate the material into an arbitrary shape, i.e., processing technologies, are crucial. In particular, customization in shape forming is required in many cases in biomedical applications to fabricate tailored products for patients. Laser processing enables such tailored fabrication because of its suitability for computer-aided scanning and processing without a mold, which shows great potential for use in the technological transition from mass production to mass customization.
Laser processing of biodegradable polymers has many advantages in addition to its simple processing. A chemical solvent, whose residue may be toxic for the human body, is not necessary for laser-based fabrication. Additional microstructuring in the localized area is easy to perform even after the formation of a general shape. Because many biodegradable polymers show large optical absorption in ultraviolet (UV) wavelengths and less absorption at visible to near-infrared wavelengths, lasers oscillating at UV wavelengths have been used for processing in cases of nanosecond laser-based fabrication [1,2,3,4]. Kancharla et al. in 2001 reported the laser ablation of polyvinyl alcohol by using an XeCl excimer laser (308 nm in wavelength) and fourth harmonics generation (FHG) of a Nd:YAG laser (266 nm in wavelength) [1]. They reported that the heat-affected zone (HAZ) was relatively smaller while using UV wavelengths. Lazare et al. formed porous structures composed of micrometer-sized bubbles on the surface of collagen, chitosan, and polyvinylpyrrolidone (PVP) by using a KrF excimer laser (248 nm) [4]. However, because femtosecond lasers enable the processing of transparent materials via nonlinear optical interaction, femtosecond lasers have opened up new avenues to fabricate three-dimensional (3D) structures with visible and near-infrared wavelengths.
The degradation rate of biodegradable polymers depends on the crystallinity and composed micro- and nanostructures. Biodegradability can be changed by laser irradiation because laser pulses induce the scission of chemical bonding. In addition, laser processing enables the formation of not only entire shapes but also micro- and nano-sized substructures. Recently, considerable attention has been given to laser-based surface structuring of biopolymers for tissue engineering and for drug delivery systems because of these advantages.
In this review, the fundamentals and applications of femtosecond laser processing of biodegradable polymers are described by reviewing previous studies. A significant increase in the number of papers on femtosecond laser processing of biodegradable polymers has been seen in the last decade. Laser processing properties are introduced, along with micro- and nanostructuring, changes in biodegradability by laser irradiation, and experimental demonstrations for potential applications.

2. Femtosecond Laser Processing of Biodegradable Polymers

Soon after the rise of research on femtosecond laser processing, pioneering studies on femtosecond laser ablation of polymers have been reported. Initial studies, including those using polymethyl methacrylate, were performed with femtosecond lasers oscillating at UV wavelength [5,6], but, thanks to the high peak intensity of a femtosecond laser pulse, it is now widely known that polymers that show less linear optical absorption in visible to near-infrared wavelengths can be processed via nonlinear optical interaction by using femtosecond lasers [7,8]. Precise three-dimensional (3D) structures can be fabricated, not only on the surface of a material, but also in its interior. Furthermore, the ultrashort interaction time of the femtosecond laser pulse and a material realizes much smaller HAZ, even for the processing of polymers that have low glass-transition and melting temperatures. These advantages are promising for processing biodegradable polymers. Table 1 lists publications on femtosecond laser processing of biodegradable polymers.
A considerable number of publications have been reported since the year 2000. One of the pioneering works was the fabrication of a biodegradable stent by using a femtosecond laser, which was reported by Tönshoff et al. They reported that the HAZ with femtosecond laser ablation was 1/10 the size of that using a CO2 laser [9]. Although the details, including the material, were not described in the paper, the result showing the precise structure was sufficient to indicate the great potential of femtosecond lasers for polymer processing. Aguilar et al. compared the results of an 800-nm femtosecond laser with those from a 193-nm nanosecond laser and reported that a smaller HAZ was observed in the case of the femtosecond laser, indicating the precise processing of the material [12]. As for a picosecond laser, Ortiz et al. reported the laser ablation of poly-l-lactic acid (PLLA) by comparing the fundamental wave (1064 nm), the second harmonic generation (SHG) wave (532 nm), and the third harmonic generation (THG) wave (355 nm) of Nd:YVO4 laser [25]. They reported that laser ablation is governed by a multiphoton process in all cases, and UV wavelengths exhibited efficient laser ablation.
Interestingly, scission of bonds after laser ablation is different for a case with femtosecond laser pulses compared to that with nanosecond laser pulses, even for the same wavelength [43]. Figure 1 shows the C1s narrow scan XPS spectra of polylactic-co-glycolic acid (PLGA) (Figure 1a) and PLLA (Figure 1b). A wavelength of 266 nm was used for both cases, with femtosecond laser pulses and nanosecond laser pulses. The THG from a Ti:sapphire chirped pulse amplification (CPA) laser system (pulse duration 100 fs) (Coherent Inc., California, CA, USA) was used as the femtosecond laser pulse, whereas the FHG from a Q-switched Nd:YAG laser (pulse duration 5 ns) was used as the nanosecond laser pulse. As can be seen in Figure 1, although the peak at 289 eV remained relatively unchanged following nanosecond laser irradiation, the peak significantly decreased following femtosecond laser irradiation. Because the bond energy of a C=O bond (7.5 eV) is higher than the photon energy at 266 nm (4.65 eV), two-photon absorption at the irradiation of intense femtosecond laser pulses contributed to induce C=O bond dissociation. The difference between a nanosecond laser and a femtosecond laser can also be seen for different crystallinities of the polymers after laser irradiation. Figure 2 shows the XRD spectra of PLLA. Peaks in the XRD spectra of PLLA decreased in height following laser irradiation, and were significant with femtosecond laser pulse irradiation. The differences in the results of bond dissociation after laser irradiation affect the degradable property of biodegradable polymers, which will be described in the next section.

3. Degradable Property after Laser Irradiation

The degradable property of biodegradable polymers affects the durability and biocompatibility of the fabricated structure in addition to the sustainability of the structure in practical applications. Controlling the degradation property is one of the keys to effective utilization, which may depend on the applications and patients. The biodegradation of a biodegradable polymer in a physiological environment proceeds via the hydrolysis of ester bonds in the presence of absorbed water. The degradation rate of a biodegradable polymer can be influenced by several factors including molecular weight, crystallinity, surface morphology, and surface hydrophilicity. Several methods have been proposed to control these factors, such as annealing [49], copolymerization [50], porous structure formation [51], and light-based modification [52,53,54,55]. Laser-based methods enable high spatial selective modification, which provides localized changes in the biodegradable property, even after molding. Because the change in biodegradable properties by laser irradiation is an emerging technology, papers describing the direct evaluation on biodegradable properties are limited, although the crystallinity, molecular weight, and bond dissociation after laser irradiation have been studied widely. In 2005, a study on the change in biodegradation rate by laser processing was reported. Aguilar et al. studied the laser ablation of polycaprolactone (PCL) and polyglycolic acid (PGA) by using ArF excimer laser (wavelength 193 nm) [12]. They reported the scission of chemical bonds and the generation of CO and CO2 gases, which was analyzed by X-ray photoelectron spectroscopy (XPS). Laser-irradiated PCL exhibited a high degradation rate compared to non-irradiated PCL, whereas PGA showed no significant change in degradation rate. Controlling the degradation rate was also attempted by taking advantage of the thermal effect of laser pulse because the degradation rate of the biodegradable polymers depends largely on the molecular structure. Laser pulses comparable to or longer than nanoseconds have been used for obtaining thermal effects, i.e., laser annealing. By using a laser, the annealing depth can be controlled by changing the wavelength. Because of the different penetration depths in a material, there is high spatial controllability of both the depth and the irradiated area, since the laser irradiation area is easily controlled by the beam diameter and laser scanning. Hsu et al. investigated the decrease in the crystallinity of PLLA after laser pulse irradiation (wavelength 248 nm, pulse duration 25 ns), which was evaluated by wide-angle X-ray diffraction (WAXD) [54].
On the basis of the decrease in the ratio of O1s to C1s peaks, they discussed the dissociation of C–O bonds and the possible emission of oxygen atoms from the film in the form of CO and CO2. Slepička et al. reported a decrease in the wettability of PLLA with laser fluence and number of pulses; the latter has a more significant influence [56].
Femtosecond laser processing of biodegradable polymers has advantages in 3D precise processing; however, detailed studies on the effects of femtosecond laser irradiation on the degradable property are limited to a few cases. Our group found different degradation rates of the biodegradable polymer after femtosecond laser ablation, which depends on the laser wavelength [40]. Figure 3 shows a comparison of laser ablation craters on a PLGA surface at different times after irradiation with 800-nm and 400-nm femtosecond laser pulses. Laser fluences and number of pulses were carefully selected to fabricate laser ablation craters of the same diameter to minimize the initial difference in the diameter. A crater fabricated by mechanical milling is also shown for comparison. The crater fabricated by femtosecond laser pulses at 800 nm in wavelength showed no significant change in diameter after 48 h of immersion in phosphate-buffered saline (PBS), whereas that by 400-nm femtosecond laser pulses exhibited comparably rapid expansion over an immersion period, indicating the acceleration of degradation. The acceleration of degradation can also be confirmed by the mass change. As shown in Figure 4, there was a significant decrease in the mass of the samples irradiated by 400 nm laser pulses. These results demonstrate the potential of femtosecond laser processing for controlling the degradation rate after form shaping and structuring by selecting a suitable wavelength.
The degradation rate of a biodegradable polymer after laser irradiation has been explained by the decrease in crystallinity associated with surface melting, and in molecular weight owing to the photolysis of chemical bonds. Because PLGA is a polymer with less crystallinity, with the wavelength of 400 nm, the significant acceleration of the biodegradation in the case of PLGA [40] is attributable to the decrease in molecular weight induced by the chemical bond dissociation rather than the change in crystallinity.

4. Formation of Laser-Induced Periodic Surface Structure (LIPSS) on the Surface of Biodegradable Polymers

Laser-induced periodic surface structure (LIPSS) is a unique nanostructure formed by laser irradiation of multiple pulses at laser fluence under or near the threshold of single-pulse laser ablation. Because an LIPSS can be formed in the laser-irradiated area with unfocused or loosely focused laser pulses, a large area can be treated, i.e., the formation throughput of subwavelength periodic structures is comparably high. Many studies on LIPSS formation on metals, dielectrics, and semiconductors have been reported. The formation of LIPSS on titanium [57] and titanium oxide [58] has been studied for enhancing the adhesion of cells and alignment toward biomedical applications. Studies on LIPSS formation on the surface of polymers can be traced back to a publication in 1985 [59]; however, investigations with biodegradable polymers are limited to a few cases. Pérez et al. demonstrated the formation of LIPSS on chitosan and polyvinylpyrrolidone, highly water-soluble biodegradable polymers [60]. They used nanosecond laser pulses at wavelengths of 193, 213, and 266 nm; therefore, linear absorption was the dominant interaction.
Periodic structures formed on a PLLA surface by using femtosecond laser pulses are shown in Figure 5. Scanning electron microscopy (SEM) images are shown for the cases of 800, 400, and 266 nm for comparison. At 800 nm, LIPSS was rarely formed only under limited experimental conditions (Figure 5a). The structure perpendicular to the laser polarization had a 149-nm average periodicity, much shorter than the laser wavelength. Figure 5b shows LIPSS formed with a 400-nm laser wavelength. Compared to the case at 800 nm, LIPSS perpendicular to the polarization was formed at wide laser fluence and pulse duration conditions. Because the photon energy at 400 nm is higher than at 800 nm, the number of photons necessary for multiphoton absorption is smaller at 400 nm, resulting in the facilitation of Coulomb explosion or bond dissociation mediated by Norrish type II reaction. The LIPSS, which has a slight curvature, was mostly formed on the peripheral part of the ablation crater. Unlike the cases at 800 nm and 400 nm, the LIPSS formed at 266 nm (Figure 5c) was quite shallow and had no dependency on the polarization. The mechanism of LIPSS formation may be different for the 266-nm case. Photomechanical pressure by the thermal effect of laser pulses possibly contributed to LIPSS formation.

5. Cell Adhesion and Behavior on the Laser-Irradiated Surface of Biodegradable Polymers

Cell behavior is affected by the surface micro- and nanostructure of the biodegradable polymers, as well as their wettability. Because the ultrashort laser pulse enables processing of transparent polymers, several studies on the fabrication of micro- and nanostructures on the surface of biodegradable polymers have been reported toward controlling cell behavior. Yeong et al. reported the attachment and alignment properties of mouse myoblasts on the surface of PLLA−PCL, in which microchannels were formed by 800-nm femtosecond laser pulses [21]. The cells exhibited attachment in the channels, and a high degree of alignment was observed. It was also reported that the microchannels with topographic micropatterns on a PLLA−PCL substrate fabricated by femtosecond laser ablation promote upregulation of several hallmark markers associated with myogenesis for human mesenchymal stem cells (hMSCs) cultured on a scaffold with microchannels [26]. In 2014, Ortiz et al. reported an investigation on the effect of micropattern on the proliferation and morphology of breast cancer cells. They reported that the pattern direction directly affected cell proliferation, leading to the guided growth of cell clusters along that direction [31]. The structure suitable for controlling cell behavior is not limited to microchannels. Castillejo et al. compared UV femtosecond and nanosecond laser pulses to form porous structures on chitosan, starch, and their blended films. Femtosecond laser pulses of 248 nm yield a porous, foamy superficial layer on the film surface, in which cells are likely to proliferate on the structured surface [29]. Jun et al. showed that fibrous platforms with patterned hierarchical topographies fabricated by femtosecond laser ablation can regulate myoblast behavior (Figure 6) [38]. Cell behavior is closely related to the surface wettability. Toosi et al. reviewed the femtosecond laser processing parameters on the surface morphology and the wettability [61].

6. Laser-Triggered Molecular Release from Biodegradable Polymers

Because the degradation rate of biodegradable polymers can be enhanced by laser irradiation, laser-triggered release and laser-controlled-sustained release of drug molecules have been investigated. Laser-based methods, among other methods, have advantages in spatial characteristics and applicability to catheter-based systems using optical fibers. Most studies for controlling molecular release using lasers take advantage of metal nanoparticles as an absorber [62] because many polymers show little absorption of visible and near-infrared light. A limited number of papers reported molecular release without doping materials. Hsu et al. studied the release of embedded fluorescence molecules from biodegradable polymers using nanosecond laser pulses at a wavelength of 248 nm [63]. The acceleration of molecular release by the degradation was reported (Figure 7). They found that laser irradiation decreased the crystallinity of the polymer surface, resulting in the acceleration of release. As for studies using femtosecond lasers, Umemoto et al. reported that femtosecond laser irradiation at 400 nm wavelength accelerates the release of loaded-fluorescent molecules from PLGA, whereas 800 nm laser irradiation does not induce a comparable degree of change in the release of loaded molecules [42]. This may be due to the different degree of change in the degradation rate depending on the laser wavelength, as described in Section 3. Ariyasu et al. reported the burst release of embedded molecules triggered by femtosecond laser pulses [64]. The release of fluorescence molecules encapsulated in biodegradable microcapsules was significantly enhanced by laser irradiation. The rupture of biodegradable microcapsules was also observed after laser irradiation.

7. Conclusions and Perspectives

The interaction of femtosecond lasers and biodegradable polymers can be discussed using laser interaction with polymers; however, laser irradiation induces changes in the degradation rate of biodegradable polymers, which is unique and interesting from the point of view of the mechanism and applications. Previous studies revealed that the degradation rate is different depending on the femtosecond laser wavelength, and the difference is attributable to the difference in chemical bond dissociation. The difference in chemical bond dissociation is closely related to nonlinear interaction and physics with intense femtosecond laser pulses; however, further study is necessary to reveal the mechanism in detail. By controlling the degradation rate of biodegradable polymers, attractive applications will be realized such as control of the residual time of tissue scaffolds, controlled molecular release of drug molecules for drug delivery systems, and sustained release of insulin for the treatment of diabetes. Lasers provide high spatial controllability and highly precise structuring, which are expected to help realize sophisticated biomedical devices. In addition, recent progress in femtosecond laser processing such as cooled laser ablation [65], Bessel beam [66], etc. has the potential to fabricate a much more precise and desirable structure.

Acknowledgments

The author is grateful to Shuhei Yada, Akimichi Shibata, Taiga Umemoto, and Naonari Kondo for their contributions to the research in our group related to laser processing of biodegradable polymers.

Conflicts of Interest

The author declares no conflict of interest.

Abbreviations

CPAchirped pulse amplification
FHGfourth harmonics generation
HAZheat affected zone
LIPSSlaser induced periodic surface structure
PCLpolycaprolactone
PGApolyglycolic acid
PLLApoly-l-lactic acid
PLGApolylactic-co-glycolic acid
PPPpolylactide-polyethylene glycol-polylactide
PVPpolyvinylpyrrolidone
SEMscanning electron microscopy
SHGsecond harmonics generation
THGthird harmonics generation
UVultraviolet
WAXDwide-angle X-ray diffraction
XPSX-ray photoelectron spectroscopy
XRDX-ray diffraction
3Dthree-dimensional

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Figure 1. C1s narrow scan XPS spectra for the surface of PLGA films (a) and PLLA films (b). Black, red, and purple lines indicate non-irradiated films (control), films irradiated with a nanosecond laser, and films irradiated with a femtosecond laser, respectively. A wavelength of 266 nm was used for both cases with femtosecond laser pulses and nanosecond laser pulses.
Figure 1. C1s narrow scan XPS spectra for the surface of PLGA films (a) and PLLA films (b). Black, red, and purple lines indicate non-irradiated films (control), films irradiated with a nanosecond laser, and films irradiated with a femtosecond laser, respectively. A wavelength of 266 nm was used for both cases with femtosecond laser pulses and nanosecond laser pulses.
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Figure 2. XRD spectra for the surface of PLLA films. Black, red, and purple lines indicate non-irradiated films (control), films irradiated with a nanosecond laser, and films irradiated with a femtosecond laser, respectively. A wavelength of 266 nm was used for both cases femtosecond laser pulses and nanosecond laser pulses.
Figure 2. XRD spectra for the surface of PLLA films. Black, red, and purple lines indicate non-irradiated films (control), films irradiated with a nanosecond laser, and films irradiated with a femtosecond laser, respectively. A wavelength of 266 nm was used for both cases femtosecond laser pulses and nanosecond laser pulses.
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Figure 3. Digital microscopic images of craters formed on PLGA films. The time shown in each figure indicates the time of the samples immersed in PBS at 37 °C. (a) Crater formed by mechanical milling. (b) Laser ablation crater under the condition of 800 nm wavelength, 1.0 J/cm2, 15,000 pulses. (c) Laser ablation crater under the condition of 400-nm wavelength, 0.15 J/cm2, 15,000 pulses. Laser fluences were carefully selected to fabricate laser ablation craters of the same diameter to minimize the initial difference in the diameter.
Figure 3. Digital microscopic images of craters formed on PLGA films. The time shown in each figure indicates the time of the samples immersed in PBS at 37 °C. (a) Crater formed by mechanical milling. (b) Laser ablation crater under the condition of 800 nm wavelength, 1.0 J/cm2, 15,000 pulses. (c) Laser ablation crater under the condition of 400-nm wavelength, 0.15 J/cm2, 15,000 pulses. Laser fluences were carefully selected to fabricate laser ablation craters of the same diameter to minimize the initial difference in the diameter.
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Figure 4. Mass of PLGA films remaining during degradation. Closed squares, red triangles, and closed blue circles indicate PLGA films without laser irradiation, PLGA films irradiated at 800 nm, and PLGA films irradiated at 400 nm, respectively.
Figure 4. Mass of PLGA films remaining during degradation. Closed squares, red triangles, and closed blue circles indicate PLGA films without laser irradiation, PLGA films irradiated at 800 nm, and PLGA films irradiated at 400 nm, respectively.
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Figure 5. LIPSS formed on the PLLA surface by the irradiation of femtosecond laser pulses at different wavelengths. (a) 800 nm, 1.0 J/cm2, 3000 pulses; (b) 400 nm, 0.4 J/cm2, 5000 pulses; (c) 266 nm, 7.5 mJ/cm2, 5000 pulses. Red double-headed arrows indicate the polarization direction.
Figure 5. LIPSS formed on the PLLA surface by the irradiation of femtosecond laser pulses at different wavelengths. (a) 800 nm, 1.0 J/cm2, 3000 pulses; (b) 400 nm, 0.4 J/cm2, 5000 pulses; (c) 266 nm, 7.5 mJ/cm2, 5000 pulses. Red double-headed arrows indicate the polarization direction.
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Figure 6. Effect of laser-ablated groove patterns on the adhesion and shape transition of C2C12 myoblasts. Scale bar indicates 100 μm. Reproduced with permission from [38], [ACS Applied Materials & Interfaces]; published by [ACS Publications], [2016].
Figure 6. Effect of laser-ablated groove patterns on the adhesion and shape transition of C2C12 myoblasts. Scale bar indicates 100 μm. Reproduced with permission from [38], [ACS Applied Materials & Interfaces]; published by [ACS Publications], [2016].
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Figure 7. Drug release profiles of laser-treated and non-laser-treated matrices. Reproduced with permission from [63], [ACS Applied Materials & Interfaces]; published by [ACS Publications], [2016].
Figure 7. Drug release profiles of laser-treated and non-laser-treated matrices. Reproduced with permission from [63], [ACS Applied Materials & Interfaces]; published by [ACS Publications], [2016].
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Table
Table 1. Ultrashort pulse laser processing of biodegradable polymers.
Table 1. Ultrashort pulse laser processing of biodegradable polymers.
YearWavelengthPulse WidthMaterialNoteRef.
2000n/an/an/amedical stents fabrication[9]
2003mid IR15 us, 5 psGelatinsurface ablation[10]
2005800,
248 nm		110 fs,
23 ns		PCLenhancement of wettability and hydrophobic nature[11]
2005800 nm,
193 nm		220 fs,
35 ns		PCL, PGAanalysis of chemical structure and biodegradability[12]
2005800 nm45 fscollagencell attachment on patterned surface[13]
2007775 nm,
n/a		150 fs,
120 ns		PCL, PETlaser ablation on electrospun scaffolds[14]
2007800, 400, 266 nm, 1064, 532, 355, 266 nm90 fs,
6 ns		gelatinsubmicron structures foaming[15]
2007800, 400, 266 nm90 fsgelatinnano-foaming[16]
2008790 nm60 fsgelatin, curcumin-doped gelatin, collagenfemtosecond laser ablation[17]
2008800, 400, 266 nm,
248 nm		90 fs,
25 ns		gelatin, collagenDiscussion on the mechanism of nano-foaming[18]
2010800 nm30 fsgelatin, PVP, PVP/chitosan3D internal modification of biopolymers[19]
2010800 nm150 fsPCL, PLAevaluation of HAZ[20]
2010800 nm150 fsPLLA-PCL copolymerevaluation of cell alignment on direct laser written surface[21]
2011800 nm20 fsPLA3D scaffold fabrication[22]
2011775 nm150 fsPCL/gelatinmicro-patterned electrospun scaffold and cell behavior[23]
2011775 nm150 fsPCLeffect of micro-channel on cell behavior[24]
20111064 nm10 psPLLAeffect of crystallinity on micro-grating fabrication[25]
2011800 nm150 fsPLA-PCLeffect of laser patterned surface on up regulation of myogenic markers[26]
2012800 nm100 fsPLLAeffect of laser processed electrospun scaffolds on cell behavior[27]
2012800 nm120 fsPLGAmicro-vessel scaffold fabrication[28]
2012248 nm,
213 nm,
248 nm		20 ns,
150 ps, 500 fs		chitosan, starch, chitosan/starcheffect of pulse duration on porous surface fabrication[29]
2013800 nm150 fsPLA-PCLnano/micro-grating and cell behavior[30]
20141064 nm10 psPLLA, PSmicro-patterned surface for cancer cell confinement[31]
2014800 nm30–100 fsGelatin, collagen, collagen-elastinporous structure in ablation area, cell proliferation.[32]
20141030, 515 nm400–800 fsPLLA, Poly(d,l-lactid)high repetition rate up to 500 kHz[33]
2015520 nm,
532 nm		350 fs,
10 ps		PLLA, PLGAparameter dependence[34]
2015800 nm, 400 nm100 fsPLLALIPSS formation[35]
2015775 nm200 fsPLGA, PPPfemtosecond laser ablation and MAPLE for cell adhesion[36]
20151040 nm115 fsPLAprocessing in air and in water, high-rep rate of 57 MHz[37]
2016515 nm400 fsPLLA electrospun fibersfibrous platforms for cell adhesion and direction[38]
2016800 nm30 fsCollagen/elastin blends, gelatinlaser ablation for changing cell adhesion and wettability[39]
2016800 nm, 400 nm100 fsPLGAbiodegradability depending on the laser wavelength[40]
2016515 nm450 fsPLLAexperimental optimization of laser parameters[41]
2017800 nm, 400 nm100 fsPLGArelease of loaded molecules after laser ablation[42]
2017266 nm100 fs,
5 ns		PLGA, PLLAcomparison of fs and ns lasers[43]
20171030 nm180 fs,PLAnano-void formation[44]
2018800, 275 nm85 fsPLAcomparison of six polymers[45]
2018800 nm30 fschitosantexturing for bio-interfaces[46]
2018800 nm30 fsPCLosteoblast cell adhesion[47]
2018515 nm450 fsPLLAdetailed study on physicochemical properties[48]

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Terakawa, M. Femtosecond Laser Processing of Biodegradable Polymers. Appl. Sci. 2018, 8, 1123. https://doi.org/10.3390/app8071123

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Terakawa M. Femtosecond Laser Processing of Biodegradable Polymers. Applied Sciences. 2018; 8(7):1123. https://doi.org/10.3390/app8071123

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Terakawa, Mitsuhiro. 2018. "Femtosecond Laser Processing of Biodegradable Polymers" Applied Sciences 8, no. 7: 1123. https://doi.org/10.3390/app8071123

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Terakawa, M. (2018). Femtosecond Laser Processing of Biodegradable Polymers. Applied Sciences, 8(7), 1123. https://doi.org/10.3390/app8071123

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