The Importance Of A 3d Supportive Structure

There are two methods of cloning organs. One is by injecting a growth factor into the wound site, causing the patient's own cells to migrate and regenerate. The other method is to harvest donor cells and pack them into a three-dimensional polymer scaffold, which is molded into the desired shape. These cells replicate and then can be transplanted into a recipient. The polymer breaks down as the cells form into the shape desired. These organs are called neo-organs. While this may sound like something straight out of a science fiction film, like Dolly, neo-organs are already a reality. All over the United States, grown skin is being used to treat everything from burn victims to skin cancer patients. Also, machines containing cloned liver cells are being used to filter blood until a transplant can be found. Cartilage, because of it's relatively simple structure, seems likely to be the next step. Larger organs will take

The attending of osteo-chondral complex tissue was similarly studied in vivo utilize a complex framework formed HA/collagen primer FGF2. FGF2 was infused inside the HA/collagen platform and after that enclosed into the osteo-chondral perfection in a rabbit femoral knee. In the times of implantation through 4 to 25 weeks, FGF2-treated platform amass showed incredibly improved bone recovery and attractive ligament recovery, proposing that the HA/collagen composite is a decent possibility for conveying FGF2 amid the recovery of osteochondral deformity.

Traumatic acute events leading to tendon losses as well as ruptures related to degenerative tendinopathy require a replacement of the damaged tissue. Yet in these cases, the healing process does not efficiently restore the native tendon structure and function, despite the surgical intervention with a high rate of re-tear (Sharma and Maffulli, 2006; Andarawis-Puri et al. 2015). Nowadays, tendon autografts are the common choice to reconstruct the tendon integrity, despite their limited supply, high donor-site morbidity, and poor functional outcomes ( Gazdag et al., 1995; Lovati et al., 2016). To overcome these limitations, tissue engineering widely investigated the generation of cell seeded scaffolds to promote regeneration and implant-tissue

. Thus they must be treated in their acute phase to inhance reepithelialization, reduce inflammation and limit further degeneration of the epithelium and

"autologous tissue, indistinguishable in form and function from its native counterpart. The cardiovascular system has been identified as a target for tissue engineering since the inception of the field and the potential of tissue engineering to benefit patients with cardiovascular disease is even more relevant in the present day. Currently, cardiovascular disease accounts for 20% of global mortality and is the most common cause of death in adults within the United States (47). While significant strides have been made in medical management, surgical intervention requiring the use of prosthetic implants continues to be critical in many adult

(What normal daily roles does fgf play in our bodies daily?) Tissue designing, with critical research contributions in the course of the most recent decades has risen as a potential device to recover harmed and

Heart disease is the leading cause of death in the world. Heart tissue engineering holds a great promise for future heart disease therapy by building personalized heart tissues. Generating a bioengineered heart requires engineering of cardiac architecture and appropriate cellular constituents. We decellularized rat hearts by coronary perfusion with detergents, preserved the underlying extracellular matrix (collagen, glycosaminoglycan and elastin content and fibronectin, collagen type II and laminin proteins) and produced decellularized, perusable vascular architecture and competent decellularized valves. Regarding unique effect of bFGF in proliferation and differentiation of induced pluripotent stem cells-derived cardiovascular progenitor cells

Elastic tissues such as the skin must have a strong and resilient structural framework. This framework is called the extracellular matrix, or connective tissue. The orientation

Currently, alternatives, such as mechanical devices and artificial prostheses, don’t repair tissue or organ functions because they are not intended for integrating host tissues, and if these alternatives are used for long-term implantation, the recipient could suffer from an inflammatory response (Chapekar). For illnesses such as end-stage liver disease, the only successful treatment is through transplant, and the odds of receiving a new liver is improbable (Kaihara and Vacanti). Another treatment must be discovered. In 1988, a NSF sponsored meeting defined a new treatment idea called tissue-engineering: the “application of the principles and methods of engineering

(Chan & Leong, 2008). Biocompatibility is also an important factor. The material should be biologically compatible with the host tissue so it does not cause an immune or inflammatory response. (Pluta, Malina, & Sobczak-Kupiec, 2012). While the cells grow on the scaffold they generate a matrix around themselves, the scaffold provides structure and is eventually absorbed by the body; leaving the newly formed tissue to manage mechanical support. (Pluta, Malina, & Sobczak-Kupiec, 2012). The scaffold needs to be absorbed by the surrounding tissue at a rate compatible with the rate of tissue growth, so the new tissue can function independently and avoid the need for surgical removal. Lastly, to ensure functionality, the mechanical properties of the Scaffold should compatible with the tissue type. (Pluta, Malina, & Sobczak-Kupiec, 2012; Chan & Leong, 2008).

Development of scaffolds plays a vital role in bone tissue engineering in order to repair, regenerate tissues by mimicking of natural bone extracellular matrixes. Considering that bone is a composite of minerals and proteins, it is preferred to develop a composite that mimics natural bone. The ideal nanocomposite materials should have biocompatibility, suitable mechanical and antimicrobial properties, nontoxicity and surface functionality to favor cell proliferation.1,2

On the forefront of tissue scaffold fabrication is 3D printing. 3D printers have a multitude of advantages over traditional scaffold fabrication methods. High print precision allows fibers to be deposited into 3D structures with finely tunable dimensions, 3D printers also have the ability to incorporate multiple materials into the same structure through multiple extrusion heads. Jakus et al. used a 3D extrusion based printer to create a graphene and polylactide-co-glycolide scaffold and showed it could create a 3D graphene structure (3DG) with features as small as 100 um and as large as 10cm offering a large range of applications. They also showed that 3DG supports human mesenchymal stem cell (hMSC) adhesion, viability, proliferation, and neurogenic differentiation with significant upregulation of glial and neuronal genes [9]. The ease in fabrication and the ability to precisely modify structure with 3D printers allows for opportunities in a wide range of tissue engineering applications.

Gel hydrogels can be considered as promising materials to be used as scaffold in tissue engineering since they present a load-bearing capacity and suitable mechanical properties.6 Almost all the measurements on the mechanical properties of hydrogel materials have used true stress-true strain or engineering stress-engineering strain definitions on the grounds of hydrogel incompressibility.26 However, there is no agreement as to which stress-strain definition should be adopted to determine the mechanical behavior of hydrogel materials in a compressive testing machine. Hydrogels are known to exhibit elastic behavior,27 hence, the elastic modulus, maximum stress and strain of Gel hydrogels are investigated. The stress-strain definition may substantially affect the measured mechanical properties, including elastic modulus, maximum stress and strain.

As ECM plays a key role in guiding specific cellular behaviour and function, the development of synthetic materials that can resemble the organization and functional complexity of the cell-cell and cell-matrix interactions observed in vivo is important. ECM-like matrix systems could provide an appropriate niche and biological cues for accelerating the regeneration of tissues and organs.1 The cells and their respective surrounding ECM are needed in an engineered tissue, as their interactions are reciprocal.2 The cells within native tissue continuously remodel the ECM, induce microenvironment changes while environment regulate gene expression, and determine cell phenotype.2,3 Therefore, the challenge in designing ECM biomaterials is to mimic

Thousands of people around the world suffer from injuries everyday which requires removal or reinforcements of the damaged tissues through surgical procedures. Tissue engineering, especially scaffolds have a major role to play in such situations. Scaffolds, a porous cross linked structure aims at the regeneration of the damaged tissue by supporting the cells mechanically while not altering the normal functioning of the cell and the individual as whole. Scaffolds are generally made of synthetic biocompatible polymers. But such scaffolds are generally expensive and may take longer time to decompose inside our body. So we looked for autologous biomaterials which have the desirable properties and can be used in place of the polymers. The autologous biomaterials will also be cheaper and decompose faster compared to the polymers. In this report, I have mentioned three such autologous biomaterials; albumin, collagen and B.mori silk fibroins, which are easily available and possesses the desired properties to manufacture scaffolds from them. I manufactured scaffolds by the process of electrospinning and tested the porosity and swelling of the scaffolds.