<?xml version="1.0" encoding="UTF-8"?><!DOCTYPE article  PUBLIC "-//NLM//DTD Journal Publishing DTD v3.0 20080202//EN" "http://dtd.nlm.nih.gov/publishing/3.0/journalpublishing3.dtd"><article xmlns:mml="http://www.w3.org/1998/Math/MathML" xmlns:xlink="http://www.w3.org/1999/xlink" dtd-version="3.0" xml:lang="en" article-type="research article"><front><journal-meta><journal-id journal-id-type="publisher-id">OJRM</journal-id><journal-title-group><journal-title>Open Journal of Regenerative Medicine</journal-title></journal-title-group><issn pub-type="epub">2169-2513</issn><publisher><publisher-name>Scientific Research Publishing</publisher-name></publisher></journal-meta><article-meta><article-id pub-id-type="doi">10.4236/ojrm.2013.24015</article-id><article-id pub-id-type="publisher-id">OJRM-38828</article-id><article-categories><subj-group subj-group-type="heading"><subject>Articles</subject></subj-group><subj-group subj-group-type="Discipline-v2"><subject>Biomedical&amp;Life Sciences</subject><subject> Medicine&amp;Healthcare</subject></subj-group></article-categories><title-group><article-title>
 
 
  Long-term morphological evaluation of porous poly-DL-lactic acid for soft tissue augmentation
 
</article-title></title-group><contrib-group><contrib contrib-type="author" xlink:type="simple"><name name-style="western"><surname>ukawa</surname><given-names>Ken</given-names></name><xref ref-type="aff" rid="aff1"><sup>1</sup></xref><xref ref-type="corresp" rid="cor1"><sup>*</sup></xref></contrib><contrib contrib-type="author" xlink:type="simple"><name name-style="western"><surname>Tachikawa</surname><given-names>Noriko</given-names></name><xref ref-type="aff" rid="aff1"><sup>1</sup></xref></contrib><contrib contrib-type="author" xlink:type="simple"><name name-style="western"><surname>Munakata</surname><given-names>Motohiro</given-names></name><xref ref-type="aff" rid="aff1"><sup>1</sup></xref></contrib><contrib contrib-type="author" xlink:type="simple"><name name-style="western"><surname>Akino</surname><given-names>Norio</given-names></name><xref ref-type="aff" rid="aff1"><sup>1</sup></xref></contrib><contrib contrib-type="author" xlink:type="simple"><name name-style="western"><surname>Kasugai</surname><given-names>Shohei</given-names></name><xref ref-type="aff" rid="aff1"><sup>1</sup></xref></contrib></contrib-group><aff id="aff1"><addr-line>Department of Oral Implantology and Regenerative Dental Medicine, Tokyo Medical and Dental University, Tokyo, Japan;</addr-line></aff><author-notes><corresp id="cor1">* E-mail:<email>yukairm@tmd.ac.jp(UK)</email>;</corresp></author-notes><pub-date pub-type="epub"><day>07</day><month>10</month><year>2013</year></pub-date><volume>02</volume><issue>04</issue><fpage>106</fpage><lpage>111</lpage><history><date date-type="received"><day>20</day>	<month>September</month>	<year>2013</year></date><date date-type="rev-recd"><day>20</day>	<month>October</month>	<year>2013</year>	</date><date date-type="accepted"><day>27</day>	<month>October</month>	<year>2013</year></date></history><permissions><copyright-statement>&#169; Copyright  2014 by authors and Scientific Research Publishing Inc. </copyright-statement><copyright-year>2014</copyright-year><license><license-p>This work is licensed under the Creative Commons Attribution International License (CC BY). http://creativecommons.org/licenses/by/4.0/</license-p></license></permissions><abstract><p>
 
 
   Soft tissues are important for aesthetic considerations in implant therapy. The purpose of this study was to investigate soft tissue augmentation by using porous poly-DL-lactic acid (PDLLA)shaped as a tablet, with a diameter of5.0 mmand a height of2.0 mm. Porous PDLLA was implanted between the periosteal and epithelial tissues in 25 rats that were sacrificed at 1, 2, 4, 12, and 24 weeks. The average height of the PDLLA scaffolds at approximately 24 weeks was 1.85 &#177;0.08 mm, and the molecular weight decreased with time. Sinusoidal capillaries at 1 week, connective tissues at 4 weeks, and necrotic tissues at 24 weeks were observed more than other periods. At 24 weeks, the connective tissue surviving in the pores was confirmed to contain blood vessels; therefore, blood vessels are considered to be critical for the survival of soft tissue in scaffold pores. In this study, PDLLA was found to be useful for soft tissue augmentation in the long term. Although the molecular weight of PDLLA decreased with time, the height of the PDLLA scaffolds was preserved. The connective tissue surviving in the pores of the scaffolds at 24 weeks were associated with blood vessels. Further studies are necessary to investigate the optimal scaffold shape and surface characteristics to improve the penetration of blood vessels. 
 
</p></abstract><kwd-group><kwd>Poly-DL-Lactic Acid (PDLLA); Soft Tissue Augmentation; Biodegradation; Porous;Scaffolds</kwd></kwd-group></article-meta></front><body><sec id="s1"><title>1. INTRODUCTION</title><p>Tissue engineering for dental implant therapy primarily relies on bone regeneration as dental implants are inserted into bone [<xref ref-type="bibr" rid="scirp.38828-ref1">1</xref>]. However, for the prognosis of implant therapy, soft tissues such as gingiva are as important as hard tissues such as the bone. Additionally, bone resorption is a critical factor for maintaining the gingival margin line to achieve aesthetic success. In the case of anterior implant therapy, black triangles often appear at the interdental papilla, and in the absence of sufficient soft tissue, plaque and bacteria can easily adhere to implants, particularly because the complicated shape and rough surface of implants complicate removal of plaque and bacteria [<xref ref-type="bibr" rid="scirp.38828-ref2">2</xref>]. Patients who receive implant therapy often have insufficient soft tissue volume. Therefore, soft tissue augmentation, particularly around dental implants, is an important concern.</p><p>Soft tissue augmentation is usually performed using autogenous materials through connective tissue grafts (CTGs) [<xref ref-type="bibr" rid="scirp.38828-ref3">3</xref>]. Harvesting in the case of CTGs is complex because the operator treats the donor sites and thus requires additional chair time. Not all patients will have sufficient connective tissue for grafting, and even if they have sufficient tissue, the CTG is absorbed to 76% of its original size during the transplantation operation and over time [<xref ref-type="bibr" rid="scirp.38828-ref4">4</xref>]. Preparation of repair materials prior to the operation may solve this problem. Regarding autogenous materials, McGuire reported a living tissue-engineered human fibroblast-derived dermal substitute [<xref ref-type="bibr" rid="scirp.38828-ref5">5</xref>]. The method, however, used for preparing this construct is complex and requires time and resources. Gao [<xref ref-type="bibr" rid="scirp.38828-ref6">6</xref>] reported that allogeneic materials are derived from animal tissue, e.g., bovine or porcine tissue. However, even when allogeneic materials are completely sterilized, they present the risk of causing unknown disorders [<xref ref-type="bibr" rid="scirp.38828-ref7">7</xref>]. The use of synthetic materials may resolve these problems. Wei et al. [<xref ref-type="bibr" rid="scirp.38828-ref8">8</xref>] reported the preparation of scaffolds from biocompatible and porous PLLA, PDLLA, and PLGA materials. Porous PLLA has been studied for the reconstruction of nerves and blood vessels [9,10]. However, no reports have addressed soft tissue augmentation and reconstruction.</p><p>The aims of the present study were to investigate synthetic, biocompatible, and porous PDLLA for soft tissue augmentation.</p></sec><sec id="s2"><title>2. MATERIALS AND METHODS</title><sec id="s2_1"><title>2.1. Materials</title><p>Porous pure PDLLA (D/L = 50/50 mol%; porosity calculated from apparent density, 70%; pore diameter, 40 - 400 μm) was provided by Takiron (Hyogo, Japan) (<xref ref-type="fig" rid="fig1">Figure 1</xref>) and was shaped as a tablet with a diameter of 5.0 mm and a height of 2.0 mm. The molecular weight (Mw) of the PDLLA was 130.9 kDa.</p></sec><sec id="s2_2"><title>2.2. Animals</title><p>In these experiments, twenty-five 8-week-old male Wistar/ST rats were used. The animals were kept under standard housing conditions and allowed ad libitum access to water and a standard dry diet. The 25 rats were divided into 5 groups containing 5 rats each, based on the time points of 1, 2, 4, 12, and 24 weeks.</p><p>The rearing of animals and animal experiments were performed at the Institute of Laboratory Animals and were conducted in accordance with the guidelines for animal experimentation at Tokyo Medical and Dental University (approval no.0110231B). Anesthesia was induced using inhaled diethyl ether and then maintained by intramuscular administration of ketamine hydrochloride (1.64 ml/kg body weight) and celactal (0.36 ml/kg body weight). After skin incision, the panniculus between the epithelium and periosteum was exfoliated via blunt dissection. A PDLLA scaffold was placed onto the periosteum, and the 4 corners of the scaffold were fixed using 5/0 nylon sutures (SOFTRETCH, GC, Tokyo, Japan) (Figures 2 and 3). Two scaffolds were placed for 3 rats in each of the 4-week, 12-week, and 24-week groups, where one scaffold was fixed with nylon sutures and the other was not. All skin incisions were closed using 4/0 nylon sutures.</p><p>The animals were killed at 1, 2, 4, 12, and 24 weeks after surgery by an overdose of pentobarbital-natrium. The scaffolds were removed together with the cranial bone and surrounding tissues. The other scaffolds that were not fixed with nylon sutures were removed with the surrounding tissue. All samples were fixed with 10% formalin solution. Five samples from each group were embedded in paraffin for H &amp; E staining. Other samples, which were not fixed with nylon sutures, were used for measurement of molecular weight.</p></sec><sec id="s2_3"><title>2.3. Measurement of Scaffold Height</title><p>The height of the scaffold was measured to evaluate</p><p>the preservation of the scaffolds. When the animals were sacrificed, the scaffolds were measured with digital calipers to determine their height. The height was provided for the line from the top position with more than twothird of the former material’s diameter to the lower base.</p></sec><sec id="s2_4"><title>2.4. Measurement of Molecular Weight</title><p>When the rats were sacrificed, the samples that were not fixed with nylon sutures were used for the measurement of molecular weight over time by using gel permeation chromatography (GPC; HLC-8320GPC; Tosoh Corporation, Japan).</p></sec><sec id="s2_5"><title>2.5. Histological Analyses</title><p>The connective tissue area, sinusoidal capillaries, and necrotic tissue were measured to evaluate the replacement of the scaffold with connective tissue (Image J software) (<xref ref-type="fig" rid="fig4">Figure 4</xref>). The diameter of the connective tissue was measured in 5 slides at 24 weeks. Connective tissue that was narrow in the middle or that existed around the PDLLA was measured by dividing by the minimal width (Image J software 1.46 r, National Institutes of Health, USA).</p></sec><sec id="s2_6"><title>2.6. Statistical Analysis</title><p>The values have been expressed as mean &#177; standard deviation values. Statistical analysis was performed by one-way analysis of variance (ANOVA) and Tukey’s HSD test or the Games-Howell test, if necessary, by using the SPSS software for Windows (PASW Statistics 18.0; SPSS Inc., Japan).</p></sec></sec><sec id="s3"><title>3. RESULTS</title><sec id="s3_1"><title>3.1. Measurement of Scaffold Height</title><p>The scaffold height was measured (<xref ref-type="fig" rid="fig5">Figure 5</xref>), and some of the values were at least 2.00 mm because the samples included tissues on the top of the scaffold. Significant differences were observed between the height at 24 weeks and those at 1, 2, and 4 weeks (p &lt; 0.05).</p></sec><sec id="s3_2"><title>3.2. Measurement of Molecular Weight</title><p>The molecular weight was measured (Tables 1 and 2), and significant differences were observed over time (p &lt; 0.05).</p></sec><sec id="s3_3"><title>3.3. Histological Analyses</title><p>PDLLA was not observed on the slides because it was dissolved by organic solvents such as xylene that were used during paraffin embedding. However, the volume and shape of the tissue in the scaffold pores were main-</p><back><ref-list><title>References</title><ref id="scirp.38828-ref1"><label>1</label><mixed-citation publication-type="other" xlink:type="simple">Dahlin, C., Linde, A., Gottlow, J. and Nyman, S. (1988) Healing of bone defects by guided tissue regeneration. Plastic and Reconstructive Surgery, 81, 672-676. http://dx.doi.org/10.1097/00006534-198805000-00004</mixed-citation></ref><ref id="scirp.38828-ref2"><label>2</label><mixed-citation publication-type="other" xlink:type="simple">López-Cerero, L. (2008) Dental implant-related infections. Enfermedades Infecciosas y Microbiología Clínica, 26, 589-592. http://dx.doi.org/10.1157/13128277</mixed-citation></ref><ref id="scirp.38828-ref3"><label>3</label><mixed-citation publication-type="journal" xlink:type="simple"><name name-style="western"><surname>Silverstein</surname><given-names> L.H.</given-names></name>,<name name-style="western"><surname> Lefkove</surname><given-names> M.D. and Garnick</given-names></name>,<name name-style="western"><surname> J.J. </surname><given-names>  </given-names></name>,<etal>et al</etal>. (<year>1994</year>)<article-title>The use of free gingival soft tissue to improve the implant/soft-tissue interface</article-title><source> Journal of Oral Implantology</source><volume> 20</volume>,<fpage> 36</fpage>-<lpage>40</lpage>.<pub-id pub-id-type="doi"></pub-id></mixed-citation></ref><ref id="scirp.38828-ref4"><label>4</label><mixed-citation publication-type="other" xlink:type="simple">Borghetti, A., Glise, J.M., Monnet-Corti, V. and Dejou, J. (1999) Comparative clinical study of a bioabsorbable membrane and subepithelial connective tissue graft in the treatment of human gingival recession. Journal of Periodontology, 70, 123-130. http://dx.doi.org/10.1902/jop.1999.70.2.123</mixed-citation></ref><ref id="scirp.38828-ref5"><label>5</label><mixed-citation publication-type="other" xlink:type="simple">McGuire, M.K. and Nunn, M.E. (2005) Evaluation of the safety and efficacy of periodontal applications of a living tissue-engineered human fibroblast-derived dermal substitute. I. Comparison to the gingival autograft: A randomized controlled pilot study. Journal of Periodontology, 76, 867-880. http://dx.doi.org/10.1902/jop.2005.76.6.867</mixed-citation></ref><ref id="scirp.38828-ref6"><label>6</label><mixed-citation publication-type="other" xlink:type="simple">Gao, Z.R., Hao, Z.Q., Li, Y., Im, M.J. and Spence, R.J. (1992) Porcine dermal collagen as a wound dressing for skin donor sites and deep partial skin thickness burns. Burns, 18, 492-496. http://dx.doi.org/10.1016/0305-4179(92)90183-U</mixed-citation></ref><ref id="scirp.38828-ref7"><label>7</label><mixed-citation publication-type="other" xlink:type="simple">Charriere, G., Bejot, M., Schnitzler, L., Ville, G. and Hartmann, D.J. (1989) Reactions to a bovine collagen implant. Clinical and immunologic study in 705 patients. Journal of the American Academy of Dermatology, 21, 1203-1208.http://dx.doi.org/10.1016/S0190-9622(89)70330-3</mixed-citation></ref><ref id="scirp.38828-ref8"><label>8</label><mixed-citation publication-type="other" xlink:type="simple">Rezwan, K., Chen, Q.Z., Blaker, J.J. and Boccaccini, A.R. (2006) Biodegradable and bioactive porous polymer/inorganic composite scaffolds for bone tissue engineering. Biomaterials, 27, 3413-3431. http://dx.doi.org/10.1016/j.biomaterials.2006.01.039</mixed-citation></ref><ref id="scirp.38828-ref9"><label>9</label><mixed-citation publication-type="other" xlink:type="simple">Yang, F., Murugan, R., Ramakrishna, S., Wang, X., Ma, Y.X. and Wang, S. (2004) Fabrication of nano-structured porous PLLA scaffold intended for nerve tissue engineering. Biomaterials, 25, 1891-1900.  http://dx.doi.org/10.1016/j.biomaterials.2003.08.062</mixed-citation></ref><ref id="scirp.38828-ref10"><label>10</label><mixed-citation publication-type="other" xlink:type="simple">Hu, J., Sun, X., Ma, H., Xie, C., Chen, Y.E. and Ma, P.X. (2010) Porous nanofibrous PLLA scaffolds for vascular tissue engineering. Biomaterials, 31, 7971-7977. http://dx.doi.org/10.1016/j.biomaterials.2010.07.028</mixed-citation></ref><ref id="scirp.38828-ref11"><label>11</label><mixed-citation publication-type="other" xlink:type="simple">Leenslag, J.W., Pennings, A.J., Bos, R.R., Rozema, F.R. and Boering, G. (1987) Resorbable materials of poly (L-lactide). VI. Plates and screws for internal fracture fixation. Biomaterials, 8, 70-73.  http://dx.doi.org/10.1016/0142-9612(87)90034-2</mixed-citation></ref><ref id="scirp.38828-ref12"><label>12</label><mixed-citation publication-type="other" xlink:type="simple">Hasegawa, S., Neo, M., Tamura, J., Fujibayashi, S., Takemoto, M., Shikinami, Y., Okazaki, K. and Nakamura, T. (2007) In vivo evaluation of a porous hydroxyapatite/poly-DLlactide composite for bone tissue engineering. Journal of Biomedical Materials Research Part A, 81, 930-938. http://dx.doi.org/10.1002/jbm.a.31109</mixed-citation></ref><ref id="scirp.38828-ref13"><label>13</label><mixed-citation publication-type="other" xlink:type="simple">Deplaine, H., Lebourg, M., Ripalda, P., Vidaurre, A., Sanz-Ramos, P., Mora, G., Prósper, F., Ochoa, I., Doblaré, M., Gómez, R.J.L., Izal-Azcárate, I. and Gallego, F.G. (2013) Biomimetic hydroxyapatite coating on pore walls improves osteointegration of poly(L-lactic acid) scaffolds. Journal of Biomedical Materials Research Part B, 101, 173-186. http://dx.doi.org/10.1002/jbm.b.32831</mixed-citation></ref><ref id="scirp.38828-ref14"><label>14</label><mixed-citation publication-type="other" xlink:type="simple">Walsh, W.R., Evans, R.O., Iliopoulos, J., Cornwall, G.B. and Thomas, K.A. (2006) Evaluation of a bioresorbable polylactide sheet for the reduction of pelvic soft tissue attachments in a porcine animal model. Journal of Biomedical Materials Research Part B, 79, 166-175. http://dx.doi.org/10.1002/jbm.b.30527</mixed-citation></ref><ref id="scirp.38828-ref15"><label>15</label><mixed-citation publication-type="other" xlink:type="simple">Shikinami, Y., Okazaki, K., Saito, M., Okuno, M., Hasegawa, S., Tamura, J., Fujibayashi, S. and Nakamura, T. (2006) Bioactive and bioresorbable cellular cubic-composite scaffolds for use in bone reconstruction. Journal of the Royal Society Interface, 3, 805-821. http://dx.doi.org/10.1098/rsif.2006.0144</mixed-citation></ref><ref id="scirp.38828-ref16"><label>16</label><mixed-citation publication-type="other" xlink:type="simple">Simon, Jr., C.G., Eidelman, N., Kennedy, S.B., Sehgal, A., Khatri, C.A. and Washburn, N.R. (2005) Combinatorial screening of cell proliferation on poly(L-lactic acid)/poly (D,L-lactic acid) blends. Biomaterials, 26, 6906-6915. http://dx.doi.org/10.1016/j.biomaterials.2005.04.050</mixed-citation></ref><ref id="scirp.38828-ref17"><label>17</label><mixed-citation publication-type="other" xlink:type="simple">Rozema, F.R., Bos, R.R., Pennings, A.J. and Jansen, H.W. (1990) Poly(L-lactide) implants in repair of defects of the orbital floor: An animal study. Journal of Oral and Maxillofacial Surgery, 48, 1305-1309; Discussion 1310. http://dx.doi.org/10.1016/0278-2391(90)90487-M</mixed-citation></ref></ref-list></back></article>