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Vernon MJ, Mela P, Dilley RJ, Jansen S, Doyle BJ, Ihdayhid AR, De-Juan-Pardo EM. 3D printing of heart valves. Trends Biotechnol 2024; 42:612-630. [PMID: 38238246 DOI: 10.1016/j.tibtech.2023.11.001] [Citation(s) in RCA: 0] [Impact Index Per Article: 0] [Reference Citation Analysis] [Abstract] [Key Words] [MESH Headings] [Track Full Text] [Journal Information] [Subscribe] [Scholar Register] [Received: 08/31/2023] [Revised: 10/31/2023] [Accepted: 11/01/2023] [Indexed: 05/04/2024]
Abstract
3D printing technologies have the potential to revolutionize the manufacture of heart valves through the ability to create bespoke, complex constructs. In light of recent technological advances, we review the progress made towards 3D printing of heart valves, focusing on studies that have utilised these technologies beyond manufacturing patient-specific moulds. We first overview the key requirements of a heart valve to assess functionality. We then present the 3D printing technologies used to engineer heart valves. By referencing International Organisation for Standardisation (ISO) Standard 5840 (Cardiovascular implants - Cardiac valve prostheses), we provide insight into the achieved functionality of these valves. Overall, 3D printing promises to have a significant positive impact on the creation of artificial heart valves and potentially unlock full complex functionality.
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Affiliation(s)
- Michael J Vernon
- T3mPLATE, Harry Perkins Institute of Medical Research, Queen Elizabeth II Medical Centre and University of Western Australia Centre for Medical Research, The University of Western Australia, Perth, WA 6009, Australia; Vascular Engineering Laboratory, Harry Perkins Institute of Medical Research, Queen Elizabeth II Medical Centre and University of Western Australia Centre for Medical Research, The University of Western Australia, Perth, WA 6009, Australia; School of Engineering, The University of Western Australia, Perth, WA 6009, Australia
| | - Petra Mela
- Medical Materials and Implants, Department of Mechanical Engineering, Munich Institute of Biomedical Engineering and TUM School of Engineering and Design, Technical University of Munich, Boltzmannstrasse 15, 85748 Garching, Germany
| | - Rodney J Dilley
- T3mPLATE, Harry Perkins Institute of Medical Research, Queen Elizabeth II Medical Centre and University of Western Australia Centre for Medical Research, The University of Western Australia, Perth, WA 6009, Australia
| | - Shirley Jansen
- Curtin Medical School, Curtin University, Perth, WA 6102, Australia; School of Medicine, Faculty of Health and Medical Sciences, The University of Western Australia, Perth, WA 6009, Australia; Department of Vascular and Endovascular Surgery, Sir Charles Gairdner Hospital, Perth, WA 6009, Australia; Heart and Vascular Research Institute, Harry Perkins Institute of Medical Research, Perth, WA 6009, Australia
| | - Barry J Doyle
- Vascular Engineering Laboratory, Harry Perkins Institute of Medical Research, Queen Elizabeth II Medical Centre and University of Western Australia Centre for Medical Research, The University of Western Australia, Perth, WA 6009, Australia; School of Engineering, The University of Western Australia, Perth, WA 6009, Australia
| | - Abdul R Ihdayhid
- T3mPLATE, Harry Perkins Institute of Medical Research, Queen Elizabeth II Medical Centre and University of Western Australia Centre for Medical Research, The University of Western Australia, Perth, WA 6009, Australia; Curtin Medical School, Curtin University, Perth, WA 6102, Australia; Department of Cardiology, Fiona Stanley Hospital, Perth, WA 6150, Australia
| | - Elena M De-Juan-Pardo
- T3mPLATE, Harry Perkins Institute of Medical Research, Queen Elizabeth II Medical Centre and University of Western Australia Centre for Medical Research, The University of Western Australia, Perth, WA 6009, Australia; School of Engineering, The University of Western Australia, Perth, WA 6009, Australia; Curtin Medical School, Curtin University, Perth, WA 6102, Australia.
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Eichinger WB, Hettich I, Bleiziffer S, Günzinger R, Hutter A, Bauernschmitt R, Lange R. Intermittent regurgitation caused by incomplete leaflet closure of the Medtronic ADVANTAGE bileaflet heart valve: analysis of the underlying mechanism. J Thorac Cardiovasc Surg 2010; 140:611-6. [PMID: 20117800 DOI: 10.1016/j.jtcvs.2009.11.001] [Citation(s) in RCA: 5] [Impact Index Per Article: 0.4] [Reference Citation Analysis] [Abstract] [Track Full Text] [Journal Information] [Submit a Manuscript] [Subscribe] [Scholar Register] [Received: 04/07/2009] [Revised: 08/28/2009] [Accepted: 11/01/2009] [Indexed: 11/16/2022]
Abstract
OBJECTIVE Clinical echocardiographic assessments of the Medtronic ADVANTAGE (Medtronic Inc, Minneapolis, Minn) prosthesis in the aortic position revealed a phenomenon identified as "intermittent regurgitation." An in vitro investigation was initiated to identify the underlying mechanism. METHODS In a pulse duplicator environment, 6 ADVANTAGE size 23 aortic valves were analyzed. Leaflet motion and flow through the valves were documented using echocardiography with color Doppler flow, digital high speed imaging, and flow meter assessment. RESULTS Intermittent regurgitation could be reproduced in all 6 of the tested valves within limited ranges of flow, pressure, and valve orientation. By virtue of high-speed imaging, the mechanism underlying intermittent regurgitation was identified. During intermittent regurgitation, the leading edge of the second-to-close leaflet makes contact with the chamfer on the leading edge of the first-to-close leaflet. The fluid closing forces working on the first-to-close leaflet prevent it from shifting back so that the leading edge of the second-to-close leaflet remains positioned against the chamfer of the first-to-close leaflet. In this position, the major radius of the second-to-close leaflet does not reach the housing's major radius. Therefore, a crescent-shaped gap remains between the leaflet tip of the second-to-close leaflet and the housing major radius during all or part of diastole. The regurgitant fraction can increase from a normal range of 6% to 25% during an intermittent regurgitation beat. CONCLUSIONS In vitro intermittent regurgitation can be induced in the size 23 aortic ADVANTAGE valve under a limited range of conditions. To avoid possible misinterpretations, the phenomenon must be known in detail by all physicians dealing with patients with an ADVANTAGE valve.
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Affiliation(s)
- Walter B Eichinger
- German Heart Center Munich, Department of Cardiovascular Surgery, Munich, Germany
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