Pericardial processing.
1. Introduction
The pericardium is a biological tissue widely used as a biomaterial for tissue engineering applications, including the construction of a variety of bioprostheses such as vascular grafts, patches for abdominal or vaginal wall reparation and, more frequently, heart valves.
However, despite significant advances, some drawbacks have been found in these bioprostheses such as biological matrix deterioration and tissue degeneration associated with calcifications, even though xenopericardium or glutaraldehyde-treated autologous pericardium were used.
In non-autologous pericardial processing, the pericardium must be decellularized in order to remove cellular antigens and procalcific remnants while preserving extracellular matrix integrity. A large variety of decellularization protocols exist, such as chemical, physical or enzymatic methods. Additional cross-linking processing must be carried out to render the tissue non-antigenic and mechanically strong.
So far, almost all bioprosthetic materials made of pericardium,and used in clinical practice, are glutaraldehyde-treated bovine or porcine xenopericardium. However, long-term reports are raising issues concerning their durability, especially highlightingthe high risk of calcification. Regarding heart valves, calcification currently represents the major drawback leading to potential failure of the bioprosthesis.
The aim of this review is to present current issues, challenges, outcomes and future prospects of pericardial processing, including decellularization and cross-linking steps. Understanding current issues and improving pericardial processing will allow refining bioprosthesis conception and patients’ safety.
2. Characteristics of the pericardium
2.1. Localization and composition
The pericardium is a connective tissue sac surrounding the heart. It is composed by two layers: a deeper layer closely adherent to the heart, the visceral serous pericardium, orepicardium, and an upper layer: the parietal pericardium. The two layers are separated by the pericardial cavity. The parietal pericardium can be excised and easily tested without causing major complications such as contracture or ischemia (Fomovsky et al., 2010).
The pericardium is composed of a simple squamous epithelium and connective tissue. It is a collagen-rich biological tissue containing mostly type I collagen, as well as glycoproteins and glycosaminoglycans (GAGs) in addition to its constitutive cells (Figure 1). Collagenis structured intodifferentlevelsoforganizationranging from fibrils to laminates, fibers and fiber bundles (Allen & Didio, 1984; Lee & Boughner, 1981). This organization determines the mechanical properties of the pericardial tissue (Sacks, 2003; Liao et al., 2005; Wiegner & Bing, 1981; Lee & Boughner, 1985) and provides an anisotropic and non-linear mechanical behaviour (Zioupos & Barbenel, 1994). Interestingly, depending on the location on the pericardium, the thickness and mechanical properties vary (Hiester & Sacks 1998a, 1998b). Thus, the location of the sample that will be harvested should be carefully selected when designing a tissue engineering protocol.
2.2. Sources of pericardium
Currently marketed heart valve bioprostheses are prepared from bovine or porcine pericardium (Vesely, 2005). Other pericardial tissues from different species have been assessed or are currently used in clinical practice such as equine (DeCarbo et al., 2010; Yamamoto et al., 2009; Sato et al.; 2008.), canine (Lee & Boughner ; 1981; Wiegner & Bing, 1981; 1985), or, even more unusually, ostrich (Maestro et al., 2006) or kangaroo pericardium (Neethling et al., 2000; 2002). However, those exogenous grafts raise several issues, and especially the immune response against the bioprosthesis as well as the viral status of the graft.
Human autologous pericardium is thus an interesting option, presenting several advantages over allografts since it is free of donor-derived pathogens and does not induce any immune response (Mirsadraee et al., 2007), is easily available, easily handled and of low cost.Ultimately, these characteristics allow for shorter and less aggressive pericardial processing before implantation of the bioprosthesis. However, because of intermittent reports of its tendency to retract or become aneurysmal, the general opinion has been negative (Edwards et al., 1969, Bahnson et al., 1970). For cusp tissue replacement or valve tissue replacement, stabilization of pericardium is performed with a solution of 0,2% to 0,6% glutaraldehyde in order to prevent secondary shrinkage (Duran et al., 1998; Al-Halees et al., 1998, 2005; Goetz et al., 2002).
3. Processing of pericardium
As allografts have been the main source for pericardial bioprostheses currently in use, significant processing steps have to be performed prior to clinical use. In particular, as xenogeneic cellular antigens induce an immune response or an immune-mediated rejection of the tissue, decellularization protocols are widely used to reduce the host tissue response (Gilbert et al., 2006.). Once decellularized, the free-cell pericardial tissue is composed of extracellular matrix proteins which are generally conserved among species, and thus can be easily used as a scaffold for the host cell attachment, migration and proliferation (Schmidt & Baier, 2000). This scaffold considerably accelerates tissue regeneration. Overall, tissue decellularization aims at reducing tissue antigenicity and host response while preserving the mechanical integrity, biological activity and composition of the ECM (Simon et al., 2006; Gilbert et al., 2006).
3.1. Extracellular matrix decellularization methods
Most decellularization protocolsinclude a combination of various methods, such as physical, enzymatic or chemical treatments (Gilbert et al., 2006; Crapo et al., 2011). Physical methods can either rely on snap freezing (Jackson et al., 1988; Roberts et al., 1991), mechanical force (Freytes et al., 2004) or mechanical agitation (Schenke-Layland et al., 2003), whereas enzymatic protocols employ nucleases, calcium chelating agents or protease digestion (Teebken et al., 2000; Bader et al., 1998; McFetridge et al., 2004; Gamba et al., 2002).
Regarding physical decellularization processes, sonication, based on the use of ultrasounds to disrupt the cell membrane, has been investigated. Such treatment considerably affects the pericardial architecture and full decellularization cannot be achieved. Thus sonication has to be carried out simultaneously with chemical treatments in order to fully decellularize the pericardial tissue and remove cellular debris. However, this combination leads to alterations of the extracellular matrix (ECM) architecture.
For the enzymatic procedure, the main enzyme employed is trypsin, cleaving peptide bonds on the C-side of arginine and lysine and thus allowing separation of the cells from the ECM.
Chemical protocols involve use of alkaline and acid treatments (Freytes et al., 2004), ionic detergents, sodium dodecyl sulfate (SDS), sodium deoxycholate and Triton X-200 (Rieder et al. 2004; Hudson et al., 2004), non-ionic detergents, such as Triton X-100 (Grauss et al., 2003), zwitterionic detergents (Dahl et al., 2003), tri(n-butyl)phosphate (Woods & Gratzer, 2005) as well as hypertonic or hypotonic solutions (Goissis et al., 2000; Woods & Gratzer, 2005; Vyavahareet al., 1997; Dahl et al., 2003). These modalities will either mediate lysis of the cells or solubilization of the cellular components.
Overall, standard decellularization protocols for allografts consist of a multimodal process starting with the lysis of the cell membrane using either ionic solutions or physical treatments. This initial step is then followed by enzymatic treatments to separate any cellular components from the ECM. Subsequently, detergents are used tosolubilize the nuclear and cytoplasmic cellular components. At the end of the procedure, all residual cell debris is removed from the remaining ECM. A washing step must also be carried out following the decellularization protocol to remove residual chemicals, thus avoiding any host tissue response (Gilbert et al., 2006). The efficiency of the decellularization protocol and the preservation of the ECM have to be assessed using histological tools.
Concerning pericardial decellularization, several protocols, which have provided interesting results, can be found in the literature. (Courtman et al., 2004; Liang et al., 2004; Wei et al., 2005; Chang et al., 2005; Mendoza-Novelo et al.,2010, Ariganello et al.,2011 ). Courtman
On human pericardial tissue, Mirsadraee
Finally, when dealing with autologous pericardium grafting, full decellularization might not be necessary and thus, simpler protocols can be used. For instance, surgeons commonly prepare autologous pericardium for heart valve replacement by mechanical friction. This allows removing sub-pericardial fat before implantation whilebetter preserving the pericardial architecture stability. This mechanical treatment mainly removes superficial cells, thus allowing 50% of viable pericardial cells to remain in the graft (personal data). The preservation of the pericardial architecture as well as part of the pericardial cells, should maintain a better integrity of the graft, while allowing re-cellularization of the superficial layers.
3.2. Effects of decellularization
Depending on the protocol, decellularization may have an impact on the structural and mechanical properties of the treated tissue (Gilbert et al., 2006). According to Zhou
Liao et al.(Liao et al., 2008) investigated the effect of three decellularization protocols on the mechanical and structural properties on porcine aortic valve leaflets. These protocols were based on the use of SDS, Trypsin and Triton X-100. They showed that decellularization resulted in collagen network disruption, and that the ECM pore size varied as a function of the protocol used. For example, leaflets treated with SDS displayed a dense ECM network and small pore sizes,characteristics that may have an impact on the recolonization of interstitial cells.
It has been demonstrated that decellularization of bovine pericardium with SDS causes irreversible denaturation, swelling and a decrease in tensile strength compared to native tissue (Courtman et al. 1994; García-Paéz et al., 2000; Mendoza-Novelo et al., 2009). Because of these deleterious effects on pericardial tissue, non-ionic detergents are preferred for decellularization processes (Mendoza-Novelo et al., 2010 ). Nevertheless, some issues may be encountered with the use of non-ionic detergents. Indeed, toxic effects (Argese et al., 1994) and estrogenic effects (Soto et al., 1991; Jobling et al., 1993) have been reported after the use of non-ionic detergents such as alkylphenol ethoxylates.
Decellularization mediates alterations of the structural and mechanical properties of the tissue, but this impact varies depending on the protocol used. For instance, Mirsadraee
Tissue decellularization reduces the cellular and humoral immune response targeted against the bioprosthesis (Meyer et al., 2005). However, removing cells does not ensure adequate removal of xenoantigens, nor mitigation of the immune response (Goncalves et al., 2005; Kasimir et al., 2006; Simon et al., 2003; Vesely et al., 1995). For this reason, decellularization protocols have turned to antigen removal protocols (Ueda et al., 2006; Kasimir et al., 2005). The presence of cell membrane antigens, such as oligosaccharide beta-Gal has been reported to lead to an immune response that can be prevented by effective decellularization (Badylak et al., 2008). Interestingly, Griffiths
Overall, no optimal decellularization treatment has been identified so far, but depending on the target tissue as well as the implantation site, the protocol can be adapted to provide the best decellularization efficiency / functional characteristics ratio. Moreover, some additional treatment can be performed following the decellularization step in order to improve the mechanical and biological features of the graft.
4. Pericardial extracellular matrix treatment
The decellularization process will lead to important alterations of the biomaterial. Its mechanical strength will be diminished and after implantation it will undergo rapid resorption. Hence, approximately 60% of the mass of the ECM isdegraded and resorbed between one and three months after
To optimize the features of the bioprosthesis before its clinical grafting, several treatments have been developed and are summarized in Table 1.
Reagents | References | |
Cross-linking treatment | Acyl azide | (Petite et al., 1990) |
Carbodiimides | (Sung et al., 2003) | |
Cyanimide | (Pereira et al., 1990) | |
Dye-mediated photooxidation | (Moore et al., 1994) | |
Epoxy compound | (Sung et al., 1997) | |
Formaldehyde | (Nimni et al, 1988) | |
Genepin | (Sung et al., 1999, 2003; Wei et al., 2005) | |
Glutaraldehyde | (Huang-Lee et al, 1990; Jayakrishnan et al., 1996; Thubrikar et al., 1983) | |
Glutaraldehyde acetals | (Yoshioka et al., 2008) | |
Penta-golloyl glucose | (Tedder et al., 2008) | |
Phytate | (Grases et al., 2006, 2008) | |
Proanthocyanidin | (Han et al., 2003) | |
Reuterin | (Chen et al., 2002) | |
Tannic acid | (Cwalina et al., 2005; Jastrzebska et al., 2006; Wang et al., 2008) | |
Coating treatment | Chitosan | (Nogueira et al., 2010) |
RGD polypeptides | (Dong et al., 2009) | |
Silk fibroin | (Nogueira et al., 2010) | |
Heparin sodium | (Lee et al., 2000) | |
Titanium | (Guldner et al., 2009) | |
Post-fixative treatment | Amino acids | (Jorge-Herrero et al., 1996; Moritz et al., 1991) |
Glycine | (Lee et al., 2010) | |
Heparin | (Lee et al., 2000, 2001) | |
Hyaluronic acid | (Ohri et al., 2004) | |
L-arginine | (Jee et al., 2003) | |
L-glutamic | (Grimm et al., 1991; Leukauf et al., 1993) | |
Lyophilization | (Santibáñez-Salgado et al., 2010) | |
Sulphonated poly(ethylene oxide) | (Lee et al., 2001) |
4.1. Cross-linking treatment of pericardial tissue
Cross-linking processing must be carried out to render the tissue non-antigenic, mechanically strong and to minimize xenogeneic tissue degradation (Eliezer et al., 2005; Love, 1997). Nevertheless, degradation should not only be considered as a negative phenomenon, as low molecular weight peptides formed during ECM degradation may have a chemo-attractant potential for several cell types (Badylak & Gilbert, 2008). It is thus the degradation rate of the scaffold that should be primarily considered and evaluated. Depending on the application and cells involved, the degradation rate has to be investigated to ensure proper host cell recruitment and tissue remodelling. The pathways of the immune response involved in this process remain to be fully described (Badylak & Gilbert, 2008).
Introducing cross-links between the polypeptide chains of the ECM has been shown to reduce immunogenicity of the pericardium (Mirsadrae et al., 2007) as well as its biodegradability (Taylor et al., 2006) by increasing its resistance to enzymatic degradation.
Until now, glutaraldehyde (GA)-fixed bovine pericardium has been preferred as a substitute to autologous human pericardium. GA was first introduced by Carpentier
It is now accepted that GA cross-linking increases tissue stiffness (Thubrikar et al., 1983) with the possibility of tissue buckling (Vesely et al., 1988). Standard use of GA cross-linking leads to a high risk of calcific degeneration as well as tissue fatigue (Grabenwoger et al., 1992). This is mostly due to inflammatory and cytotoxicity changes (Huang Lee et al., 1990), and continuous wear and tear leading to collagen fiber fragmentation.
Besides glutaraldehyde, several cross-linking compounds have been reported in the literature such as genipin (Wei et al., 2005) or epoxy compound (Sung et al., 1997). These alternative methods are used to bridge hydroxylysine residues of different polypeptide chains or amino groups of lysine by oligomeric or monomeric crosslinks (Sung et al., 2003). Because of the adverse effects of cross-linking with glutaraldehyde or other aldehyde treatments such as formaldehyde (Nimni et al., 1988) or dialdehyde starch (Rosenberg, 1978), numerous non-aldehyde treatments have been proposed, such as carbodiimides (Sung et al., 2003), glycerol (Ferrans et al., 1991), glycidal ethers (Thyagarajanet al., 1992) including poly(glycidylether) (Noishiki et al., 1986), acyl azide (Petite et al., 1990), cyanimide (Pereira et al., 1990), genipin (Wei et al., 2005), or dye-mediated photo-oxidation, phytate (Grases et al.,2008).
Genipin, obtained from the fruits of
Carbodiimides generate amide-type crosslinks via direct cross-linking of the polypeptide chains. Use of carbodiimide cross-linking leads to the activation of the carboxylic acid groups of glutamic or aspartic acid residues to obtain O-acylisourea groups. Hydroxyline residues or free amino groups of lysine generate a nucleophilic attack which allows cross-link formation (Timkovich, 1977). It was noted that adding N-hydroxysuccinimides to carbodiimides considerably increases cross-link number (Olde Damink et al., 1996). In addition, the use of carbodiimides displayed increased stability towards enzymatic degradation on collagen-based tissue such as pericardium (Sung et al., 2003).
Glutaraldehyde acetal cross-linking reagent has been developed with glutaraldehyde in acid ethanolic solution (Yoshioka & Goissis, 2008), protecting free aldehydic reactive groups and minimizing the polymeric formation of glutaraldehyde. This reduces superficial effects with glutaraldehyde cross-linking on pericardial tissue.
Crosslinking of the pericardial tissue with a dye-mediated photo-oxydation process provides chemical, enzymatic and
Numerous alternative treatments to glutaraldehyde cross-linking have been developed and investigated over the years. However, most of them were mainlyevaluated
4.2. Coating of the pericardium
Another possible post-decellularization treatment resides in the coating of the bioprosthesis. This procedure should allow improvement of graft integration at the site of implantation as well as decreasing degradation of the pericardial tissue.
Coating bovine pericardium with biopolymeric films, either chitosan or silk fibroin, has been investigated by Nogueira et al. (Nogueira et al., 2010). These methods are interesting approaches and both treatments appear to be non-cytotoxic. Nevertheless, chitosan does not allow endothelialisation and silk fibroin-coated bovine pericardium calcifies
In their study, Dong
4.3. Pericardium anti-calcification treatments
The mechanism of calcification on glutaraldehyde-treated pericardium is not well understood because of its complexity. Nevertheless, there is evidence that pericardial tissue residual antigens, free aldhehyde groups of glutaraldehyde and phospholipids are involved in this mechanism.
Thus, circulating antibodies can contribute to pericardial calcification due to a possible immune response. Free aldehyde groups of glutaraldehyde can attract host plasma calcium, increasing tissue calcification. Phospholipids may bind calcium and play an important role in the calcium phosphate crystal formation. Several strategies have been investigated to tackle these major issues.
Suppression of residual antigenicity has been proposed to prevent calcification and it has been shown to be effective. This was performed by fixation treatments using a broad rangeof high concentrations of glutaraldehyde (Trantina-Yates et al., 2003; Zilla et al., 2000). To remove free aldehyde groups, a large number of amino acids or amino compounds were studied. Post-fixation treatments with aminoacids displayedan improved spontaneous endothelialisation
Alcohol solutions, including ethanol, have been investigated as a treatment to remove tissue phospholipids, thus preventing calcification (Pathak et al., 2004; Vyavahare et al., 1998). Besides, other techniques have been proposed to minimize the side effects of glutaraldehyde residues on GA-treated pericardium. Lyophilization has been shown to decrease aldehyde residues, decreasing the risk of calcification and cytotoxicity (Santibáñez-Salgado et al., 2010).
Moreover, treatments with heparin or sulphonated poly(ethylene oxide) following glutaraldehyde pre-treatment have been proposed (Lee et al., 2000, 2001). Both methods blockside effects of GA residues and thus prevent calcification of the pericardium. Finally,a modified adipic dihydrazide hyaluronic acid has been proposed to be grafted on to glutaraldehyde-treated bovine pericardium (Ohri et al., 2004). Calcifications decreased considerably with this post-treatment compared to the control group at two weeks following a subcutaneous implantation in mice.
5.Applications of the pericardium as a biomaterial
So far, the pericardium has been mostly used for cardio-vascular applications, i.e. vascular grafts (Schmidt & Baier, 2000; Chvapil et al., 1970; Matsagas et al., 2006; Menasche et al., 1984
Pericardium source | Surgicalfields | Product | Company |
Bovine orporcine | Soft tissue repair Hernia repair Abdominal & thoracic wall defects | -Peripatch Implantable surgical tissue -TutoMesh | Neovasc, Maverick Biosciences PTY Limited, Tutogen medical GmbH, RTI Biologics, Med&Care, Biovascular Inc, Novomedics |
Strip reinforcement | -Veritas Peristrips Dry | Synovis Life Technology | |
Orbital repair | -Tutopatch -Ocugard | Tutogen medical GmbH, RTI Biologics, Med&Care, Biovascular Inc, Novomedics | |
Dural repair | -Lyolem r All BP | National tissue Bank Malaysia | |
Perivascular Patch | -Peripatch biologic vascular patch | Neovac | |
Cardiac reconstruction and repair | -Peripatch Implantable Surgical Tissue | Neovasc,Maverick Biosciences PTY Limited | |
Heart valve replacement | -PercevalS aortic valve -Mitroflow pericardial aortic valve -Freedom solo -Carpentier-Edwards PERIMOUNT Magna EaseAortic Heart Valve -Carpentier-Edwards PERIMOUNTMagna Mitral Ease Heart Valve -Carpentier-Edwards PERIMOUNT TheonAortic Heart Valve -Carpentier-Edwards PERIMOUNT TheonMitral Replacement System | Sorin group “ “ Edwards Life Sciences “ “ “ | |
Equine | Tendon repair | -OrthADAPT | Synovis Life Technologies Inc |
Human | Valvuloplasty Heart valve | -Xeno or (tissue bank) or autologous grafts | Lausberg et al, 2006 Mirsadaee et al, 2006 |
; Moon & West; 2008), and heart valves (Ishihara et al., 1981; Schoen & Levy, 1999; Flanagan & Pandit, 2003; Vesely, 2005). Pericardial bioprostheseshave also been described for the treatment of acquired cardiac pathologies, including postinfarction septal defects (David et al., 1995), reconstruction of mitral valve annulus (David et al., 1995a, 1995b) or outflow obstruction (Sommers & David, 1997).
Additionally, pericardiumhas also been used for the construction of bioprostheses in non-cardiac treatments such as patches for vaginal (Lazarou et al., 2005) or abdominal wall reparation (Limpert et al., 2009), dural repair (Cantore et al., 1987) or tracheoplasty (Dunham et al., 1994).
6. Conclusion
For clinical application, pericardial tissue has to be decellularized to prevent an immune responses or immune-mediated rejection of the pericardium. Various decellularization protocols have been largely reviewed here. The choice of the decellularization strategy has an impact on the mechanical properties, the scaffold pore size, the scaffold tissue integration and the development of long-term calcification. All these considerations should be carefully taken into account when designing new pericardial-based biomaterials. Currently, glutaraldehyde is the gold standard for pericardial treatment used in clinical practice. Nevertheless, it has important drawbacks including cytotoxic effects, prevention of host cell attachment, migration and proliferation (Huang-Lee et al., 1990), and a high propensity to calcify. Alternative treatments to replace or complement glutaraldehyde crosslinking of the pericardium have been investigated using other crosslinking reagents, decellularization, lyophilisation or coating with biopolymers (Nogueira et al., 2010). Despite many studies, it is still difficult to know which strategy to adopt regarding pericardial treatment. First, we do not have enough follow-up to permit evaluation of most of these alternatives and treatments. Second, every new treatment proposed is generally compared only to glutaraldehyde. It is thus not possible to classify these treatments by efficiency. Finally, the protocol for an optimal treatment depends largely on the final application targeted. In addition, there have been recent advances in tissue regeneration with the emergence of cell therapy and new pericardial treatments with cellular growth factors promoting recellularization (Chang et al., 2007). However, further improvements need to be achieved to transform these techniques into clinical applications. The use of autologous pericardium in cardiac valvular therapy is also a challenging alternative. Nevertheless, it still currently requires the development of local pericardial treatments aiming to favor the valvular remodelling. The understanding of current issues and the improvement of pericardial processing may have a huge impact for bioprothesis conception and patient safety.
References
- 1.
Aortic valve repair with bovine pericardium. (Al-Halees Z. Gometza B. Duran C. M. 1998 65 601 602 - 2.
Al-Halees Z. Al Shahid. M. Al Sanei. A. Sallehuddin A. Duran C. Up to. . years follow-up. of aortic. valve reconstruction. with pericardium. a. stentless readily. available cheap. valve? 2005 . Aug;28 200 205 - 3.
Allen DJ, Didio LJA. 1984 The structure of native human, bovine and porcine parietal pericardium. ,208 3 7A 7A - 4.
Argese E. Marcomini A. Bettiol C. Perin G. Miana P. 1994 Submitochondrial particle response to linear alkylbenzene sulfonates, nonylphenol polyethoxylates and their biodegradation derivates. ,13 737 742 - 5.
Ariganello MB, Labow RS, Lee JM. 2010 In vitro response of monocyte-derived macrophages to a decellularized pericardial biomaterial. ,93 1 280 288 - 6.
Ariganello MB, Simionescu DT, Labow RS, Lee JM. 2011 Macrophage differentiation and polarization on a decellularized pericardial biomaterial. ,32 2 439 449 - 7.
Axelsson L. Chung T. C. Dobrogosz W. J. Lindgren L. E. 1989 Production of a broad spectrum antimicrobial substance by ,2 131 136 - 8.
Bader A. Schilling T. Teebken O. E. Brandes G. Herden T. Steinhoff G. Haverich A. 1998 Tissue engineering of heart valves-human endothelial cell seeding of detergent acellularized porcine valves. ,14 3 279 284 - 9.
Badylak SF, Freytes DO, Gilbert TW. 2009 Extracellular matrix as a biological scaffold material: structure and function. ,5 1 1 13 - 10.
Badylak SF, Gilbert TW. 2008 Immune response to biologic scaffold materials. ,20 2 109 116 - 11.
Bahnson H. T. Hardesty R. L. Baker L. D. Brookes D. I. I. Gall D. A. 1970 Fabrication and evaluation of tissue leafletsfor aortic and mitral valve replacement. ,171 939 947 - 12.
Cantore G. Guidetti B. Delfini R. 1987 Neurosurgical use of human dura mater sterilized by gamma rays and stored in alcohol: long-term results. ,66 1 93 95 - 13.
Carpentier A. Lemaigre G. Robert L. Carpentier S. Dubost C. 1969 Biological factors affecting long-term results in valvular heterografts. ,58 4 467 483 - 14.
Chang Y. Chen S. C. Wei H. J. Wu T. J. Liang H. C. Lai P. H. Yang H. H. Sung H. W. 2005 Tissue regeneration observed in a porous acellular bovine pericardium used to repair a myocardial defect in the right ventricle of a rat model. ,130 5 705 711 - 15.
Chang Y. Lai P. H. Wei H. J. Lin W. W. Chen C. H. Hwang S. M. Chen S. C. Sung H. W. 2007 Tissue regeneration observed in a basic fibroblast growth factor-loaded porous acellular bovine pericardium populated with mesenchymal stem cells. J Thorac Cardiovasc Surg,134 1 65 73 - 16.
Chen CN, Sung HW, Liang HF, Chang WH. 2002 Feasibility study using a natural compound (reuterin) produced by in sterilizing and crosslinking biological tissues. J Biomed Mater Res,61 3 360 369 - 17.
Chvapil M. Kronenthal R. L. van Winkle Jr W. 1970 Medical and surgical applications of collagen, In: , Hall DA, Jackson DS.6 1 61 Chapter 1], Academic Press, NY. - 18.
Courtman D. W. CA Pereira Kashef. V. Mc Comb D. Lee J. M. Wilson G. J. 1994 Development of a pericardial acellular matrix biomaterial: biochemical and mechanical effects of cell extraction. ,28 6 655 666 - 19.
Crapo PM, Gilbert TW, Badylak SF. 2011 An overview of tissue and whole organ decellularization processes. ,32 12 3233 3243 - 20.
Cwalina B. Turek A. Nozynski J. Jastrzebska M. Nawrat Z. 2005 Structural changes in pericardium tissue modified with tannic acid. ,28 6 648 653 - 21.
Dahl S. L. Koh J. Prabhakar V. Niklason L. E. 2003 Decellularized native and engineered arterial scaffolds for transplantation. ,12 6 659 666 - 22.
David T. E. Dale L. Sun Z. 1995 Postinfarction ventricular septal rupture: Repair by endocardial patch with infarct exclusion. ,110 5 1315 1322 - 23.
David T. E. Feindel C. M. Armstrong S. et al. 1995 Reconstruction of the mitral annulus. A ten-year experience. ,110 1323 x1328 - 24.
DeCarbo WT, Feldner BM, Hyer CF. 2010 Inflammatory Reaction to Implanted Equine Pericardium Xenograft. ,49 2 155 158 - 25.
Dong X. Wei X. Yi W. Gu C. Kang X. Liu Y. Li Q. Yi D. 2009 RGD-modified acellular bovine pericardium as a bioprosthetic scaffold for tissue engineering. ,20 2327 2336 - 26.
ME Dunham Holinger. L. D. Backer C. L. Mavroudis C. 1994 Management of severe congenital tracheal stenosis. ,103 351 356 - 27.
Treated bovine and autologous pericardium for aortic valve reconstruction. (Duran C. M. Gometza B. Shahid M. Al-Halees Z. 1998 Dec;66 S166 S199 - 28.
Edwards WS. 1969 Aortic valve replacement with autogenous tissue.8 126 132 - 29.
Eliezer MA, Lydia MM, Virna VR, Carlos FR. 2005 Mechanics of biomaterials: vascular graft prostheses. , GED, University of Puerto Rico, Mayaguez, Group A: A1 A25, May 2005. - 30.
Ferrans V. J. Milei J. Ishihara T. Storino R. 1991 Structural changes in implanted cardiac valvular bioprostheses constructed of glycerol-treated dura mater. ,5 3 144 154 - 31.
Flanagan T. C. Pandit A. 2003 Living artificial heart valve alternatives: a review. ,6 28 45 - 32.
Fomovsky G. M. Thomopoulos S. Holmes J. W. 2010 Contribution of extracellular matrix to the mechanical properties of the heart. ,48 3 490 496 - 33.
Freytes DO, Badylak SF, Webster TJ, Geddes LA, Rundell AE. 2004 Biaxial strength of multilaminated extracellular matrix scaffolds. ,25 12 2353 2361 - 34.
Fujikawa S. Yokota T. Koga K. Kumada J. 1987 The continuous hydrolysis of geniposide to genipin using immobilized β-glucosidase on calcium alginate gel. ,9 697 702 - 35.
Gallo I. Artinano E. Nistal F. 1985 Four- to seven-year follow-up of patients undergoing Carpentier-Edwards porcine heart valve replacement. ,33 6 347 351 - 36.
Gamba P. G. Conconi M. T. Lo Piccolo. R. Zara G. Spinazzi R. Parnigotto P. P. 2002 Experimental abdominal wall defect repaired with acellular matrix. ,18 5-6 327 331 - 37.
García-Paéz J. M. Herrero J. Carrera-San Martín. A. García-Sestafe J. V. Téllez G. Millán I. Salvador J. Cordon A. Castillo-Olivares J. L. 2000 The influence of chemical treatment and suture on the elastic behavior of calf pericardium utilized in the construction of cardiac bioprostheses. ,11 5 273 277 - 38.
Gilbert TW, Sellaro TL, Badylak SF. 2006 Decellularization of tissues and organs. Biomaterials,27 19 3675 3683 - 39.
Goetz W. A. Lim H. S. Lansac E. Weber P. A. Duran C. M. A. temporarily stented. autologous pericardial. aortic valve. prosthesis 2002 .Sep;11(5):(696-702). - 40.
Goissis G. Suzigan S. Parreira D. R. Maniglia J. V. Braile D. M. Raymundo S. 2000 Preparation and characterization of collagen-elastin matrices from blood vessels intended as small diameter vascular grafts. ,24 3 217 223 - 41.
Goncalves AC, Griffiths LG, Anthony RV, Orton EC. 2005 Decellularization of bovine pericardium for tissue-engineering by targeted removal of xenoantigens. ,14 2 212 217 - 42.
Grabenwoger M. Grimm M. Eybl E. Leukauf C. MM Muller Plenck. Jr Böck H. P. 1992 Decreased tissue reaction to bioprosthetic heart valve material after glutamic acid treatment. A morphological study. ,26 9 1231 1240 - 43.
Grabenwoger M. Sider J. Fitzal F. Zelenka C. Windberger U. Grimm M. Moritz A. Böck A. Wolner E. 1996 Impact of glutaraldehyde on calcification of pericardial bioprosthetic heart valve material. ,62 3 772 777 - 44.
Grases F. Sanchis P. Costa-Bauzá A. Bonnin O. Isern B. Perelló J. Prieto R. M. 2008 Phytate inhibits bovine pericardium calcification in vitro. ,17 3 139 145 - 45.
Grases F. Sanchis P. Perello J. Isern B. Prieto R. M. Fernandez-Palomeque C. Fiol M. Bonnin O. Torres J. J. 2006 Phytate (myo-inositol hexakisphosphate) inhibits cardiovascular calcifications in rats. ,11 136 142 - 46.
Grauss R. W. Hazekamp M. G. van Vliet S. Gittenberger-de Groot. A. C. De Ruiter M. C. 2003 Decellularization of rat aortic valve allografts reduces leaflet destruction and extracellular matrix remodeling. ,126 6 2003 2010 - 47.
Griffiths LG, Choe LH, Reardon KF, Dow SW, Orton EC. 2008 Immunoproteomic identification of bovine pericardium xenoantigens. ,29 26 3514 3520 - 48.
Grimm M. Eybl E. Grabenwoger M. Griesmacher A. Losert U. Bock P. MM Muller Wolner. E. 1991 Biocompatibility of aldehyde-fixed bovine pericardium. An in vitro and in vivo approach toward improvement of bioprosthetic heart valves. ,102 2 195 201 - 49.
Guldner N. W. Jasmund I. Zimmermann H. Heinlein M. Girndt B. Meier V. Flüß F. Rohde D. Gebert A. Sievers H. H. 2009 Detoxification and Endothelialization of Glutaraldehyde-Fixed Bovine Pericardium With Titanium Coating: A New Technology for Cardiovascular Tissue Engineering. ,119 12 1653 1660 - 50.
Han B. Jaurequi J. Wei Tang. B. ME Nimni 2003 Proanthocyanidin: A natural crosslinking reagent for stabilizing collagen matrices. ,65 1 118 124 - 51.
Hiester ED, Sacks MS. 1998a Optimal bovine pericardial tissue selection sites. I. Fiber architecture and tissue thickness measurements. ,39 2 207 214 - 52.
Hiester ED, Sacks MS. 1998b Optimal bovine pericardial tissue selection sites. II. Cartographic analysis. ,39 2 215 221 - 53.
Huang Lee LLH, Cheung DT, Nimni ME. 1990 Biochemical changes and cytotoxicity associated with the degradation of polymeric glutaraldehyde derived cross-links. ,24 9 1185 1201 - 54.
Hudson T. W. Zawko S. Deister C. Lundy S. Hu C. Y. Lee K. CE Schmidt 2004 Optimized acellular nerve graft is immunologically tolerated and supports regeneration. ,10 11-12 1641 1651 - 55.
Ishihara T. Ferans V. J. Jones M. Boyce S. W. Roberts W. C. 1981 Structure of bovine parietal pericardium and of unimplanted Ionescu shiley pericardial valvular bioprostheses. ,81 5 747 757 - 56.
Jackson D. W. Grood E. S. Wilcox P. Butler D. L. Simon T. M. Holden J. P. 1988 The effects of processing techniques on the mechanical properties of bone-anterior cruciate ligament-bone allografts. An experimental study in goats. ,16 2 101 105 - 57.
Jastrzebska M. Zalewska-Rejdak J. Wrzalik R. Kocot A. Mroz I. Barwinski B. Turek A. Cwalina B. 2006 Tannic acid-stabilized pericardium tissue: IR spectroscopy, atomic force microscopy, and dielectric spectroscopy investigations. ,78 1 148 156 - 58.
Jayakrishnan A. Jameela S. R. 1996 Glutaraldehyde as a fixative in bioprostheses and drug delivery matrices. ,17 5 471 484 - 59.
Jee KS, Kim YS, Park KD, Kim YH. 2003 A novel chemical modification of bioprosthetic tissues using L-arginine. ,24 20 3409 3416 - 60.
Jobling S. Sumpter J. P. 1993 Detergent components in sewage effluent are weakly estrogenic to fish- an in vitro study using rainbow-trout. ,27 361 372 - 61.
Jorge-Herrero E. Fernandez P. Escudero C. Garcia-Paez J. M. Castillo-Olivares J. L. 1996 Calcification of pericardial tissue pretreated with different amino acids. ,17 6 571 575 - 62.
Jorge-Herrero E. Fernandez P. Turnay J. Olmo N. Calero P. Garcia R. Freile I. Castillo-Olivares J. L. 1999 Influence of different chemical cross-linking treatments on the properties of bovine pericardium and collagen. ,20 6 539 545 - 63.
Kasimir M. T. Rieder E. Seebacher G. Nigisch A. Dekan B. Wolner E. Weigel G. Simon P. 2006 Decellularization does not eliminate thrombogenicity and inflammatory stimulation in tissue-engineered porcine heart valves. ,15 2 278 286 discussion 286]. - 64.
Kasimir M. T. Rieder E. Seebacher G. Wolner E. Weigel G. Simon P. 2005 Presence and elimination of the xenoantigen gal (alpha1, 3) gal in tissue-engineered heart valves. ,11 7-8 1274 1280 - 65.
Keuren J. F. W. Wielders S. J. H. Driessen A. Verhoeven M. Hendriks M. Lindhout T. 2004 Covalently-bound heparin makes collagen thromboresistant. ,24 3 613 617 - 66.
Lazarou G. Powers K. Pena C. Bruck L. MS Mikhail 2005 Inflammatory reaction following bovine pericardium graft augmentation for posterior vaginal wall defect repair. ,16 3 242 244 - 67.
Lee C. Kim S. H. Choi S. H. Kim Y. J. 2011 High-concentration glutaraldehyde fixation of bovine pericardium in organic solvent and post-fixation glycine treatment: in vitro material assessment and in vivo anticalcification effect. ,39 3 381 387 - 68.
Lee JM, Boughner DR. 1981 Tissue mechanics of canine pericardium in different test environment. ,49 2 533 544 - 69.
Lee JM, Boughner DR. 1985 Mechanical properties of human pericardium. Differences in viscoelastic response when compared with canine pericardium. ,57 3 475 481 - 70.
Lee W. K. Park K. D. Han D. K. Suh H. Park J. C. Kim Y. H. 2000 Heparinized bovine pericardium as a novel cardiovascular bioprosthesis. ,21 22 2323 2330 - 71.
Lee W. K. Park K. D. Kim Y. H. Suh H. Park J. C. Lee J. E. Sun K. MJ Baek Kim. H. M. Kim S. H. 2001 Improved Calcification Resistance and Biocompatibility of Tissue Patch Grafted with Sulfonated PEO or Heparin after Glutaraldehyde Fixation. ,58 1 27 35 - 72.
Leukauf C. Szeles C. Salaymeh L. Grimm M. Grabenwoger M. Losert U. Moritz A. Wolner E. 1993 In vitro and in vivo endothelialization of glutaraldehyde treated bovine pericardium. ,2 2 230 235 - 73.
Liang H. C. Chang Y. Hsu C. K. Lee M. H. Sung H. W. 2004 Effects of crosslinking degree of an acellular biological tissue on its tissue regeneration pattern. ,25 17 3541 3552 - 74.
Liao J. Joyce E. M. MS Sacks 2008 Effects of decellularization on the mechanical and structural properties of the porcine aortic valve leaflet. ,29 8 1065 1074 - 75.
Liao J. Yang L. Grashow J. MS Sacks 2005 Molecular orientation of collagen in intact planar connective tissues under biaxial stretch. ,1 1 45 54 - 76.
Limpert JN, Desai AR, Kumpf AL, Fallucco MA, Aridge DL. 2009 Repair of abdominal wall defects with bovine pericardium. ,198 e60 e65 - 77.
Love JW. 1997 Cardiac prostheses, In: , Lanza R, Langer R, Chick W,365 378 R.G. Landes Company, New York. - 78.
Lovekamp J. J. Simionescu D. T. Mercuri J. J. Zubiate B. MS Sacks Vyavahare. N. R. 2006 Stability and function of glycosaminoglycans in porcine bioprosthetic heart valves. ,27 8 1507 1518 - 79.
MM Maestro Turnay. J. Olmo N. Fernández P. Suárez D. García Páez. J. M. Urillo S. MA Lizarbe-Herrero Jorge. E. 2006 Biochemical and mechanical behavior of ostrich pericardium as a new biomaterial. ,2 2 213 219 - 80.
Matsagas M. I. Bali C. Arnaoutoglou E. Papakostas J. C. Nassis C. Papadopoulos G. Kappas A. M. 2006 Carotid endarterectomy with bovine pericardium patch angioplasty: mid-term results. ,20 5 614 619 - 81.
Mc Fetridge P. S. Daniel J. W. Bodamyali T. Horrocks M. Chaudhuri J. B. 2004 Preparation of porcine carotid arteries for vascular tissue engineering applications. ,70 2 224 234 - 82.
Menasche P. Flaud P. Huc Co. A. Piwnica A. 1984 Collagen vascular grafts: a step towards improved compliance in small-caliber by-pass surgery: preliminary report. ,2 4 233 237 - 83.
Mendoza-Novelo B. EE Avila-Rodríguez Cauich. Jorge-Herrero J. V. Rojo E. Guinea F. J. Mata-Mata G. V. J. L. 2011 Decellularization of pericardial tissue and its impact on tensile viscoelasticity and glycosaminoglycan content. ,7 3 1241 1248 - 84.
Mendoza-Novelo B. Cauich-Rodriguez J. V. 2009 The effect of surfactants, crosslinking agents and L-cysteine on the stabilization and mechanical properties of bovine pericardium. ,7 2 123 131 - 85.
Meyer S. R. Nagendran J. Desai L. S. Rayat G. R. Churchill T. A. Anderson C. C. Rajotte R. V. Lakey J. R. T. Ross D. B. 2005 Decellularization reduces the immune response to aortic valve allografts in the rat. ,130 2 469 476 - 86.
Mirsadraee S. Wilcox H. E. Korossis S. Kearney J. N. Watterson K. G. Fisher J. Ingham E. 2006 Development and characterization of an acellular human pericardial matrix. ,12 4 763 773 - 87.
Mirsadraee S. Wilcox H. E. Watterson K. G. Kearney J. N. Hunt J. Fisher J. Ingham E. 2007 Biocompatibility of Acellular Human Pericardium. ,143 2 407 414 - 88.
Moon JJ, West JL. 2008 Vascularization of engineered tissues: approaches to promote angiogenesis in biomaterials. ,8 4 300 310 - 89.
MA Moore Bohachevsky. I. K. Cheung D. T. BD Boyan Chen. W. Bickers R. R. Mc Ilroy B. K. 1994 Stabilization of pericardial tissue by dye-mediated photooxidation. ,28 5 611 618 - 90.
Moritz A. Grimm M. Eybl E. Grabenwoger M. Grabenwoger F. Bock P. Wolner E. 1991 Improved spontaneous endothelialization by postfixation treatment of bovine pericardium. ,5 3 155 159 discussion 160]. - 91.
Neethling W. M. Cooper S. Van Den Heever. J. J. Hough J. Hodge A. J. 2002 Evaluation of kangaroo pericardium as an alternative substitute for reconstructive cardiac surgery. ,43 3 301 306 - 92.
Neethling W. M. Papadimitriou J. M. Swarts E. Hodge A. J. 2000 Kangaroo versus porcine aortic valve tissue-valve geometry morphology, tensile strength and calcification potential. ,41 3 341 348 - 93.
ME Nimni Cheung. D. Strates B. Kodama M. Sheikh K. 1988 Bioprosthesis derived from cross-linked and chemically modified collagenous tissues, In: , Nimni ME,1 38 CRC Press, Boca Raton, FL. - 94.
Nogueira G. M. Rodas A. C. D. Weska R. F. Aimoli C. G. Higa O. Z. Maizato M. AA Leiner Pitombo. R. N. M. Polakiewicz B. MM Beppu 2010 Bovine pericardium coated with biopolymeric films as an alternative to prevent calcification: calcification and cytotoxicity results. Materials Science and Engineering C,30 575 582 - 95.
Noishiki Y. Kodaira K. Furuse M. Miyata T. 1989 Method of preparing antithrombogenic medical materials, U.S. Patent4 - 96.
Noishiki Y. Miyata T. Kodaira K. 1986 Development of a small caliber vascular graft by a new crosslinking method incorporating slow heparin release collagen and natural tissue compliance. ,32 1 114 119 - 97.
Ohri R. Hahn S. K. AS Hoffman Stayton. P. S. Giachelli C. M. 2004 Hyaluronic acid grafting mitigates calcification of glutaraldehyde-fixed bovine pericardium. ,70 2 328 334 - 98.
Olde Damink. L. H. Dijkstra P. J. MJ van Luyn van Wachem. P. B. Nieuwenhuis P. Feijen J. 1996 Cross-linking of dermal sheep collagen using a water-soluble carbodiimide. ,17 8 765 773 - 99.
CP Pathak Adams. A. K. Simpson T. Phillips R. E. MA Moore 2004 Treatment of bioprosthetic heart valve tissue with long chain alcohol solution to lower calcification potential. ,69 1 140 144 - 100.
CA Pereira Lee. J. M. Haberer S. 1990 Effect of alternative crosslinking methods on the strain rate viscoelastic properties of bovine pericardial bioprosthetic material. ,24 3 345 361 - 101.
Petite H. Rault I. Huc A. Menasche P. Herbage D. 1990 Use of the acyl azide method for cross-linking collagen-rich tissues such as pericardium. ,24 2 179 187 - 102.
MD Pierschbacher Ruoslahti. E. 1984 Cell attachment activity of fibronectin can be duplicated by small synthetic fragments of the molecule. ,309 5963 30 33 - 103.
Rieder E. Kasimir M. T. Silberhumer G. Seebacher G. Wolner E. Simon P. Weigel G. 2004 Decellularization protocols of porcine heart valves differ importantly in efficiency of cell removal and susceptibility of the matrix to recellularization with human vascular cells. ,127 2 399 405 - 104.
Roberts T. S. Drez Jr D. Mc Carthy W. Paine R. 1991 Anterior cruciate ligament reconstruction using freeze-dried, ethylene oxide-sterilized, bone-patellar tendon-bone allografts. Two year results in thirty-six patients. ,19 1 35 41 - 105.
Rosenberg D. 1978 Dialdehyde starch tanned bovine heterografts: Development, In: , Sawyer PN, Kaplitt MJ,261 270 Appleton Century-Crofts, New York. - 106.
Ruoslahti E. MD Pierschbacher 1987 New perspectives in cell adhesion: RGD and integrins. ,238 4826 491 497 - 107.
Sacks MS. 2003 Incorporation of experimentally-derived fiber orientation into a structural constitutive model for planar collagenous tissues. ,125 2 280 287 - 108.
Santibáñez-Salgado J. A. Olmos-Zúñiga J. R. Pérez-López M. Aboitiz-Rivera C. Gaxiola-Gaxiola M. Jasso-Victoria R. Sotres-Vega A. Baltazares-Lipp M. Pérez-Covarrubias D. Villalba-Caloca J. 2010 Lyophilized Glutaraldehyde-Preserved Bovine Pericardium for Experimental Atrial Septal Defect Closure. ,19 158 165 - 109.
Sato H. Suzuki N. Baba T. Ueda T. Mawatari T. Izumiyama O. Morishita K. Hasegawa T. 2008 Repair of ventricular septal perforation with asymmetrical conical patch exclusion. ,14 3 192 195 - 110.
Schenke-Layland K. Vasilevski O. Opitz F. Konig K. Riemann I. Halbhuber K. J. Wahlers T. Stock U. A. 2003 Impact of decellularization of xenogeneic tissue on extracellular matrix integrity for tissue engineering of heart valves. ,143 3 201 208 - 111.
Schmidt CE, Baier JM. 2000 Acellular vascular tissues: natural biomaterials for tissue repair and tissue engineering. ,21 22 2215 2231 - 112.
Schoen FJ, Levy RJ. 1999 Tissue heart valves: current challenges and future research perspectives. ,47 4 439 465 - 113.
Simon P. Kasimir M. T. Rieder E. Weigel G. 2006 Tissue Engineering of heart valves-Immunologic and inflammatory challenges of the allograft scaffold. ,21 161 165 - 114.
Simon P. Kasimir M. T. Seebacher G. Weigel G. Ullrich R. Salzer-Muhar U. Rieder E. Wolner E. 2003 Early failure of the tissue engineered porcine heart valve SYNERGRAFT in pediatric patients. ,23 6 1002 1006 discussion 1006]. - 115.
Sommers KE, David TE. 1997 Aortic valve replacement with patch enlargement of the aortic annulus. ,63 6 1608 1612 - 116.
Soto A. M. Justicia H. Wray J. M. Sonnenschein C. 1991 P-nonylphenol, an estrogenic xenobiotic released from modified polystyrene. ,92 167 173 - 117.
Sung HW, Chang WH, Ma CY, Lee MH. 2003 Crosslinking of biological tissues using genipin and/or carbodiimide. ,64 3 427 438 - 118.
Sung HW, Hsu CS, Wang SP, Hsu HL. 1997 Degradation potential of biological tissues fixed with various fixatives: An study. J Biomed Mater Res,35 2 147 155 - 119.
Sung HW, Huang RN, Huang LLH, Tsai CC. 1999 evaluation of cytotoxicity of a naturally occurring crosslinking reagent for biological tissue fixation. J Biomater Sci Polymer,10 63 78 - 120.
Taylor PM, Cass AEG, Yacoub MH. 2006 Extracellular matrix scaffolds for tissue engineering heart valves. ,21 219 225 - 121.
ME Tedder Liao. J. Weed B. Stabler C. Zhang H. Simionescu A. Simionescu D. T. 2009 Stabilized Collagen Scaffolds for Heart Valve Tissue Engineering. ,15 6 1257 1268 - 122.
Teebken O. E. Bader A. Steinhoff G. Haverich A. 2000 Tissue engineering of vascular grafts: human cell seeding of decellularised porcine matrix. ,19 4 381 386 - 123.
MJ Thubrikar Deck. JD Aouad J. Nolan S. P. 1983 Role of mechanical stress in calcification of aortic bioprosthetic valves. ,86 1 115 125 - 124.
Thyagarajan K. Nguyen H. Tu R. Lohre J. Guida S. Sagartz J. W. Quijano R. C. 1992 Preliminary evaluation of calcification potential of Denacolt treated small diameter biological vascular grafts. ,15 686 688 - 125.
Timkovich R. 1977 Detection of the stable addition of carbodiimide to proteins. ,79 1-2 135 143 - 126.
Trantina-Yates A. E. Human P. Zilla P. 2003 Detoxification on top of enhanced, diamine-extended glutaraldehyde fixation significantly reduces bioprosthetic root calcification in the sheep model. ,12 1 93 101 discussion 100-1]. - 127.
Tsai T. H. Westly J. Lee T. F. Chen C. F. 1994 Identification and determination of geniposide, genipin, gardenoside, and geniposidic acid from herbs by HPLC/photodiode-array detection. ,17 2199 2205 - 128.
Ueda Y. Torrianni M. W. Coppin C. M. Iwai S. Sawa Y. Matsuda H. 2006 Antigen clearing from porcine heart valves with preservation of structural integrity. ,29 8 781 789 - 129.
Vesely I. Boughner D. Song T. 1988 Tissue buckling as a mechanism of bioprosthetic valve failure. ,46 3 302 308 - 130.
Vesely I. Noseworthy R. Pringle G. 1995 The hybrid xenograft/autograft bioprosthetic heart valve: in vivo evaluation of tissue extraction. ,60 No. Suppl. 2,S359 S364 - 131.
Vesely I. 2005 Heart Valve Tissue Engineering. ,97 8 743 755 - 132.
Vyavahare N. Hirsch D. Lerner E. Baskin J. Z. Schoen F. J. Bianco R. Kruth H. S. Zand R. Levy R. J. 1997 Prevention of bioprosthetic heart valve calcification by ethanol preincubation. Efficacy and mechanisms. ,95 2 479 488 - 133.
Vyavahare N. R. Hirsch D. Lerner E. Baskin J. Z. Zand R. Schoen F. J. Levy R. J. 1998 Prevention of calcification of glutaraldehyde-crosslinked porcine aortic cusps by ethanol preincubation: Mechanistic studies of protein structure and water-biomaterial relationships. ,40 4 577 585 - 134.
Wang D. Jiang H. Li J. Zhou J. Y. Hu S. S. 2008 Mitigated calcification of glutaraldehyde-fixed bovine pericardium by tannic acid in rats. ,121 17 1675 1679 - 135.
Wei H. J. Liang H. C. Lee M. H. Huang Y. C. Chang Y. Sung H. W. 2005 Construction of varying porous structures in acellular bovine pericardia as a tissue-engineering extracellular matrix. ,26 14 1905 1913 - 136.
Wiegner AW, Bing OH, Borg TK, Caulfield JB. 1981 Mechanical and structural of canine pericardium. ,49 3 807 814 - 137.
Woods T. Gratzer P. F. 2005 Effectiveness of three extraction techniques in the development of a decellularized bone-anterior cruciate ligament-bone graft. ,26 35 7339 7349 - 138.
Yamamoto H. Yamamoto F. Ishibashi K. Motokawa M. 2009 In situ replacement with equine pericardial roll grafts for ruptured infected aneurysms of the abdominal aorta. ,49 4 1041 1045 - 139.
Yoshioka S. A. Goissis G. 2008 Thermal and spectrophotometric studies of new crosslinking method for collagen matrix with glutaraldehyde acetals. ,19 3 1215 1223 - 140.
Zhou J. Fritze O. Schleicher M. Wendel H. P. Schenke-Layland K. Harasztosi C. Hu S. Stock U. A. 2010 Impact of heart valve decellularization on 3-D ultrastructure, immunogenicity and thrombogenicity. ,31 9 2549 2554 - 141.
Zilla P. Weissenstein C. Human P. Dower T. von Oppell. U. O. 2000 High glutaraldehyde concentrations mitigate bioprosthetic root calcification in the sheep model. ,70 6 2091 2095 - 142.
Zioupos P. Barbenel J. C. 1994 Mechanics of native bovine pericardium. I. The multiangular behavior of strength and stiffness of the tissue. ,15 5 366 373