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Kofidis, T. Myocardial Restoration Therapy. Encyclopedia. Available online: https://encyclopedia.pub/entry/10402 (accessed on 25 April 2024).
Kofidis T. Myocardial Restoration Therapy. Encyclopedia. Available at: https://encyclopedia.pub/entry/10402. Accessed April 25, 2024.
Kofidis, Theo. "Myocardial Restoration Therapy" Encyclopedia, https://encyclopedia.pub/entry/10402 (accessed April 25, 2024).
Kofidis, T. (2021, June 02). Myocardial Restoration Therapy. In Encyclopedia. https://encyclopedia.pub/entry/10402
Kofidis, Theo. "Myocardial Restoration Therapy." Encyclopedia. Web. 02 June, 2021.
Myocardial Restoration Therapy
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This entry is adapted from the peer-reviewed paper 10.3390/biomedicines9060595

Myocardial restoration approaches so far have encompassed various types of cells, cell products or derivatives, scaffolds of various physical conditions, as well as multiple administration routes. 

hydrogel extracellular matrix hydrogels myocardial infarctions myocardial infarction therapy cardiac stem cell therapy tissue engineering cell-based therapy

1. Introduction

The prevailing dogma suggesting that adult mammalian cardiomyocytes are post-mitotic cells with no ability to renew has been recently overthrown by studies demonstrating a low level of proliferation, even in adult hearts [1]. However, the regenerative capacity is minimal and insufficient to overcome the loss of cardiac cells following MI. The inability of the adult heart to regenerate has yielded several preclinical and clinical studies focused on different cell-based therapies. Despite very promising preclinical results, these results have so far not been translated into clinical practice. Some of the major challenges limiting their clinical application are low retention and survival rates; very limited trans-differentiation into cardiomyocytes; safety; and, in some cases, ethical concerns.
Over the last few decades, cell therapy has been applied in clinical myocardial restoration. Though the result is non-conclusive, some studies have shown the attenuation of ventricular remodeling. The ensuing hostile and inflammatory environment results in the rapid death of injected cells, or lack of integration thereof. It is incomprehensive, and the vast majority of studies have proven that injected cells do not organize in an integrated syncytium, which excites orchestrated contractility. Depending on the type of cells that are randomly injected, different complications occur [2]. Solid scaffolds—even when adding thickness to the aneurysmatic scar—have not proven themselves as a viable solution either, particularly due to the necessity of open heart surgery to implant them (Figure 1).
Figure 1. Diagram showing the current methods of regenerative cardiac therapy. (A): Method 1—intramyocardial delivery (injection) of stem cells only, without a retaining matrix. (B): Method 2—seeding of cells into a patch-like matrix, which is then implanted onto the epicardium via sutures or glue. (C): Method 3—intramyocardial injection of cells/active ingredient retained in a gel matrix, either during an open surgery (thoracotomy) or in a minimally invasive manner (percutaneously, etc.).
There is an obvious need for a targeted, less invasive myocardial restoration treatment, which does not add too much stand-alone trauma to the patient and can be integrated into a viable clinical protocol, to be adopted by cardiologists as well. Arising from the above pain-points, we have long shifted our focus from stem cells to liquid compounds, with the following key value propositions:
  • Injectable, hence minimally invasive, administration
  • Autologous material, not of stem cell nature, to be derived simply during treatment
  • A polytherapy approach to address concomitant aspects of the vicious circle of myocardial ischemia (antioxidants, purine metabolism blockers/anti-inflammatory drugs)
  • Easy adoption and clinical penetration in the horizon.

2. Targeted Myocardial Restoration with Injectable Hydrogels

2.1. Post-MI Survivability

In the vast majority of cases, MI is a consequence of a vulnerable plaque rupture and a subsequent intracoronary thrombosis. The process initiates maladaptive changes in the myocardium, termed “cardiac remodeling“, which may result in the development of HF (Figure 1). The clinical sequelae are encountered in up to three-quarters of patients within five years after their first coronary event [3]. Importantly, HF has not only a significant impact on patients‘ functional capacity and quality of life, but the disease also significantly affects their life expectancy. Available data indicate that approximately half of the patients with HF do not survive for more than five years after the diagnosis [4], meaning that despite the advances in cardiac care, survival rates in this patient population are still very poor and are comparable to those observed in many types of cancer [5][6]. Given the above, more still needs to be done to tackle the burden of the disease more efficiently, thus triggering alternative mono- or poly-therapeutic treatments using viable matter and scaffolds.

2.2. Injectable Hydrogel-Based Approach for Cardiac Tissue Engineering

Owing to the intricate myocardial architecture and function, we believe that the triple approach (i.e., enhancing viability, counteracting inflammation, and stabilizing the diminishing architectural integrity of the left ventricle) yields the best restorative effect. Some of the most promising therapeutic compounds are hydrogel-based biomaterials that can not only provide mechanical support for a failing heart, but can also serve as a vehicle for cells, growth factors, and drugs. Because of their potential for minimally invasive transcatheter delivery, injectable hydrogels appear to be one of the most promising types of compounds in terms of their potential clinical application. Several types of hydrogel-based approaches for cardiac tissue repair have been investigated to date. Each category of hydrogels has its advantages and disadvantages that can influence their potential clinical applicability. There are various types of hydrogels with different properties based on their origin (natural/synthetic), various mechanisms of cross-linking, etc.
Based on the best evidence, we have observed a diverse range of compounds with none of the compositions showing clear superiority (Table 1). There are a number of studies, using acellular hydrogel by changing the matrix composition, more focused to investigate whether hydrogel characteristics (i.e, stiffening) enhances therapeutic efficacy to limit LV remodeling and heart failure [7]. Synthetic hydrogel: poly (NIPAAm-co-HEMA-co-MAPLA) (Sigma-Aldrich, St. Louis, MO, USA) was used in some studies [8][9], but hyaluronic acid-based hydrogel was used in most cases. Cell types, including skeletal myoblasts (SKMs), CMs, and other progenitor cells capable of differentiation to CMs, like embryonic stem cells (ESCs), ESC-derived CMs (ESCCMs), and mesenchymal stem cells (MSCs) with limited potentials, were investigated. Human umbilical mesenchymal stem cells [hUMSC] are a new focus [10], whereas basic fibroblast growth factor (bFGF), acidic gelatin hydrogel microspheres (AGHM), and vascular endothelial growth factor (VEGF) are in use with non-superiority to each other. Vu et al. used hyaluronic acid-based hydrogel coupled with PRP and showed improved host-cell viability [11]; while Traverse et al. [12] reported the first-in-human study with VentriGelTM (ECM from the decellularized porcine myocardium) in patients with 1st STEMI treated by PCI within a period of post-intervention between 60 days and 3 years, and found MRI evidence of LV remodeling and a clinical improvement in the study subgroup.
Table 1. Hydrogel characterization and mode of delivery.
Author Method of MI Creation Artery Involved Cell Delivered Type of Matrix Method of Delivery to Myocardium
Giordano, C et al., 2013 [13] Left thoracotomy with ameroid constrictor Proximal LCx CAC Type-I rat tail collagen cross-linked with glutaraldehyde (BD Bioscience, Oakville, Canada) Open; Intramyocardial
Leor, J et al., 2009 [14] Balloon occlusion Mid-LAD artery Acellular Sodium alginate (VLVG, NovaMatrix, FMC Biopolymers, Drammen, Norway) Intracoronary
Matsumura, Y et al., 2019 [8] Left thoracotomy with suture ligation Between 1st and 2nd diagonal branches Acellular Synthetic Hydrogel: Poly (NIPAAm-co-HEMA-co-MAPLA) (Sigma-Aldrich, USA) Open; Intramyocardial
Qiang Wang et al., 2021 [10] Left thoracotomy with suture ligation LAD distal to origin of 2nd branch hUMSC Bovine collagen Open; Intramyocardial
Yamamoto, T et al., 2001 [15] Left thoracotomy with suture ligation LAD between 1st and 2nd diagonal branches bFGF AGHM Open; Subepicardial implantation
Zhou, D et al., 2012 [16] Left thoracotomy with suture ligation LAD below 1st diagonal branch VEGF165 Temperature-responsive Chitosan hydrogel Open; Transmyocardial jet revascularization
Cohen, J.E et al., 2020 [17] Left thoracotomy with suture ligation 2nd and 3rd diagonal branches of LAD NRG (R&D Systems, Minneapolis, MN, USA) HEMA-HA based hydrogel (Lifecore Biomedical Inc., Chaska, MN, USA) Open; intramyocardial
Contessotto, P et al., 2021 [18] Left thoracotomy with suture ligation LAD from 1st diagonal branch, moving distally till apex Acellular ELRs hydrogel Open; Intramyocardial
Li, Y et al., 2021 [19] Left thoracotomy with suture ligation 1st two obtuse marginal arteries of LCx MSN/miR-21-5p complex Injectable hydrogel matrix Open; Intramyocardial
Purcell, B.P et al., 2013 [20] Left thoracotomy with suture ligation 1st two obtuse marginal arteries of LCx Full-length rTIMP-3 Hyaluronic acid-based hydrogel with MMP Open; Intramyocardial
Chang, M.Y et al., 2016 [21] Left thoracotomy with suture ligation Mid-LAD CB-MNC Hyaluronic acid hydrogel Open; Intramyocardial
Ifkovits, J. L et al., 2010 [22] Left thoracotomy with suture ligation LAD and 2nd diagonal coronary artery Acellular Methacrylated hyaluronic acid macromers (MeHA) hydrogel Open; Intramyocardial
Koudstaal, S et al., 2014 [23] 75 min intracoronary balloon occlusion LCx IGF-1/HGF UPy hydrogel Open; Intramyocardial
Lin, Y.D et al., 2015 [24] Left thoracotomy with suture ligation Mid-LAD MNCs Peptide nanofibers Open; Intramyocardial
Liu, Y et al., 2006 [25] Left thoracotomy with suture ligation LAD distal to 1st diagonal branch bFGF, BDNF Gelatin hydrogel (Boster Bioengineering Company, Wuhan, China) Open; Intramyocardial
Yao Chang, M et al., 2005 [26] Left thoracotomy with suture ligation Mid-LAD Bone marrow MNC Peptide nanofibers Open; Intramyocardial
Rodell, C.B et al., 2016 [7] Left thoracotomy with suture ligation Selective ligation of obtuse marginal branches Acellular Guest-host hydrogels; Dual-crosslinking hydrogels Open; Intramyocardial
Spaulding, K.A et al., 2020 [9] Left thoracotomy with suture ligation LAD and its diagonal branches Acellular NIPAAm-PEG1500 hydrogel (Sigma-Aldrich, USA) Open; Intramyocardial
Takehara, N et al., 2008 [27] 90 min intracoronary balloon occlusion, followed by reperfusion LAD bFGF (Kaken Pharmaceutical
Co., Tokyo, Japan)		 Gelatin hydrogel Open; Intramyocardial
Vu, T.D et al., 2011 [11] Left thoracotomy with suture ligation Proximal LCx Platelet-rich plasma Hyaluronate Gelatin (Glycosan BioSystems Inc, Salt Lake City, UT, USA) Open; Intramyocardial
Traverse, J.H et al., 2019 [12] Patients with 1st STEMI treated by PCI within past 60 days to 3 years with moderate LV dysfunction. − Acellular VentriGelTM—ECM from decellularized porcine myocardium Transcatheter delivery through endocardium into myocardium
LCx: Left Cirumflex Artery; CAC: Circulating Angiogenic Cells; LAD: Left Anterior Descending Artery; hUMSC: Human Umbilibal Mesenchymal Stem Cell; bFGF: Basic Fibroblast Growth Factor; AGHM: Acidic Gelatin Hydrogel Microspheres; VEGF: Vascular Endothelial Growth Factor; NRG: Neuregulin; HEMA-HA: Hyaluronic Acid Macromers with Hydroxyethyl Methacrylate Group Modification; ELRs: Elastin-like Recombinamers; MSN: Mesoporous Silica Nanoparticles; miR: microRNA; rTIMP-3: Tissue Inhibitors of Metalloproteinase Recombinant Protein; MMP: Matrix Metalloproteinase; CB-MNC: Cord Blood Mononuclear Cells; MeHA: Methacrylated Hyaluronic Acid; IGF-1: Insulin-like Growth Factor 1; HGF: Hepatocyte Growth Factor; UPy: Ureidopyrimidinone; MNCs: Mononuclear Cells; BDNF: Brain-Derived Neurotrophic Factor; NIPAAm: N-Isopropyl Acrylamide; PEG: Polyethylene Glycol.

 

 

2.3. Less Invasive Administration Modes

One of the most important aspects of hydrogel-based myocardial restoration therapy is the mode of delivery. In the context of the increasing role of minimally invasive techniques, a particular emphasis has been placed on shifting away from open heart surgery to catheter-based techniques. We doubt that any restoration method involving major surgical trauma can survive as a stand-alone treatment, as no patient, cardiologist, or surgeon will adopt it. Second, therapy may have to be chronic and repeated (i.e., multiple sessions during the process of time post-MI as HF chronifies). The patient cannot undergo countless re-dos if the procedure is invasive. This has prompted researchers to develop new devices for pinpointing the delivery of therapeutic compounds into a desired area of the myocardium. As a result, catheter-based techniques for myocardial restoration therapy have evolved from simple intracoronary injections (which are far from perfect, due to the rapid washout of an intravascular compound) to techniques with more efficient therapeutic retention. One of the examples is the TransAccess catheter system with fluoroscopic and intravascular ultrasound guidance, which was used for autologous skeletal myoblast delivery [28]. Currently, the most advanced device for intramyocardial delivery of therapeutic compounds is the NOGA system (Figure 2). The latter allows for the performance of 3D electromechanical mapping of the LV in order to identify target zones and perform precise transendocardial injections of therapeutics. Available data and the authors‘ own experience, derived from large animal models, confirm that the NOGA device is safe and highly effective.
Figure 2. The NOGA® system allows visualization of the LV contraction in 3D. NOGA is able to map the heart in a full 360° rotation. (A,C): unipolar voltage maps (mV) and (B,D): regional wall motion maps by local linear shortening (LLS%) can help the electromechanical assessment of the myocardium. NOGA shows viability on the left column; dense scarring is visible at the apex and the antero-septal wall (red); scar area (<0.5 mV) = RED; viable tissue (>1.5 mV) = PURPLE. Comparing the bipolar and unipolar maps, NOGA is able to define border zone areas better.

3. Conclusions

Less Invasive procedures, coupled with injectable compounds, present a valid platform for a translational restoration protocol, which may be adopted by interventional cardiologists and heart surgeons. Polytherapeutic adjuvants, such as antioxidants, paracrine-active drugs, and anti-inflammatory substances, may be added to the protocols to ensure a sustained myocardial restoration effect.
Among all biomaterials currently used in cardiac tissue engineering, injectable hydrogels, with their potential for minimally invasive delivery and in-vivo breakdown into harmless derivatives, represent the most promising therapeutic option. However, the translational pathway from bench to bedside is challenging and still needs to be explored. It can be anticipated that in the next few decades the role of cell-vehicle compounds in the treatment of ischemic HF patients will expand, and injectable hydrogels will penetrate into the clinical arena to a higher extent.

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