Long-Term Survival and Regeneration Following Transplantation of 3D-Printed Biodegradable PCL Tracheal Grafts in Large-Scale Porcine Models

Abstract

Polycaprolactone (PCL) implants in large animals show great promise for tracheal transplantation. However, the longest survival time achieved to date is only about three weeks. To meet clinical application standards, it is essential to extend the survival time and ensure the complete integration and functionality of the implant. Our study investigates the use of three-dimensional (3D)-printed, biodegradable, PCL-based tracheal grafts for large-scale porcine tracheal transplantation, assessing the feasibility and early structural integrity crucial for long-term survival experiments. A biodegradable PCL tracheal graft was fabricated using a BIOX bioprinter and transplanted into large-scale porcine models. The grafts, measuring 20 × 20 × 1.5 mm, were implanted following a 2 cm circumferential resection of the porcine trachea. The experiment design was traditionally implanted in eight porcines to replace four-ring tracheal segments, only two of which survived more than three months. Data were collected on the graft construction and clinical outcomes. The 3D-printed biosynthetic grafts replicated the native organ with high fidelity. The implantations were successful, without immediate complications. At two weeks, bronchoscopy revealed significant granulation tissue around the anastomosis, which was managed with laser ablation. The presence of neocartilage, neoglands, and partial epithelialization near the anastomosis was verified in the final pathology findings. Our study demonstrates in situ regenerative tissue growth with intact cartilage following transplantation, marked by neotissue formation on the graft’s exterior. The 90-day survival milestone was achieved due to innovative surgical strategies, reinforced with strap muscle attached to the distal trachea. Further improvements in graft design and granulation tissue management are essential to optimize outcomes.

1. Introduction

In the realm of tracheal reconstruction, addressing the intricate challenges posed by extensive tracheal resection has necessitated the exploration of diverse reconstructive strategies, including the use of autografts, allografts, and prosthetics [1,2,3,4]. Despite these efforts, achieving long-term success and functional regeneration of the trachea remains elusive [5]. This challenge has spurred interest in tissue engineering as a promising avenue for developing sustainable, tissue-engineered tracheas that meet the needs of patients undergoing long-segment tracheal resections [6]. The advent of 3D printing technology has revolutionized the field, offering unprecedented precision in creating biodegradable polycaprolactone (PCL) scaffolds tailored to individual anatomical specifications [7,8,9]. PCL, known for its mechanical strength and biocompatibility, stands out among biodegradable polymers for its suitability in 3D printing applications [10,11]. This eliminates the need for a time-consuming decellularization process [12,13] and harmful solvents [14], allowing for the fabrication of scaffolds that closely replicate the intricate architecture of the natural trachea. Such advances have not only paved the way for structural repairs but also promise functional restoration over prolonged periods, marking a significant leap forward from traditional methods that provided only temporary solutions [6,15].

The utilization of large animal models plays a crucial role in this research, bridging the gap between small-scale experiments and human clinical applications [16]. While small-animal models have contributed valuable insights into the design and testing of bioengineered tracheas and grafts [17,18,19,20], their limitations become apparent when assessing graft functionality in vivo, primarily due to the inability of small airways to accommodate bronchoscopic instrument [21]. Thus, large-scale animal models, with airway sizes more comparable to humans, are essential for a realistic evaluation of tracheal transplantation and long-term graft viability. The PCL implants in large animals show great promise for tracheal transplantation. However, the longest survival time achieved to date is only about three weeks. To meet clinical application standards, it is essential to extend the survival time and ensure the complete integration and functionality of the implant. Our current research extends beyond the scope of previous studies by providing a comprehensive analysis of the entire neotissue layer in situ, including cartilage, muscle, adipose, and glandular tissues derived from mesenchymal cells [22,23]. We have documented the chronological development of chondrogenesis, glandogenesis, myogenesis, and adipogenesis, elucidating the intricate processes of cellular development within the regenerative tissue. This lucid examination highlights the crucial role of airway remodeling and the formation of new tissue.

The process toward achieving a successful long segment of circumferential tracheal replacement has encountered numerous challenges, from the technical difficulties of integrating synthetic grafts to the ethical and logistical issues associated with donor-dependent methods [24,25,26,27,28]. The transition toward biosynthetic scaffolds represents a critical advancement, offering a viable platform for in vivo tissue engineering that circumvents the limitations of previous approaches. This strategy not only provides immediate structural support but also promotes the emergence of new tissue, laying the groundwork for sustained graft survival and integration into the body’s ecosystem [29].

By harnessing the capabilities of 3D printing to develop PCL tracheal grafts tailored for large-scale porcine models, our research aims to surmount the longstanding obstacles faced in tracheal reconstruction. This initiative seeks to create a versatile platform for investigating the potential of customizable tracheal scaffolds, thereby enhancing not only the survival prospects but also the regeneration capabilities of tracheal tissues.

2. Materials and Methods

2.1. Design and Preparation of PCL Tracheal Grafts

The design and preparation process for PCL tracheal grafts (Figure S1) involved 3D printing using a CELLINK BIOX™ bioprinter (Figure S2A). The specified graft dimensions incorporated six strategically placed distribution holes, as outlined by G-code parameters. The fabrication commenced with ester-terminated PCL (CAS-n 24980-41-4, CELLINK, TP-60505) pellets, a biodegradable polyester, heated to a molten state, then extruded in layers to form the graft, requiring 3–4 h. To summarize, we used Cellink HeartWare 2.4 software to edit the G-code printing program. We produced the best graft by printing with both sterilized support material “CELLINK START” (CELLINK, IK-190000) and PCL in different cartridges. This method comprised alternating PCL and washable support materials for the inner and outer layers, with PCL serving as the filler material. The maximum flexibility of the implant was attained with 20 mm in length, 20 mm in diameter, a thickness of 1.5 mm and a 25% infill. This method created implants with fine and regular pores, resulting in optimal printing conditions. The final PCL grafts featured four deliberately placed perforations to promote uniform cell ingrowth and integration with the native trachea after implantation (Figure S2B). These grafts were comparable in thickness to the trachea of a young pig, which is circular in contrast to the C-shape typical of a human trachea. The properties of the grafts were validated against those of a native porcine trachea using a JSV-H1000 system. After production, the grafts underwent refinement and sterilization with ethanol and UV light according to Kim et al., 2019 [30], preparing them for transplantation in large-scale animal models.

2.2. Methods Design for In Vivo Experiments

Eight LY female porcine were obtained from Pinguan Modern Livestock Co., Ltd., (Taichung, Taiwan). These animals were approximately three months old and weighed between 30 and 62.5 kg (Figure 1). The Taichung Veterans General Hospital Institutional Experimentation Committee provided ethical approval for the experimental procedures (Animal Welfare Protocol Number La-1111859, approved on 3 November 2022). Our study team had extensive experience in conducting large-scale animal trials involving tracheal transplantation, with over 30 tests utilizing various materials for 3D-printed grafts. In this study, the implants were made from aseptic 3D-printed grafts that were well-preserved. There was a surgical fixation method: porcine were lastly handled with Traction sutures of proximal and distal ends of trachea, tied together to alleviate tension at the anastomosis sites bilaterally (Figure S3A–G), and subsequently reinforced with additional reinforcement in which dual-end needle 3-O prolene sutures were used to penetrate the strap muscle individually and tied over the anterior lateral surface of the muscle for tension relief of graft force for negative pressure of the thorax (Figures S3H and S4). The experimental procedure entailed resecting a 2 cm circumferential segment of the trachea, followed by an end-to-end anastomosis between the proximal and distal tracheal portions with non-absorbable 3-O prolene sutures. This approach closely resembled human tracheal surgery (Supplementary Video S1. Procedures of surgical intervention of PCL tracheal graft). Animal feeding and care techniques adhered to both national and international standards.

2.3. Anesthesia, Surgical Intervention and Postoperative Care

Each porcine was anesthetized with Zoletil 50 (8 mg/kg, IM, Virbac, Carros, France) and intubated using a 7.0 mm endotracheal tube. Anesthesia was maintained with 4% isoflurane. The animals were placed in a supine position, and their necks were shaved and sterilized with povidone iodine followed by 75% alcohol. A disposable sterile towel was used for draping. A cervical midline incision was made, and the strap muscles were separated to expose the upper trachea (Figure S3A). A 2 cm circumferential segment of the trachea was excised and replaced with the 3D-printed PCL tracheal graft (Figure S3B–F). Cross-table ventilation was used during the creation of the proximal end anastomosis, which was replicated at the distal end. The endotracheal tube was repositioned through the graft into the distal trachea after completing the proximal and posterior distal end anastomoses with a continuous running 3-O prolene suture. The anterior half of the distal anastomosis was completed with interrupted 4-O prolene sutures placed above the tube. Traction sutures of proximal and distal ends of the trachea were tied to alleviate tension at the anastomosis sites bilaterally (Figure S3G). After confirming an airtight seal, the strap muscles were closed, a silicone Penrose drain was inserted, and the wound was sutured in layers. Postoperatively, the animals were extubated in the operating room and recovered without complications within 12 h, resuming normal activities and diet. Postoperative care included pain relief with diclofenac potassium (25 mg), antibiotic treatment with ampicillin (500 mg), and a mucolytic agent (bromhexine hydrochloride, 2 mg/mL), all administered with food under veterinary supervision.

2.4. Scheduled Postoperative Bronchoscopic Evaluation and Laser Ablation for Granulation Tissue

Post-transplant, the tracheal lumen was regularly evaluated using intraluminal telescopic visualization (bronchoscopy) with a 4.9 mm 0° endoscope (Olympus BF-260/CV-260/CLV-260, YUAN YU INDUSTRY Co., Ltd., Taipei, Taiwan), approximately on a weekly basis, to monitor graft integration and ensure airway patency (Figure S5). Sedation was maintained during these procedures. Stenosis was quantitatively assessed by comparing the diameters of stenosed and non-stenosed tracheal segments. When significant granulation tissue was observed at the anastomosis site, Argon-plasma Coagulation (FiAPC probe 1500 A/VIO200D, Soma Technology, Inc., Bloomfield, CT, USA) was utilized to ablate the tissue and maintain lumen patency. ERA Bioteq ENTERPRISE Co., Ltd. (Taipei, Taiwan) supplied the equipment for this process.

2.5. Tracheal Tissue Harvested and Gross Examination

Biodegradable PCL tracheal grafts, produced using a BIOX bioprinter, were implanted into large-scale porcine models with the goal of achieving a three-month long-term survival. Upon the study’s completion, the tracheal grafts and associated cylindrical neotissues were harvested. During the autopsies, these in situ regenerated tissues underwent gross examination, focusing on infection, necrosis, and the severity of tracheal stenosis at both proximal and distal anastomosis sites. The samples were then fixed in 10% formalin and embedded in paraffin for subsequent analysis (Figure S6).

2.6. Regenerated Tubular Tissue outside Graft by Histology Analysis

Chondrocyte markers, including Sox9, type II collagen, and aggrecan, were effectively stained. Proliferating cells were detected using the proliferating cell nuclear antigen (PCNA) assay. CD31 and αSMA, markers for blood vessels within the neocartilage, were employed to assess angiogenesis using the UltraVision LP Detection System HRP Polymer & DAB Plus Chromogen (Thermo, TL-060-HD, Thermo Fisher Scientific Inc., Waltham, MA USA). Photomicrographs were captured using NDP.view 2.6.8 software. The total pixel areas within the sections stained for Sox9, aggrecan, and PCNA were computed, taking into account positively stained chondrocytes in the immunohistochemistry (IHC) staining, with the assistance of Image J 2 software.

Tissue specimens were fixed in 10% formalin and then embedded in paraffin. Various histological stains were utilized to assess the regenerated tissues, including hematoxylin and eosin (H&E), alcian blue (ScyTek, ANC250, ScyTek, UT, USA), and safranin O/fast green (Cat. #8348a/Cat. #8348b). Images of the stained sections were captured using NDP.view 2.6.8 software. The number of chondrocytes, as indicated by the H&E-stained sections, was quantified using Image J software. The neocartilage matrix content, specifically glycosaminoglycans (GAGs), was determined from the alcian blue and safranin O/fast green-stained sections. The total pixel area within the cartilage sections stained by H&E was calculated, taking into account the distinct lacunar morphology. The data from the neocartilage and native tracheal cartilage of the test subjects were gathered and compared to that of a mature six-month-old porcine with a stable tracheal cartilage (Stage IV).

2.7. Statistical Analyses

Images from each slide underwent random review and analysis by an individual blinded to the research questions. The data are presented as mean ± SEM and were subjected to statistical comparison using the Kruskal–Wallis test or ANOVA, as appropriate. The number of chondrocytes across different tissue samples was compared utilizing the Dunn–Bonferroni post hoc test within the Kruskal–Wallis framework or the Bonferroni correction within ANOVA. Statistical significance was established at a p-value of less than 0.05.

3. Results

The implanted PCL tracheal grafts with dimensions of 20 mm in length, 20 mm in diameter, a thickness of 1.5 mm, and 25% infill (Figure S2B).

Table 1. Demographics of PCL tracheal grafts transplanting into porcine model.

Item	Animals
	Porcine 1	Porcine 2
Weight, kg	60	62.5
Number of bronchoscopy	9	10
Number of laser ablation for granulation tissue	8	7
Complication	Granulation Infection (soft tissue) Calcification	Granulation
Weight gain, kg	100	101
Survival day	92	92
Cause of death (no. of animal)	Sacrifice	Sacrifice

and Figure 1 present a summary of the outcomes from transplanting the PCL tracheal grafts into a porcine model. The study utilized two methods of surgical procedures across eight female porcines that varied significantly in weight. Six exclusions were due to complications such as infection, necrosis, and dehiscence, and survived for less than three months due to respiratory failure. A notable improvement with two inclusions, recorded weight gain, and all animals surviving beyond three months, led to their elective sacrifice for the study.

3.1. Gross Specimen of Tissue Regeneration Following Long-Term Implantation into Large-Scale Porcines

To gain insights into the tracheal regeneration process, we collected and analyzed regenerated tissues 92 days after graft implantation into the trachea (Figure S6). The whole-mount tissue was divided into three sections, ranging from proximal to distal, with each region further subdivided into left and right parts (Figure 1 and Figure 2). Due to the inability to precisely localize the specimens without reference to the esophagus, the exact position of the regenerated tissue could not be determined. However, this division facilitated subsequent analysis. The figure is a composite of photographs and histology slides depicting neotissue growth at various regions (proximal, middle, and distal) around a tracheal graft in two different porcine subjects over a period of 90 days post-implantation. For porcine 1, which had a soft tissue infection: The images showed the gross morphology of the intact cylindrical neotissue at the proximal, middle, and distal regions, respectively, with the PCL tracheal rings visible inside the neotissue (Figure 2A,C,E). The corresponding histology slides, stained with Hematoxylin & Eosin (H&E), show red circles indicating areas of heterotopic ossification (HO) (Figure 2B,D,F). For Porcine 2, which did not have an infection, the images displayed the gross morphology of the neotissue, with only a half-ring of neotissue growth in image G compared to the intact rings in images I and K (Figure 2G,I,K). The histology slides for Pig2, again with red circles, highlight areas of HO (Figure 2H,J,L).

3.2. Tracheal Tissue Regeneration Followed by Tracheal Graft Implantation

This is a set of histological sections showing a comparison of regenerated tracheal tissues in a large-scale porcine model over 90 days, focusing on the proximal area of neotissue. It comprises two main images (Figure 3), A and E, each with a scale bar indicating 10 mm, which provide a comprehensive view of the regenerated tracheal tissues. Accompanying each main image are close-up views of specific areas of interest, marked by colored squares that correspond to insets B–D for image A and F–H for image E. Figure 3A shows the overall view of the regenerated tracheal tissue featuring integrated cartilage, abundant submucosal glands, and a smooth epithelium. Inset B (marked with a red square on image A) displays the intact neocartilage with signs of chondrogenesis at the tip. Inset C (marked with a green square on image A) highlights the abundant newly formed submucosal gland clusters. Inset D (marked with a yellow square on image A) presents a smoothly regenerated epithelium. Figure 3E provides an overall view of another sample of regenerated tracheal tissue, but with heterotopic ossification, irregular submucosal glands, and epithelium. Inset F (marked with a red square on image E) is a representative central area showing the lamellar bone trabeculae with intervening fibrous tissue that resembles fibrotic marrow. Inset G (marked with a green square on image E) illustrates irregular clusters of submucosal glands. Inset H (marked with a yellow square on image E) shows the epithelium in the tissue sample.

The series presents histological sections comparing the distribution and morphology of submucosal glands in the trachea of three-month-old and six-month-old porcine subjects, as well as in regenerated tracheal tissue after implantation into a large-scale porcine model for over 90 days (Figure S7). The submucosal glands from the native trachea of a three-month-old porcine appear to have a homogenous distribution throughout the tissue, characterized by uniform spacing and size (Figure S7A,B). The submucosal glands of a six-month-old porcine’s native trachea show a heterogeneous distribution, with variable spacing and size, indicating a less uniform pattern compared to the three-month-old porcine trachea (Figure S7C,D). The regenerated tracheal tissue, implanted in the porcine for over 90 days, features submucosal glands that are more abundant and larger in size than those in the native trachea (Figure S7E,F).

3.3. The Impact of Bacterial Infection-Induced Inflammation after Tracheal Graft Transplantation and Heterotopic Ossification (HO) Observed 92 Days Post-Implantation

This analysis presents various histological features of tracheal neotissue in a large-scale porcine model 90 days after implantation: It showcases the overall histological structure, with a focus on areas of HO (Figure 4A). It reveals the presence of bacterial clumps, suggesting an area of microbial colonization (Figure 4B). It indicates congestion in the submucosal area, likely due to increased vascularity or inflammation (Figure 4C). It highlights a polyp formation within the neotissue (Figure 4D). It details the tissue morphology surrounding the HO (Figure 4E). Each colored square (yellow, red, blue, green) corresponds to magnified views at 100× within panels B–E, offering a closer look at the specific histological features identified in the neotissue.

3.4. Characteristics of Vascular Canals (VCs) in the Evolution of Chondrogenesis: Derived from Perichondrium as Chondro-Modulators in the Maturation of Cartilage to Prune Excessive Chondrocytes

This section illustrates the microscopic features of neocartilage 19 days post-graft implantation, highlighting the perichondrial papillae (PP), pre-resorptive layers (PRL), and vascular canals (VCs). The focus is on PP and PRL, utilizing H&E, safranin O/fast green staining, and immunohistochemistry (IHC) with αSMA antibodies, where “P” indicates perichondrium, and black arrows point to PRL (Figure 5A–C). It details the VCs, demonstrated through H&E, safranin O/fast green, alcian blue stains, and IHC with antibodies for type II collagen, Sox9, aggrecan, PCNA, αSMA, and CD31 (Figure 5D–L). The protein expression is shown in brown, while safranin O/fast green appears red, and alcian blue in blue. All images are magnified at 200×, providing a detailed view of the tissue’s staining characteristics and protein expression related to cartilage development and vascularization.

3.5. Concise Four-Stage Developmental Model to Elucidate the Intricate Process of Tracheal Cartilage Regeneration Based on the Occurrence of Key Chondrogenesis Features

This figure provides a comprehensive overview of the stages of chondrogenesis in graft neotissue, characterized by histological changes and specific protein expressions: It shows the progression of cartilage through five distinct stages, revealing changes in cell morphology and structure by H&E stain (Figure 6A–D). It indicates the presence of glycosaminoglycans (GAGs) in the cartilage matrix, with blue coloring signifying their distribution and density by alcian blue stain (Figure 6E–H). It displays the GAGs in red, with the vascular canal modulator structure identified by black arrows in safranin O/fast green stain (Figure 6I–L). It quantifies the number of chondrocytes and the ratios of protein expressions (Sox9, aggrecan, and PCNA) across different chondrogenesis stages, highlighting the dynamic nature of cartilage development within the neotissue. All images are magnified to show fine details, and the data presented include mean values with standard deviations, noting statistically significant differences where p < 0.05 (Figure 6M–P).

3.6. Types of Cartilage Evolution during Chondrogenesis

The figure presents a series of histological sections that illustrate the stages of cartilage development during chondrogenesis, as indicated by H&E and type II collagen stains. It shows early-stage chondrogenesis with tapering spear-like neocartilage exhibiting elongation within the tracheal structure, suggesting initial cartilage formation (Figure S8A,B). This reflects the intermediary stage where separate cartilage templates are in the process of merging (Figure S8C,D). It then demonstrates a more advanced stage where the cartilage templates have fused, with type II collagen expression indicated by the brown coloration (Figure S8E,F). All images are magnified at 100× to detail the progressive structural changes and protein expression that occur as neocartilage matures.

4. Discussion

In our journey to advance tracheal transplantation techniques, nearly 40 extensive animal experiments have significantly contributed to our understanding of tracheal tissue regeneration. We harnessed 3D printing technologies to evolve from Crystal and Silicone to the biodegradable polycaprolactone (PCL), which proved instrumental in enhancing tissue ingrowth due to its design featuring simulated cartilaginous rings (Figure S2) [31]. This design not only ensured the necessary mechanical strength and flexibility but also paved the way for effective tissue integration. Despite initial experiments having had short survival spans, these trials were crucial in revealing early tissue regeneration dynamics and morphological transformations, casting light on aspects akin to embryonic organ regeneration. This underscores the benefits of leveraging large animal models to obtain comprehensive observations—a feat challenging to achieve with smaller animal models due to their inherent limitations [17,18,19,20].

A pivotal finding from our recent endeavors is the survival of two large animals beyond 90 days, illustrating complete regeneration of cartilage rings, mucous membranes, and additional phenomena such as polyp formation and ossification, typically associated with infections (Figure 1, Figure 2 and Figure 3). This significant results underscores the efficacy of biodegradable PCL grafts, fabricated through bioprinting for large animal applications, as potential viable clinical solutions [16]. Notably, the use of biodegradable PCL without tracheal stents in large animals represents a groundbreaking achievement.

Despite the biodegradability and tissue compatibility of PCL tracheal implants, a duration of approximately two to three years is required for their complete degradation to allow full tracheal tissue regeneration at the reconstruction site [6,15]. This prolonged process exposes the implant to environmental factors, which communicates with the environment at the upper tracheal end, is exposed to varying pH levels, humidity, impurities, and potential lung infections, potentially leading to complications such as infection, inflammation, and necrosis, which could compromise the integrity of the implant, resulting in tracheal collapse. To mitigate these risks, we adopted an innovative approach by utilizing reinforcement suture over distal trachea and strap muscle to release tension at the anastomosis site, thereby enhancing stability and resistance against the thoracic cavity’s negative pressure (Figure S4). Further, to address the issue of excessive granulation tissue, we applied laser therapy to ensure the airway remained unobstructed, enabling the animals’ survival beyond 90 days (Figure S5). This combination of innovative techniques has been crucial in our success, suggesting the future potential of enhancing tracheal implants with coatings similar to drug-eluting stents for reduced granulation tissue formation and improved postoperative outcomes [32,33]. Postoperatively, the administration of antibiotics via muscle injections could actively prevent infections and their severity, potentially extending the duration of survival even further.

Our observations upon implantation revealed two distinct cartilage tissue growth patterns: (1) the spear-like extension of chondroblasts in some regions, indicating initial cartilage formation; and (2) the fusion of cartilage templates in others, signifying advanced stages of cartilage development. This variability highlights the complex nature of cartilage regeneration within the neotissue, influenced by factors such as nutrient supply and waste removal facilitated by structures derived from the perichondrium. The roles of VC, PP, and PRL derived from the perichondrium are essential in supplying nutrients, metabolizing chondrocyte products, and eliminating metabolites through the submucosa and epithelium areas (as indicated by alcian blue staining and CD31 marker) [31]. Ninety-two days post-implantation, our examination of regenerated tissues offered profound insights, especially noting extensive ossification near the anastomotic ends. This suggests a link between tissue ossification and infection-induced inflammatory responses, offering valuable perspectives on the regeneration process.

Addressing postoperative care challenges, particularly in preventing complications like stenosis due to intraluminal granulation tissue, remains a priority. Our research underscores the promising potential of 3D-printed PCL scaffolds in tracheal tissue regeneration, showcasing improved survival and integration in large animal models. The surgical techniques and postoperative care strategies developed through this research, including the strategic use of strap muscle for graft stabilization and laser ablation for granulation tissue management, represent significant advancements in overcoming the hurdles associated with tracheal transplantation. Moreover, the prospective application of mTOR inhibitors on the scaffold surfaces opens new avenues for enhancing the success and longevity of tracheal implants, paving the way for novel approaches to tracheal repair and regeneration in clinical settings.

The limitations of this study include: (a) The sample size of pigs utilized in the research was still small, the need for a greater number of successes in future endeavors; (b) The postoperative care and management of large animal present significant challenges, particularly when administering anesthesia to individuals exceeding 100 kg. It is imperative to address and surmount these challenges. One potential solution could involve the utilization of mini-pigs; (c) In an effort to increase survival durations and diminish the likelihood of postoperative infections, it is essential to improve the animals’ living conditions. This entails the enhancement of sanitary practices and the regulation of environmental conditions, such as temperature and humidity, to support the well-being of the animals.

5. Conclusions

Our research substantiates the significant potential of 3D-printed PCL scaffolds in tracheal tissue regeneration, emphasizing the importance of innovative surgical techniques and postoperative care strategies in overcoming the challenges of tracheal transplantation. Our results have demonstrated that: (1) The improved surgical technique has successfully overcome the challenge of thoracic negative pressure, ensuring the stability of the implant and trachea; (2) After implantation, overcoming the dilemma of technique of general anesthesia, laser ablation technology is applied to manage granulation tissue, maintaining airway patency for long-term survival; (3) This stability has allowed the animals to survive for more than 90 days, proving the technique’s effectiveness. However, achieving complete tissue regeneration requires the full degradation of PCL, which takes two to three years. Therefore, our further experiment is to employ Lanyu mini-pigs for tracheal transplantation, effectively controlling weight gain to achieve the goal of successful and complete tissue regeneration.