Review Special Issues

An insight into the biomaterials used in craniofacial tissue engineering inclusive of regenerative dentistry

  • Received: 03 April 2023 Revised: 18 May 2023 Accepted: 19 May 2023 Published: 02 June 2023
  • Craniofacial tissue-engineered techniques have significantly improved over the past 20 years as a result of developments in engineering and in material science. The regeneration of the craniofacial tissue is frequently complicated due to the craniofacial region's complexity, which includes bone, cartilage, soft tissue, and neurovascular bundles. It is now possible to construct tissues in the lab using scaffolds, cells, and physiologically active chemicals. For bone repair/augmentation, the biomaterials are classified into natural like “collagen, fibrin, alginate, silk, hyaluronate, chitosan” and synthetic like “polyethyleneglycol, poly-e-caprolactone, polyglycolic acid” and some bioceramics “tricalcium phosphate, hydroxyapatite, biphasic calcium phosphate, and the bioactive glasses” along with metals certain (Titanium and Zirconia ) and as this is part of advanced tissue engineering in dentistry there are some bioactive restorative materials like mineral trioxide aggregate and biodentine. The newer advanced techniques like 3D printed templates present a framework for achieving the three pillars of tissue engineering: healing, rebuilding and rejuvenation. The field of tissue engineering has recently become interested in 3D printing, also known as “Additive Manufacturing”, which is a ground-breaking technique that allows for the printing of patient-specific scaffolds, medical devices, multiscale, biomimetic/intricate cytoarchitecture/function-structure hierarchies and multicellular tissues in complex microenvironments. Biopolymers use is dependent on meeting the criteria for various scaffolds, including mechanical integrity, thermal stability, chemical composition, along with biological properties. Researchers have developed a revolutionary 4D bioprinting technique using cell traction forces and they are used to develop intricate dynamic structures, smart medical devices, or complex human organs.

    Citation: Tanishka Taori, Anjali Borle, Shefali Maheshwari, Amit Reche. An insight into the biomaterials used in craniofacial tissue engineering inclusive of regenerative dentistry[J]. AIMS Bioengineering, 2023, 10(2): 153-174. doi: 10.3934/bioeng.2023011

    Related Papers:

    [1] Xiaohang Su, Peng Liu, Haoran Jiang, Xinyu Yu . Neighbor event-triggered adaptive distributed control for multiagent systems with dead-zone inputs. AIMS Mathematics, 2024, 9(4): 10031-10049. doi: 10.3934/math.2024491
    [2] Wei Zhao, Lei Liu, Yan-Jun Liu . Adaptive neural network control for nonlinear state constrained systems with unknown dead-zones input. AIMS Mathematics, 2020, 5(5): 4065-4084. doi: 10.3934/math.2020261
    [3] Shihua Zhang, Xiaohui Qi, Sen Yang . A cascade dead-zone extended state observer for a class of systems with measurement noise. AIMS Mathematics, 2023, 8(6): 14300-14320. doi: 10.3934/math.2023732
    [4] Hadil Alhazmi, Mohamed Kharrat . Echo state network-based adaptive control for nonstrict-feedback nonlinear systems with input dead-zone and external disturbance. AIMS Mathematics, 2024, 9(8): 20742-20762. doi: 10.3934/math.20241008
    [5] Giovanni G. Soares, Ernesto Estrada . Navigational bottlenecks in nonconservative diffusion dynamics on networks. AIMS Mathematics, 2024, 9(9): 24297-24325. doi: 10.3934/math.20241182
    [6] Guijun Xing, Huatao Chen, Zahra S. Aghayan, Jingfei Jiang, Juan L. G. Guirao . Tracking control for a class of fractional order uncertain systems with time-delay based on composite nonlinear feedback control. AIMS Mathematics, 2024, 9(5): 13058-13076. doi: 10.3934/math.2024637
    [7] Miao Xiao, Zhe Lin, Qian Jiang, Dingcheng Yang, Xiongfeng Deng . Neural network-based adaptive finite-time tracking control for multiple inputs uncertain nonlinear systems with positive odd integer powers and unknown multiple faults. AIMS Mathematics, 2025, 10(3): 4819-4841. doi: 10.3934/math.2025221
    [8] Le You, Chuandong Li, Xiaoyu Zhang, Zhilong He . Edge event-triggered control and state-constraint impulsive consensus for nonlinear multi-agent systems. AIMS Mathematics, 2020, 5(5): 4151-4167. doi: 10.3934/math.2020266
    [9] Fang Zhu, Pengtong Li . Adaptive fuzzy consensus tracking control of multi-agent systems with predefined time. AIMS Mathematics, 2025, 10(3): 5307-5331. doi: 10.3934/math.2025245
    [10] Mohsen Bakouri, Abdullah Alqarni, Sultan Alanazi, Ahmad Alassaf, Ibrahim AlMohimeed, Mohamed Abdelkader Aboamer, Tareq Alqahtani . Robust dynamic control algorithm for uncertain powered wheelchairs based on sliding neural network approach. AIMS Mathematics, 2023, 8(11): 26821-26839. doi: 10.3934/math.20231373
  • Craniofacial tissue-engineered techniques have significantly improved over the past 20 years as a result of developments in engineering and in material science. The regeneration of the craniofacial tissue is frequently complicated due to the craniofacial region's complexity, which includes bone, cartilage, soft tissue, and neurovascular bundles. It is now possible to construct tissues in the lab using scaffolds, cells, and physiologically active chemicals. For bone repair/augmentation, the biomaterials are classified into natural like “collagen, fibrin, alginate, silk, hyaluronate, chitosan” and synthetic like “polyethyleneglycol, poly-e-caprolactone, polyglycolic acid” and some bioceramics “tricalcium phosphate, hydroxyapatite, biphasic calcium phosphate, and the bioactive glasses” along with metals certain (Titanium and Zirconia ) and as this is part of advanced tissue engineering in dentistry there are some bioactive restorative materials like mineral trioxide aggregate and biodentine. The newer advanced techniques like 3D printed templates present a framework for achieving the three pillars of tissue engineering: healing, rebuilding and rejuvenation. The field of tissue engineering has recently become interested in 3D printing, also known as “Additive Manufacturing”, which is a ground-breaking technique that allows for the printing of patient-specific scaffolds, medical devices, multiscale, biomimetic/intricate cytoarchitecture/function-structure hierarchies and multicellular tissues in complex microenvironments. Biopolymers use is dependent on meeting the criteria for various scaffolds, including mechanical integrity, thermal stability, chemical composition, along with biological properties. Researchers have developed a revolutionary 4D bioprinting technique using cell traction forces and they are used to develop intricate dynamic structures, smart medical devices, or complex human organs.


    Abbreviations

    3D/3DP:

    Three-Dimensional printing; 

    CAD:

    computer-aided design; 

    AM:

    additive manufacturing; 

    3DP:

    three-dimensional printing; 

    SFF:

    solid freeform fabrication; 

    TE:

    tissue engineering; 

    CCTP:

    collagen, chitosan and tricalcium phosphate; 

    PLGA:

    Poly Lactic-co Glycolic acid; 

    GAG:

    glycosaminoglycan; 

    CaP:

    Calcium Phosphate; 

    HA:

    Hydroxyapatite; 

    MSC:

    Mesenchymal Stem Cell; 

    CS:

    Chitosan; 

    TCP:

    Tricalcium Phosphate; 

    BMP:

    Bone Morphogenetic protein; 

    SF:

    Silk Fibroin; 

    PBS:

    phosphate-buffered saline; 

    HFIP:

    hexafluoroisopropano; 

    NFRCs:

    natural fibers reinforced composites; 

    CNC:

    Cellulose nanocrystal; 

    NFC:

    Nano fibrillated Cellulose; 

    BNC:

    Bacterial nanocellulose; 

    PEG:

    Polyethyleneglycol; 

    PCL:

    Poly-E-Caprolactone; 

    PGA:

    Polyglycolic Acid; 

    BCP:

    Bicalcium Phosphate; 

    Ti:

    Titanium; 

    Al:

    Aluminium; 

    V:

    Vanadium; 

    PEKK:

    Polyetherketoneketone; 

    HEA:

    High entrophy alloys; 

    LC:

    Laser cladding; 

    LAAM:

    Laser-aided additive manufacturing; 

    LC-HEACs:

    Laser-cladded high-entropy alloy coatings; 

    BAG:

    Bioactive glass; 

    SiO2:

    Silicon Dioxide; 

    Na2O:

    Sodium Dioxide; 

    CaO:

    Calcium Oxide; 

    P2O5:

    Phosphorus Pentaoxide; 

    PEEK:

    polyetheretherketone; 

    PAEK:

    polyaryletherketone; 

    BTR:

    Bone tissue regeneration; 

    RM:

    Regenerative Medicine; 

    SMPs:

    Shape Memory Polymers; 

    SMAs:

    Shape Memory Alloys; 

    PVA:

    Polyvinyl Alcohol

    The non-stationary Stokes and Navier-Stokes equations are the cornerstone of fluid mechanics and have been widely applied in numerous engineering fields. The non-stationary Stokes equations serve as an abridged form of the Navier-Stokes equations, and their numerical solutions are indispensable for fluid dynamics design and analysis in engineering environments.

    The finite volume element method (FVEM) is a powerful numerical method widely employed for tackling partial differential equations (PDEs) encountered in fluid dynamics, heat conduction, and various other disciplines dealing with continuous materials. Its capacity to preserve local conservation laws, adapt to complex geometries, and provide accurate and efficient results has earned it popularity among researchers and engineers. Additionally known as the finite volume method [1, 2], the control volume method, the mixed co-volume method [3, 4], the box method [5, 6], or the first-order generalized difference method [7], the FVEM is also recognized as a variant of the control volume finite element (CVFE) method without overlapping control volumes [8, 9, 10]. Essentially, the FVEM can be regarded as a numerical solution method that bridges the finite element method (FEM) and the finite difference method (FDM). In the past two decades, significant progress has been made in the application of FVEMs to solving the Stokes and Navier-Stokes equations. The rapid development of FVEMs has resulted in a wealth of research achievements, especially with a significant focus on theoretical aspects such as stability and convergence, as described in [11]. However, there is a significant gap in theoretical analysis compared to the extensive theoretical research of FEMs. This paper will theoretically discuss the stability and error estimation of a fully discrete spatial-temporal FVEM scheme for solving non-stationary incompressible Stokes equations.

    Currently, the research focus on solving non-stationary Stokes equations using FVEMs is mainly on the adoption of spatially low-order finite volume techniques. These techniques approximate the velocity in the Stokes equations using piecewise linear polynomial functions. This preference arises from the lower computational complexity of low-order methods, which is beneficial for theoretical research, easy to implement, and thus enhances their attractiveness to researchers and professionals. The paper [12] proposed a semi-discrete FVEM scheme for the spatial discretization of the non-stationary Stokes equations, utilizing the P1P0 macro-element. By employing a post-processing technique, this method enhances the convergence order for the H1 norm of the velocity and improves the L2 norm accuracy of the pressure. The paper [13] established the optimal estimates for a low-order spatial-temporal fully discrete method for the non-stationary Navier-Stokes equations. It uses a semi-implicit Euler method for time and a special finite volume scheme for space, with the P1P0 trial function pair for spatial discretization and macro elements for stability. A low-order semi-discrete scheme for non-stationary Navier-Stokes equations was presented in [14], followed by a new fully discrete FVEM scheme using macroelements. Error estimates for the FVEM solutions were obtained via standard FEM techniques. Utilizing the lowest equal-order finite element space pairs, based on two local Gauss integrals, the paper [15] constructed a stabilized FVEM scheme for the transient Stokes equations. In this approach, both the velocity and pressure were approximated with piecewise linear polynomial functions, and this paper achieved the optimal error estimates in the H1 norm for the velocity and in the L2 norm for the pressure. In [16], a stabilized FVEM scheme for transient Navier-Stokes equations was presented, which maintains conservation and yields optimal velocity and pressure estimates through error analysis derived from the FVEM scheme. This scheme offers convergence similar to the stabilized linear FEM under the same solution regularity and source term conditions. For a more in-depth understanding of solving incompressible flow problems using the FVEM, readers can refer to the latest relevant research literature on FVEM studies.

    According to our current understanding, there is a clear lack of research literature regarding the application of spatially high-order FVEMs to study non-stationary Stokes or Navier-Stokes equations. In this work, we propose a full-discrete scheme where the spatial discretization employs quadratic FVEM for velocity and discontinuous piecewise linear elements for pressure, coupled with a first-order temporal discretization. As widely recognized, the quadratic FVEM for velocity approximation offers distinct advantages over lower-order spatial methods, such as offering more precise discrete velocity solutions, especially when dealing with smooth situations or high-precision requirements. Compared to linear methods, the quadratic methods also converge faster to the actual solution, which is very helpful for dealing with complex geometries or boundary conditions. Consequently, developing a fully discrete FVEM that employs quadratic polynomials to approximate velocity in the non-stationary Stokes equations, and performing theoretical analysis on its stability and error estimates, holds significant theoretical importance and practical utility.

    As is well known, the continuity equation for incompressible fluids is generally considered to embody the law of mass conservation for fluid velocities. The Hood-Taylor finite element space pairs are extensively applied in the numerical solution of the Stokes equations, and their theoretical foundations have been thoroughly investigated in numerous scholarly works [17, 18]. Nonetheless, the Hood-Taylor finite element space pairs are typically based on continuous pressure spaces, which can only weakly ensure the mass conservation of discrete velocity solutions on the whole domain. In contrast, the use of discontinuous pressure spaces can lead to local mass conservation for discrete velocity solutions, as they could ensure theoretically that the average of the divergence is zero within each individual element. To guarantee the local mass conservation of the discrete velocity solution, many research efforts have adopted a modification of the Hood-Taylor finite element space pairs as the approximation spaces for the velocity and pressure components in the Stokes equations. A distinguishing feature of this modification is the addition of piecewise constant functions in the continuous pressure space. This idea was first introduced in [19], and the stability of these methods has been demonstrated in subsequent studies by [20, 21]. The LC finite element space pair [22, 23] happens to be a modification of the lowest-order Hood-Taylor finite element space pair, and it was originally designed to cater to the FEMs for solving stationary Stokes problems. This paper will employ the LC element to approximate the velocity and pressure in the Stokes equations so that the proposed FVEM scheme would be classified as a pressure-robust method [24]. This selection constitutes the major distinction between the current work and the paper [25], who employed the lowest-order classical Hood-Taylor finite element space pairs to deal with the velocity-pressure pairs of the Stokes problem. Therefore, these two FVEM schemes exhibit significant differences in their stability analysis. Specifically, for the Taylor-Hood elements, the equivalence of bilinear forms derived from gradient and divergence operators is generally valid in any dual partition of the test space with respect to the velocity, while for the LC elements, equivalence requires careful design of the dual partition of the test space with respect to the velocity to ensure the stability of the FVEM scheme. It is observed that in the FVEM scheme using the LC element, the velocity is approximated with a continuous piecewise quadratic polynomial, while the pressure is approximated using a discontinuous piecewise linear polynomial on the same meshes. This implies that the divergence of the discrete velocity solutions lies within the discontinuous pressure space, and thus it can be inferred that the integral average of the divergence of the discrete velocity solution in the FVEM over each element will vanish. This property inherently guarantees the local mass conservation property of the discrete velocity solutions, preserving the original physical characteristics of incompressible fluid flows [26, 27]. Thus, the proposed FVEM scheme is demonstrated to be a stable and local mass conservation numerical method on the barycenter-refined triangular meshes. This is one of the primary contributions of this paper.

    We note that, despite paper [28] employing the discontinuous finite element spaces as the trial spaces for the FVEM in solving the Stokes equations with respect to velocity and pressure, the stability and convergence analysis relies on an interior penalty term. In spite of the analysis in paper [29], which considered the mixed FVEM for the Stokes problem on triangular meshes, utilizing the MINI element for the velocity-pressure trial spaces and piecewise constant functions for the test spaces, the proposed scheme is classified as a low-order numerical method.

    The mapping, which connects the trial space of FVEMs with their test spaces, plays a crucial role in the stability analysis of the FVEMs. Many studies are now focused on introducing novel mappings to check the stability of these methods. To investigate the stability and error estimates for the space of the fully discrete FVEM scheme, we employ the one-to-many mapping identified in the literatures [30, 31, 32]. This technique results in the FVEM scheme, when equipped with this mapping, being equivalent to the conventional FVEM scheme that does not utilize such a mapping. In this paper, we first propose a semi-discrete first-order temporal scheme for the non-stationary Stokes equations, and then derive a fully discrete FVEM scheme by starting directly from the semi-discrete temporal scheme, utilizing the FVEM based on dual partitions for spatial discretization. The reason we are compelled to develop the semi-discrete scheme for time before achieving the fully discrete spatial-temporal FVEM scheme is due to the fact that the introduced one-to-many mapping differs from the conventional one-to-one mapping and it does not possess the self-adjoint property with respect to the L2 inner product. By introducing the one-to-many mapping and utilizing classical finite element analysis techniques, the theoretical analysis of the existence, uniqueness, and error estimation of the fully discrete FVEM solution has been derived in this paper.

    The plan of this article is as follows. In the next section, we will introduce the non-stationary Stokes equations and establish their variational forms. Then, in Section 3, a semi-discrete scheme for the non-stationary Stokes equations with respect to time is provided. Section 4 proposes the fully discrete FVEM scheme for the non-stationary Stokes equations and proves its stability. Section 5 gives the optimal order estimate of the scheme. Finally, Section 6 provides numerical experiments to verify the obtained theoretical results, and the last section gives the conclusion of this paper.

    In this section, we will discuss the non-stationary Stokes equations and present their classical variational formulations.

    In the context of a bounded and connected domain ΩR2, characterized by a boundary Ω that is Lipschitz continuous, we consider the following incompressible, time-dependent Stokes equations, which are subject to homogeneous boundary conditions. We seek to determine the velocity u and the pressure p for all T>0 such that

    {utμΔu+p=f,for all (x,t)Ω×(0,T],divu=0,for all (x,t)Ω×(0,T],u(x,t)=0,for all (x,t)Ω×(0,T],u(x,0)=u0(x),for all xΩ. (2.1)

    Here, u(x,t)=(u1(x,t),u2(x,t)) denotes the velocity vector of the fluid, p(x,t) represents the pressure, T is the duration of the time interval, f(x,t) is the prescribed body force, u0(x) is the initial velocity distribution, μ is the coefficient of viscosity, and ut=ut signifies the partial derivative of the velocity with respect to time.

    We now present the variational form for the problem (2.1). For any subdomain DΩ and any integer r0, we use (,)D to represent the L2(D) inner product, r,D for the Hr(D) norm, and ||r,D for the Hr(D) semi-norm. When D=Ω, the subscript D is omitted for clarity. We define L20(Ω) as the set of functions p in L2(Ω) with the property that Ωpdx=0, H10(Ω) as the set of functions v in H1(Ω) that vanish on the boundary Ω, and Hr(Ω) as the square of the Sobolev space Hr(Ω). The standard variational form for addressing the problem (2.1) is given by: Find (u(t),p(t))(H10(Ω),L20(Ω)) for all t(0,T] such that

    {(ut,v)+a(u,v)b(v,p)=(f,v),for all vH10(Ω),b(u,q)=0,for all qL20(Ω),u(x,0)=u0(x),for all xΩ, (2.2)

    where a(u,v)=μ(u,v) and b(u,p)=(p,divu). It is a well-established fact that the problem (2.1) is valid for sufficiently smooth solutions u and p if and only if the variational form (2.2) holds for almost every t(0,T].

    In this paper, we will employ C and c as arbitrary positive constants, whose values are determined by the data (μ,T,u0,Ω) and may vary in different situations. We assume that the initial velocity u0(x) and the body force f(x,t) in (2.1) are sufficiently smooth and compatible to fulfill the following conditions:

    u02+sup0<tT(f0+ft0)C. (2.3)

    Furthermore, we ensure that, as in [33, 34], for any arbitrary T>0, there exists a unique solution pair (u,p) for the problem (2.1) that has the following regularity requirements:

    sup0<tT(u22+p21)C, sup0<tTτ(t)ut21+T0τ(t)(ut22+pt21+utt20)dtC, (2.4)

    with τ(t)=min{1,t}. These estimates (2.3) and (2.4) will serve as the foundation for the theoretical analysis presented in the subsequent sections.

    We remark that the bilinear form a(,) possesses the following properties:

    a(u,u)=μ|u|21,a(u,v)μ|u|1|v|1

    for all u,vH10(Ω). Additionally, the bilinear form b(,) satisfies the infsup stability condition [35]

    supvH10(Ω)b(v,q)|v|1cq0,  for all qL20(Ω). (2.5)

    For any uH10(Ω), the Poincaré inequality implies the following inequalities:

    u0u1C|u|1.

    These inequalities will be recurrently employed in the subsequent discussion.

    In this section, we will present a semi-discrete variational scheme about time for problem (2.1), and then examine its stability properties and derive error estimates.

    We next introduce the semi-discrete temporal scheme. Given a positive integer M1, we define the time increment as Δt=TM, and denote un as the semi-discrete approximation of u at the time point tn=nΔt. The approximation of the temporal derivative ut is given by

    dtun=unun1Δt,

    where nZM and ZM:={1,2,,M}. We define fn=f(x,tn), which represents the value of f(x,t) at the time tn due to the smoothness of the body force f. The semi-discrete temporal scheme reads as follows: For any t(0,T], find (un,pn)(H10(Ω),L20(Ω)), nZM, such that

    {(dtun,v)+a(un,v)b(v,pn)=(fn,v),for all vH10(Ω),b(un,q)=0,for all qL20(Ω),u(x,0)=u0(x),for all xΩ. (3.1)

    The following theorem holds for the semi-discrete scheme (3.1). To clarify our main points, the proof has been moved to Appendix A.

    Theorem 1. If u0H10(Ω) and fL2(Ω) for any t(0,T], then the semi-discrete scheme (3.1) has a unique sequence of solutions (un,pn)(H10(Ω),L20(Ω)), nZM, which satisfies the following stability conditions:

    un20+μΔtni=1|ui|21u020+μ1Δtni=1fi20,Δtni=1pi20C(u021+μ1Δtni=1fi20),

    with C being a constant that is independent of the parameter Δt.

    This theorem indicates the temporal stability of the proposed semi-discrete scheme (3.1).

    Next we examine the error estimates for the semi-discrete scheme presented in (3.1). For any time point t(0,T], Taylor's theorem provides the following expansion:

    u(t)=u(tn)+ut(tn)(ttn)+12ttnutt(s)(ts)2ds,

    which combining the time step Δt=tntn1, where nZM, derives the following expression for ut(tn):

    ut(tn)=u(tn)u(tn1)Δt12Δttntn1utt(t)(ttn1)2dt. (3.2)

    By employing similar methods as in [34], it can be proven that the solution to the scheme (3.1) satisfies the following theorem. To clarify our main points, the proof has been moved to Appendix B.

    Theorem 2. Let (u,p)(H10(Ω),L20(Ω)) denote the solution pair for the problem (2.1) at any time t(0,T], and the solution pair (un,pn)(H10(Ω),L20(Ω)) results from the semi-discrete scheme (3.1) for all nZM. If u0H10(Ω) and fL2(Ω) for every t(0,T], then the following error estimates are valid:

    u(tn)un20+ni=1μΔt|u(ti)ui|21CΔt2,ni=1p(ti)pi20CΔt,           

    where C represents a constant that is independent of the discretization parameter Δt.

    The theorem provides an error estimation of the convergence order of the semi-discrete scheme (3.1) about time, and the theoretical result of this theorem may not be the optimal convergence order about time. The primary focus of this paper is to analyze the stability and convergence order of the FVEM scheme using the LC element in the spatial discretization for solving non-stationary Stokes equations.

    In this section, we will present a fully discrete spatial-temporal FVEM scheme for the time-dependent Stokes problem as stated in (2.1), and examine its stability.

    To elucidate the construction of the FVEM scheme, we first present the primary partition T and its associated dual partition T for the domain Ω. In this paper, we utilize a distinctive triangular mesh as the primary partition T. We define TM={M} as a macro-element partition of the polygonal region Ω, with each macro-element being a triangle, as shown in Figure 1. This indicates that the polygonal domain Ω is divided into a finite number of macro triangles. Then the primary partition T={K} is derived by subdividing each macro triangle MTM into three smaller triangles KT, in the spirit of connecting the vertices of the macro triangle to its barycenter, as illustrated in Figure 2. The meshes generated by T are termed barycenter-refined triangular meshes. In numerous studies, including the references [36, 37, 38], the primary partition T is alternatively referred to as the Clough-Tocher refinement of the macro-element partition TM. It is evident that the smaller triangles KT are nested within the macro triangle MTM, and the collective union of all these smaller triangles constitutes the primary partition T of the domain Ω. We denote by hK the diameter of the element K and by ρK the diameter of the largest ball contained in K, and set h:=maxKThK. Let T={T} be a family of the triangulations of Ω, and assume the family of primary partitions T={T} to be a regular triangulation. For such triangulations, there exits a constant σ>1 such that hKσρK, for all KT, TT. For a subset DR2, the notation Pr(D) refers to the set of all polynomials of degree at most r defined on D. The trial space UT for the velocity is selected to be a quadratic conforming finite element space, which is defined as follows:

    UT={u=(u1,u2):uiUT, iZ2},
    Figure 1.  Macro-element partition TM for Ω.
    Figure 2.  Primary partition T for Ω.

    where UT={u:uH10(Ω)C(Ω),u|KP2(K), for all KT}. This implies that the velocity is approximated using continuous piecewise quadratic polynomial functions.

    We then present the dual partition T:={K} associated with the primary partitions T. In the context of a triangle K=ΔP1P2P3, we identify the three midpoints as P4, P5, and P6, and the barycenter as P0, as depicted in Figure 3. To delineate the dual elements, we define the mesh parameters α(0,12) and β(0,23). For any distinct indices m and n with m,nN3, we denote the point Pαm,n on the boundary ¯PmPn such that |¯PmPαm,n|=α|¯PmPn|. The point Pβm,m+3, where mN3, is defined as the point on the midline ¯PmPm+3 such that |¯PmPβm,m+3|=β|¯PmPm+3|. By connecting the points Pβm,m+3 to the barycenter P0 and joining the points Pβm,m+3 with Pαm,n for all m,nN3 where mn, using straight lines, we construct the dual partition of K as illustrated in Figure 3. Consequently, the dual partitions T={K} of the domain Ω are formed by the dual partitions of all elements KT.

    Figure 3.  Dual partition for ΔP1P2P3.

    In light of the dual partitions T of the domain Ω, the test space UT associated with the velocity is defined as follows:

    UT={v=(v1,v2):viUT, iZ2},

    with the definition of UT:=span{χK:KT} where χE represents the scalar characteristic function defined on the dual element ET. The variations of the mesh parameters α and β lead to a distinct FVEM scheme. In our discussion, we choose α(16,12) and β=116α. It is evident that β(0,23).

    We define the trial and test spaces for the pressure as QTL20(Ω) and by

    QT={p:pL20(Ω),p|KP1(K),for all KT}.

    Specifically, the pressure space QT is defined as follows, as described in [22, 23, 26]:

    QT={pL20(Ω):p=p0+p1,where p1C(Ω),p1|KP1(K),and p0|KP0(K),KT}.

    This space is characterized by augmenting the continuous linear space with piecewise constant functions within each element of the partition T, and thus it can be seen as composed of discontinuous piecewise linear polynomial functions defined on each element KT, thereby ensuring that the divergence of the trial space for the velocity remains a subspace of it. This contrasts with the selection of the pressure space QT presented in [25].

    The finite element space pair (UT,QT) is referred to as the LC finite element space pair, and the space QT defined above is called the continuous linear plus constant pressure element, as noted in [22, 23]. Observe that the primary partition TT is constructed by joining the vertices and barycenter of every macro triangle UTM. It is documented in references [22, 23] that the spaces UT and QT satisfy the following discrete infsup inequality:

    cq0supvUTb(v,q)|v|1,  for all qQT, (4.1)

    with c being a constant that is invariant with respect to the mesh size h and the time step Δt.

    Next, we present the fully discrete scheme for the problem as stated in (2.1). For all (u,p)(UT,QT) and (v,q)(UT,QT), we define the following discrete bilinear forms:

    aT(u,v)=KTKT(KintKuvdxKintKv(nu)ds),bT(v,p)=KTKT(KintKpvndsKintKpdivvdx),dT(u,q)=KT(KqundsKuqdx), (4.2)

    where intK refers to the interior region of the element K, and n represents the outward-pointing unit normal vector on the boundary K or K. Let Πh be the interpolation projection that maps functions from the space H1(Ω) onto the finite element space UT, and Γh serves as the interpolation projection from the space L20(Ω) to the finite element space QT. Given that the family of primary partitions T={T} is regular, the interpolation theory on finite element spaces guarantees the following inequalities. For any wH3(Ω), m{0,1}, we have

    wΠhwmCh3mw3.

    Similarly, for any qH2(Ω), m{0,1}, the inequality

    qΓhqmCh2mq2

    holds. We now suggest a fully discrete FVEM scheme for the problem defined in (2.1), which is formulated as follows: Find (unh,pnh)(UT,QT) for all nZM such that it satisfies the following conditions:

    {(dtunh,v)+aT(unh,v)+bT(v,pnh)=(fn,v),  for all vUT,dT(unh,q)=0,  for all qQT,u0h=Πhu(x,0),  for all xΩ, (4.3)

    where fn represents the value of the function f(x,t) at the time point tn.

    We remark that the velocity trial space UT is defined as the continuous piecewise quadratic finite element space, while the pressure trial space QT is defined as the sum of a continuous piecewise linear finite element space and a local constant function space, and this characterization explicitly clarifies its inherent discontinuity. This ensures that the divergence of UT is contained within QT. As a result, the discrete velocity solution derived from (4.3) is provided with the property that the integral average of the divergence over each element will automatically vanish. Consequently, the scheme presented in (4.3) is guaranteeing local mass conservation of the discrete velocity within each element KT and the pressure-robustness. In other words, any modifications to the function f(x,t) at the right end of the problem (2.1) that solely impact the pressure will only influence the variation of the discrete pressure solution in (4.3).

    We find that the mapping from the trial space UT to the test space UT can facilitate the theoretical analysis of the FVEM scheme. We now present the mapping ΠT:UTUT that is discussed in [25]. For any vUT, the mapping ΠT is defined such that for each vertex Pi of K, iN3,

    ΠTv(Pi)=v(Pi),

    and for each interior midpoint Mi,j of K, i, jN3 with i<j,

    ΠTv(Mi,j)=ωv(Mi,j)+1ω2(v(Pi)+v(Pj)),

    with ω being a non-zero constant. The specific relationships between the nodal points are depicted in Figure 3, with M1,2=P6, M1,3=P5, and M2,3=P4. The mapping ΠT can be constructed from the linear mappings ΠT defined on each element KT. For any non-zero real number ω, it can be readily demonstrated that ΠT is a linear invertible mapping from the space UT onto UT.

    By employing the linear invertible mapping ΠT as previously defined, for any non-zero coefficient ωR, the fully discrete FVEM scheme (4.3) for the problem given in (2.1) is equivalent to the following formulation. Find (unh,pnh)(UT,QT), where nZM, satisfying

    {(dtunh,ΠTv)+aT(unh,ΠTv)+bT(ΠTv,pnh)=(fn,ΠTv),  for all vUT,dT(unh,q)=0,  for all qQT,u0h=Πhu(x,0),  for all xΩ, (4.4)

    with the notation ΠTw:=(ΠTw1,ΠTw2) for any vector w:=(w1,w2)UT.

    We will now examine the stability of the fully discrete scheme presented in (4.4). This scheme must satisfy the abstract theories of generalized saddle-point problems as outlined in [39, 40]. To facilitate this analysis, we select the mapping coefficient ω as ω=113αβ in the subsequent discussion. It is important to note that the mesh parameters are defined as β=116α, where α(16,12). This choice results in ω=216α. From the references [25, 41], it can be seen that the choice of mapping coefficient ω does not affect the numerical solution of the FVEM scheme.

    We define a block matrix A as follows:

    A=(Iω0E0ωI), (4.5)

    where ω0=1ω2, E=1I, I is the 3×3 identity matrix, and 1 is a 3×3 matrix with all entries equal to 1. By employing proof techniques similar to those in references [25, 42], the following conclusion can be obtained.

    Lemma 1. For all vP2(K) and uP0(K), the following equations hold for any KT:

    (u,ΠTv)K=(u,v)K, (4.6)

    and

    (u,ΠTv)K=(u,v)K. (4.7)

    As a direct result of Lemma 1, we derive the following proposition.

    Proposition 1. For all uUT and vUT, and for all qQT, the following equations hold:

    bT(ΠTv,q)=dT(v,q)=b(v,q). (4.8)

    Proof. Note that the space QT is the discontinuous function space. According to the definition of bT(,), for any vUT and qQT, we have

    bT(ΠTv,q)=KTKTKintKq(ΠTv)ndsKTKTKintKq(ΠTv)dx.

    Since ΠTvUT and UT consists of piecewise constant functions, it follows that

    KTKTKintKq(ΠTv)dx=0,

    which simplifies the bilinear form bT(,) to

    bT(ΠTv,q)=KTKTKintKq(ΠTv)nds+KTKTKintKq(ΠTv)ndsKTKTKintKq(ΠTv)nds.

    Applying Green's formulae to the above expression results in

    bT(ΠTv,q)=KTKq(ΠTv)dxKTKTKintKq(ΠTv)nds=KT(Kq(ΠTv)dxKq(ΠTv)nds).

    From the definition of dT(,), it is confirmed that for any vUT and qQT,

    bT(ΠTv,q)+dT(v,q)=KTKq(ΠTvv)dxKTKq(ΠTvv)nds. (4.9)

    Given that for any KT, q|KP1(K), q|K(P0(K),P0(K)), and v|K(P2(K),P2(K)), and using the result of (4.6) in Lemma 1, it is evident that

    Kq(ΠTvv)dx=0.

    Now, let us examine the final term on the right-hand side of (4.9). Due to the discontinuity of qQT on the boundaries of adjacent elements KT, it is typically the case that

    KTKq(ΠTv)nds0,  KTKqvnds0.

    Given that for any qQT, q=q1+q0 with q1C(Ω) and q1|KP1(K), q0|KP0(K) for each KT, we have

    KTKq(ΠTvv)nds=KTKq1(ΠTvv)nds+KTKq0(ΠTvv)nds.

    The fact that q1C(Ω) and the result of (4.7) in Lemma 1 imply

    KTKq1(ΠTvv)nds=0,  Kq0(ΠTvv)nds=0.

    This shows that for any vUT and qQT,

    KTKq(ΠTvv)nds=0.

    Consequently, it follows that bT(ΠTv,q)+dT(v,q)=0 for any (v,q)(UT,QT), and thus the Eq (4.8) is established.

    Noticing that according to the definitions of the bilinear forms dT(,) and b(,), the verification of the following equation can be readily achieved by applying Green's formulae. That is, it holds for all u,vUT and qQT that

    b(v,q)=dT(v,q).

    This completes the proof of the proposition.

    Proposition 1 elucidates that the discrete bilinear forms bT(ΠT,) and dT(,) in the FVEM scheme with an LC element are equivalent to those in the FEMs when the mapping coefficient is set to ω=113αβ, with β=116α. It is important to note that although the conclusion of Proposition 1 is consistent with Proposition 5.10 as referenced in [25], the conditions required for these theorems are distinct. This proposition chooses the space QT to be a space of discontinuous pressures.

    We note that the following equalities inherently hold for all (v,q)(UT,QT) when QT is selected as a continuous linear finite element space, that is,

    KTKq(ΠTv)nds=KTKqvnds=0.

    This result has been previously established in [25]. In these conditions, the validity of Eq (4.8) is ensured only by Eq (4.6) from Lemma 1, and thus obviating the need for the restrictive Eq (4.7) which is derived from β=116α. For details, refer to [25]. This implies that when QT is a continuous finite element space, Equation (4.8) can be valid for a broader range of α(0,12) and β(0,23), provided that ω=113αβ.

    From the preceding conclusions, it is evident that for a map coefficient ω defined as ω=113αβ, the fully discrete FVEM scheme for the problem described in (2.1) can be expressed in the following forms: Find (unh,pnh)(UT,QT), where nZM, such that

    {(dtunh,ΠTv)+aT(unh,ΠTv)b(v,pnh)=(fn,ΠTv),  for all vUT,b(unh,q)=0,  for all qQT,u0h=Πhu(x,0),  for all xΩ. (4.10)

    It is important to note that the FVEM scheme (4.3) is fundamentally the same as the FVEM scheme (4.4) when the linear mapping ΠT:UTUT is applied, regardless of any map coefficient ωR. The FVEM scheme (4.10) is a specific instance of the FVEM scheme (4.4) that arises from the choice of ω=113αβ. This implies that the FVEM scheme (4.10) is inherently equivalent to the FVEM scheme (4.3). Given that the discrete velocity solution in (4.10) is the local mass conservation within each element KT, the numerical solution of the FVEM scheme (4.3) also maintains the local mass conservation. Therefore, to investigate the stability of (4.3), it is sufficient to focus on the analysis of (4.10).

    To this end, we need to establish some preliminary conclusions. For the mesh parameters α(0,12) and β(0,23), we define the following expressions:

    a1=216αβ(α2+αβ3α+β23β+3),b1=54αβ(2α2+αβ2α+β22β),a2=108αβ2(α+β),b2=216αβ(α2+αβ2α+β22β),a3=54αβ3+108αβ216,b4=54αβ3216αβ2+40,b3=216α3β162α2β2+432α2β135αβ3+378αβ2324αβ+8,a4=432α3β+324α2β2864α2β+216αβ3432αβ2+136.

    We introduce the matrices

    B=1360(6IE4I4I32I+16E),  C=11296(a1I+b1E  a2I+b2Ea3I+b3E  a4I+b4E),

    where E=1I is a 3×3 matrix as defined in (4.5). For every wUT, we define the norm |||w|||0 as (w,ΠTw)12. This norm ||||||0 can be demonstrated to be equivalent to 0 on the subspace UT.

    Proposition 2. There exist two positive constants c and C such that for all wUT,

    cw0|||w|||0Cw0.

    Proof. To establish the proposition, it is enough to show that there are constants c and C such that for all KT,

    cw20,K|||w|||20,KCw20,K. (4.11)

    For every wUT, we define w restricted to K as the linear combination w|K=6i=1wi,Kφi,K, where φi,K are the basis functions associated with the nodal points Pi on the element K. From the definition of ΠT on each KT, it follows that

    ΠTΦK=AXK.

    Through a direct calculation, we obtain

    |||w|||20,K=wA(KXKΦTKdx)wT=2meas(K)wACwT=2meas(K)wDwT,w20,K=w(KΦKΦTKdx)wT=2meas(K)wBwT,                

    with w=[wi,K,iN6] and D=AC+(AC)T2. Noting that ω=113αβ and β=116α for α(16,12), it is straightforward to confirm that the matrices D and B are positive definite. This guarantees the existence of positive constants c and C that are independent of the mesh size h and the time step Δt, satisfying

    cwTBwwTDwCwTBw

    for all wR6. Consequently, the inequality (4.11) is verified, and the proof of the proposition is complete.

    In this section, we note that the inner product (,ΠT) defined on the mapping ΠT presented in this paper is not self-adjoint in general, unlike the linear FVEMs. Specifically, the equality

    (v,ΠTw)=(w,ΠTv)

    holds if and only if w=vUT. This non-self-adjointness necessitates the development and analysis of semi-discrete temporal schemes for the problem (2.1) before we can proceed to the fully discrete FVEM scheme. Referring to the works of [25, 41], we present the following properties of the mapping ΠT.

    Proposition 3. There exist positive constants c and C such that for all wUT, the following inequalities hold:

    cw0ΠTw0Cw0,wΠTw0Ch|w|1.

    This proposition demonstrates the equivalence between the discrete norms and the error estimates on ΠT.

    It is widely recognized that the coercivity of the bilinear forms aT(,ΠT) as presented in (4.4) is dependent on the geometric characteristics of the primary triangular meshes KT. To streamline our discussion, we shall hereafter assume that the primary partition family T={T} is of shape regularity, ensuring the existence of a positive constant c0 such that

    aT(u,ΠTu)c0μ|u|21,  for all uUT. (4.12)

    Furthermore, as demonstrated in [25, 41], there exists a constant C for all TT such that the following uniform boundness holds:

    aT(u,ΠTv)Cμ|u|1|v|1,   for all u,vUT. (4.13)

    Our theoretical exploration will employ the following discrete Gronwall lemma, as outlined in [43, 44].

    Lemma 2. Consider the nonnegative sequences an, bn, cn, and dn. If they satisfy

    am+τmi=1bnτm1i=0andn+τm1i=0cn+C,  m1,

    then it follows that

    am+τmi=1bnexp(τm1i=0dn)(τm1i=0cn+C),  m1,

    with τ and C being positive constants that are independent of the mesh size h and the time step Δt.

    After the above preparations, we establish the stability of the fully discrete FVEM scheme presented in (4.10).

    Theorem 3. If u0H10(Ω) and fL2(Ω) for all t(0,T], there exists a unique sequence of solutions (unh,pnh)(UT,QT), where nZM, for the fully discrete FVEM scheme (4.10), and the solutions satisfy the following stability conditions:

    unh20+μΔtni=1|uih|21C(u020+Δtμ1ni=1fi20), (4.14)
    Δtni=1pih20C(u021+Δtμ1ni=1fi20), (4.15)

    where C denotes a positive constant that is independent of the mesh size h and the time step Δt.

    Proof. For all (unh,pnh)(UT,QT) and (v,q)(UT,QT), where (UT,QT)(H10(Ω),L20(Ω)), we set

    A(unh,v)=(unh,ΠTv)+ΔtaT(unh,ΠTv),F(v)=(Δtfn+un1h,ΠTv).

    The inequalities (4.12) and (4.13) imply that the discrete bilinear form aT(unh,ΠTv) is uniformly bounded and coercive. Specifically, it satisfies the following conditions:

    aT(unh,ΠTv)Cμ|unh|1|v|1,aT(unh,ΠTunh)c0μ|unh|21.

    The discrete bilinear form b(unh,q) also satisfies the discrete infsup condition (4.1). From Proposition 2 and Proposition 3, we have the following inequalities:

    cunh0|||unh|||0Cunh0,cv0ΠTv0Cv0.

    By applying the same proof technique as in Theorem 1, we can establish the existence of solutions for the FVEM scheme (4.10).

    For the stability estimates, we first demonstrate the estimate (4.14). From the scheme (4.10), we have for all (v,q)(UT,QT),

    (dtunh,ΠTv)+aT(unh,ΠTv)b(v,pnh)+b(unh,q)=(fn,ΠTv).

    By choosing v=unh and q=pnh, we obtain

    |||unh|||20+Δtc0μ|unh|21Δt(fn,ΠTunh)+(un1h,ΠTunh).

    Applying the Cauchy-Schwarz inequality, Poincaré inequality, and Yang's inequality to the right-hand side of the above equation, we get

    |||unh|||20+Δtc0μ|unh|21CΔtfn0unh0+Cun1h0unh0CΔtfn0|unh|1+C|||un1h|||0|||unh|||0CΔtμ1fn20+c02Δtμ|unh|21+12|||unh|||20+C|||un1h|||20.

    From this inequality, we can conclude that

    |||unh|||20+Δtμ|unh|21CΔtμ1fn20+(δ1)|||un1h|||20+|||un1h|||20,

    where δ1 is a positive constant independent of h and Δt. By summing the above inequality from 1 to n and applying the discrete Gronwall lemma, we obtain

    |||unh|||20+μΔtni=1|uih|21|||u0h|||20+CΔtμ1ni=1fi20+Cni=1|||ui1h|||20C(|||u0h|||20+ni=1Δtμ1fi20).

    Noting that for any vUT,

    u0h0=Πhu(x,0)0=Πhu00Cu00  and  cv0|||v|||0Cv0,

    we derive the estimate (4.14) from the above inequalities.

    To demonstrate the second estimate (4.15), we first provide the estimate for dtunh0. It is noted that the pair (unh,pnh)(UT,QT), where nZM, constitutes a unique sequence of solutions for the fully discrete FVEM scheme in (4.10). This implies that for any (v,q)(UT,QT), the following holds

    (dtunh,ΠTv)+aT(unh,ΠTv)b(v,pnh)+b(dtunh,q)=(fn,ΠTv).

    By selecting v=dtunh and q=pnh in the above equation, we obtain

    Δt|||dtunh|||20+aT(unh,ΠTunh)aT(unh,ΠTun1h)=Δt(fn,ΠTdtunh),

    which results in

    Δt|||dtunh|||20+c0μ2(|unh|21|un1h|21)Δt2Cfn20+Δt2|||dtunh|||20+C|un1h|21.

    Considering again that |u0h|1Cu01 and cv0|||v|||0Cv0 for any vUT, summing the above inequality from 1 to n and applying the discrete Gronwall lemma gives

    Δtni=1dtuih20+μ|unh|21C(μu021+Δtni=1fi20+ni=1|un1h|21).C(μu021+Δtni=1fi20)C(u021+Δtμ1ni=1fi20).

    By employing a technique similar to that used to derive the estimate of pn0 in Theorem 1, the estimate (4.15) can be derived. This concludes our proof.

    This theorem elucidates that the fully discrete FVEM scheme, as described in (4.10), being equivalent to the FVEM scheme in (4.3), possesses a unique series of solutions and meets the necessary stability requirements.

    This section is dedicated to deriving error estimates for the fully discrete FVEM scheme presented in (4.10). To streamline the theoretical investigation, we focus on the FVEM in (4.10) with the mesh parameter as follows:

    α=ˉα:=12(113)(16,12).

    This specific choice of α allows for an easier analysis. Similar approaches can be applied to other cases. Given α=ˉα, it can be deduced that β=116α and ω=113αβ yield β=α and ω=23.

    The following results are then derived from the work of [25, 42].

    Proposition 4. For every vP2(K) and uP1(K), it is shown that

    (u,ΠTv)K=(u,v)K,  for any  KT, (5.1)

    which consequently implies that for all uUT and vUT,

    aT(u,ΠTv)=a(u,v). (5.2)

    In this context, the fully discrete FVEM scheme, as presented in (4.10), with α=ˉα, can be expressed as follows: Find (unh,pnh)(UT,QT), for nZM, satisfying

    {(dtunh,ΠTv)+a(unh,v)b(v,pnh)=(fn,ΠTv),  for all vUT,b(unh,q)=0,  for all qQT,u0h=Πhu(x,0),  for all xΩ. (5.3)

    The primary objective of the subsequent discussion is to investigate the error estimates for the equations given in (5.3).

    To streamline the verification of error estimation, we first present the Stokes projection, which was initially proposed in [33] within the context of the FEM. We denote the Stokes projection of the solutions (un,pn)(UT,QT) for the semi-discrete scheme (3.1) as (Shun,Qhpn), where nZM. This projection ensures that for the solutions (un,pn)(H10(Ω),L20(Ω)), there exists the corresponding (Shun,Qhpn)(UT,QT) satisfying the following conditions

    {(dtShun,v)+a(Shun,v)b(v,Qhpn)=(dtun,v)+a(un,v)b(v,pn),  for all vUT,b(Shun,q)=b(un,q)  for all qQT,Shu0=Πhu0(x), u0=u0(x),  for all xΩ. (5.4)

    Following the standard FEM technique for the Stokes equations as outlined in [35], we derive the following proposition.

    Proposition 5. Let (un,pn), nZM, be the solutions of the semi-discrete scheme (3.1) with (un,pn)(H10(Ω)H3(Ω),L20(Ω)H2(Ω)), and assume that u0H20(Ω). Then, the following error estimates are valid:

    unShun20+Δtμni=1|uiShui|21Ch4,ΔtpnQhpn0Ch2,

    where C is a positive constant that is independent of the mesh size h and the parameter Δt.

    Proof. Employing a proof technique similar to Theorem 1, it follows that there is a unique sequence of solutions (˜unh,˜pnh)(UT,QT), where nZM, for the system of equations given by

    {(dt˜unh,v)+a(˜unh,v)b(v,˜pnh)=(fn,v),  for all vUT,b(˜unh,q)=0,  for all qQT,u0=u0(x),  for all xΩ. (5.5)

    We now examine the error estimates. Similar to standard mixed finite element analysis, for any qQT, we select ˜wnhUT such that b(˜wnh,q)=0, where the infsup condition is satisfied by the space pair (UT,QT). It is worth noting that b(˜unh,q)=0, which implies b(˜unh˜wnh,q)=0 for all qQT. By substituting v=˜unh˜wnh into Eq (5.5), we obtain

    (dt˜unh,v)+a(v,v)=(fn,v)a(˜wnh,v).

    Subtracting Eq (3.1) from the above equation, we get

    (dt˜unhdtun,v)+a(v,v)=a(un˜wnh,v)b(v,pnΓhpn),

    with the observation that b(v,Γhpn)=b(˜unh˜wnh,Γhpn)=0 since ΓhpnQT and pnL20(Ω)H2(Ω). Thus we have

    (˜unhun,v)+Δtμ|v|21=(˜un1hun1,v)+Δta(un˜wnh,v)Δtb(v,pnΓhpn).

    Considering v=˜unhun+un˜wnh, the following equation is derived:

    ˜unhun20+Δtμ|v|21=(˜un1hun1,v)+Δta(un˜wnh,v)(˜unhun,un˜wnh)Δtb(v,pnΓhpn). (5.6)

    Next, we examine each term located at the right-hand side of the above equation. By utilizing the Cauchy-Schwarz inequality, Poincaré inequality, and Yang's inequality for each term, we obtain the following:

    (˜un1hun1,v)=(˜un1hun1,˜unhun)+(˜un1hun1,un˜wnh)˜un1hun10˜unhun0+˜un1hun10un˜wnh02˜un1hun120+14˜unhun20+14un˜wnh20,

    and

    Δta(un˜wnh,v)Δtμ|un˜wnh|1|v|1Δtμ|un˜wnh|21+Δtμ4|v|21,(˜unhun,un˜wnh)˜unhun0un˜wnh014˜unhun20+un˜wnh20,Δtb(v,pnΓhpn)Δt|v|1pnΓhpn0Δtμ4|v|21+Δtμ1pnΓhpn20.

    By substituting the above inequalities into the right-hand side of (5.6), we obtain the following result:

    ˜unhun20+Δtμ|v|214˜un1hun120+52un˜wnh20+2Δtμ|un˜wnh|21+2Δtμ1pnΓhpn20. (5.7)

    It is observed that v=˜unh˜wnh leads to the inequality

    |˜unhun|1|˜unh˜wnh|1+|˜wnh˜un|1=|v|1+|˜wnh˜un|1.

    This implies that

    ˜unhun20+Δtμ|˜unhun|21˜unhun20+2Δtμ(|v|21+|˜wnh˜un|21),

    which, when combined with the inequality (5.7), results in

    ˜unhun20+Δtμ|˜unhun|218˜un1hun120+5un˜wnh20+6Δtμ|un˜wnh|21+4Δtμ1pnΓhpn20.

    By utilizing the given information

    |un˜wnh|mCinfvnhUTunvnhmCh3mun3,  m{0,1},

    and pnΓhpn0Ch2pn2, we can deduce that

    ˜unhun20+Δtμ|˜unhun|218˜un1hun120+Ch4(un22+Δtun23+Δtpn22).

    Define the projection ˜u0h=Πhu0=Shu0, and observe the inequality

    ˜u0hu00Ch2u02.

    By summing the above inequality from 1 to n and applying the discrete Gronwall inequality, we obtain

    ˜unhun20+Δtμni=1|˜uihui|21Ch4u022+Ch4ni=1(ui22+Δtui23+Δtpi22)+7ni=1˜ui1hui120Ch4(u022+Δtni=1(ui23+pi22))Ch4,

    with the condition ΔtT being utilized. In the context of the above inequalities, let Shun=˜unh and Qhpn=pnh for all nZM. This leads to the first estimate of the proposition.

    Next, we examine the second estimation. Define ηn=pnΓhpn and ηnh=QhpnΓhpn. This implies that ηnηnh=pnQhpn. For any (v,q)(UT,QT), subtracting Eq (5.5) from Eq (3.1) under the conditions Shun=˜unh and Qhpn=pnh, for all nZM, results in

    Δtb(v,ηnh)=(unShun,v)(un1Shun1,v)+Δta(unShun,v)Δtb(v,ηn).

    By utilizing the discrete infsup condition (4.1), we derive the following inequality:

    Δtηnh0C(unShun0+un1Shun10+Δtμ|unShun|1+Δtηn0).

    By applying the first estimate of this proposition to the right-hand side of the above inequality, we derive the following inequality:

    Δtηnh0C(h2+Δt12h2+Δtηn0),

    and thus we have

    ΔtpnQhpn0=Δtηnηnh0Δtηn0+Δtηnh0Ch2.

    Here, the interpolation estimate ηn0=pnΓhpn0Ch2pn2 and the condition ΔtT are utilized. This completes the proof of the proposition.

    Utilizing the results of Proposition 5 concerning the Stokes projection, we derive the following error estimates for the solutions (unh,pnh) obtained from the fully discrete FVEM scheme presented in (5.3), where (unh,pnh)(UT,QT) and nZM. The fully discrete FVEM scheme proposed by (5.3) is equivalent to the FVEM scheme in (4.10) when α is set to α=ˉα. We then establish the following theorem.

    Theorem 4. We are given that (unh,pnh)(UT,QT) represents the solutions for the fully discrete FVEM scheme as described in (5.3), with nZM, and that (un,pn)(H10(Ω)H3(Ω),L20(Ω)H2(Ω)) are the solutions for the semi-discrete scheme in (3.1), with nZM. If u0H20(Ω) and fH1(Ω) for all t(0,T], the following error estimates are valid:

    ununh20+μΔtni=1|uiuih|21Ch4,Δtpnhpn0Ch2,

    with C being a positive constant that is independent of the mesh size h and the time step Δt.

    Proof. We begin by examining the first estimate. By subtracting (5.3) from (3.1), we obtain the error equation for all (v,q)(UT,QT). The equation is presented as follows:

    (dtun,v)(dtunh,ΠTv)+a(ununh,v)b(v,pnpnh)+b(ununh,q)=(fn,vΠTv), (5.8)

    which can be rewritten as

    (ununh,v)+Δta(ununh,v)Δtb(v,pnpnh)+Δtb(ununh,q)=Δt(fn,vΠTv)+(un1un1h,v)(unhun1h,vΠTv).

    We select Π0TwUT as the piecewise constant interpolation function for wH2(Ω) associated with the primary partitions TT. By applying the first outcome of Lemma 1 to the above equation, it follows that for all (v,q)(UT,QT),

    (ununh,v)+Δta(ununh,v)Δtb(v,pnpnh)+Δtb(ununh,q)=Δt(fnΠ0Tfn,vΠTv)+(un1un1h,v)(unhΠ0Tunh,vΠTv)+(un1hΠ0Tun1h,vΠTv).

    We define en as en=unShun, and denote ηn as ηn=pnQhpn. We introduce enh=unhShun and ηnh=pnhQhpn, which allows us to express the following relationships:

    enenh=ununh,ηnηnh=pnpnh.

    Based on these definitions, the given equation can be rewritten as follows:

    (enh,v)+Δta(enh,v)Δtb(v,ηnh)+Δtb(enh,q)=Δt(fnΠ0Tfn,vΠTv)+(unhun1hΠ0T(unhun1h),vΠTv)+(en1h,v)+(enen1,v)+Δta(en,v)Δtb(v,ηn)+Δtb(en,q). (5.9)

    Observe that for any integer nZM, the pairs (un,pn)(H10(Ω),L20(Ω)) and (Shun,Qhpn)(UT,QT) satisfy the Eq (5.4). Thus for any (v,q)(UT,QT), the following holds:

    (enen1,v)+Δta(en,v)Δtb(v,ηn)+Δtb(en,q)=0.

    This simplifies the Eq (5.9) to the following form:

    (enh,v)+Δta(enh,v)Δtb(v,ηnh)+Δtb(enh,q)=Δt(fnΠ0Tfn,vΠTv)+(unhun1hΠ0T(unhun1h),vΠTv)+(en1h,v). (5.10)

    We now evaluate each term on the right-hand side of the above equality by setting v=enh and q=ηnh. By applying the Cauchy-Schwarz inequality, the Poincaré inequality, and Yang's inequality on each individual term, we obtain the following inequalities:

    |(en1h,enh)|14enh20+en1h20,

    and

    |Δt(fnΠ0Tfn,enhΠTenh)|Ch2Δtfn1enh1Ch4Δtfn21+μΔt4|enh|1,|(unhun1hΠ0T(unhun1h),enhΠTenh)|Ch2|unhun1h|1|enh|1.

    The second inequality in Proposition 3 is employed in the derivation of these estimates. Next, we delve into a more detailed analysis of the estimate for the term h2|unhun1h|1|enh|1. Utilizing Taylor's theorem, we obtain the following inequality for all nZM,

    |u(tn)u(tn1)|1CΔtsup0<tTut1.

    Based on the result of Theorem 2, we have |u(tn)un|1CΔt for every nZM. This implies that for any nZM, the following inequality holds:

    |unun1|1|unu(tn)|1+|u(tn)u(tn1)|1+|u(tn1)un1|1CΔt.

    Thus, we derive the following inequality:

    |unhun1h|1|enh|1+|ShunShun1|1+|en1h|1|enh|1+C|unun1|1+|en1h|1|enh|1+|en1h|1+CΔt. (5.11)

    By utilizing the inverse inequality in finite element theory and Yang's inequality, we can deduce the following inequality from the previous one:

    Ch2|unhun1h|1|enh|1C(h32|enh|1)(h12|enh|1)+C(h|en1h|1)(h|enh|1)+Ch2Δt|enh|1C(h12enh0)(h12|enh|1)+Cenh0en1h0+Ch2Δt|enh|1Chenh20+Ch|enh|21+18enh20+Cen1h20+Ch4Δt+μΔt8|enh|21.

    Consequently, for sufficiently small values of h, we obtain

    Ch2|unhun1h|1|enh|114enh20+Cen1h20+Ch4Δt+μΔt4|enh|21.

    By substituting the above estimates into (5.10), with v=enh and q=ηnh, we obtain

    enh20+μΔt|enh|21Ch4Δtfn21+μΔt2|enh|1+12enh20+Cen1h20+Ch4Δt.

    This simplifies to

    enh20+μΔt|enh|21Ch4Δt+Cen1h20.

    It is observed that e0h0Ch2. By summing the above inequality from 1 to n and applying the discrete Gronwall lemma, we have

    enh20+μΔtni=1|eih|21Ch4T+e0h20+Cn1i=0eih20C(h4+n1i=0eih20)Ch4.

    Note that the equation ununh=enenh and the results of Proposition 5 hold, and by employing the trigonometric inequality and the interpolation theorem of finite elements, the first estimate can be derived.

    We now examine the second estimation. Observe that for every qQT, the following equality holds:

    b(un,q)=b(unh,q)=0.

    Thus from Eq (5.8), we deduce that for all (v,q)(UT,QT), the following relationship is valid:

    (ununh,v)(un1un1h,v)+(unhun1h,vΠTv)+Δta(ununh,v)Δtb(v,pnpnh)=Δt(fn,vΠTv).

    Given the expressions ηn=pnQhpn, ηnh=pnhQhpn, and thus ηnηnh=pnpnh, we can derive the following equality:

    Δtb(v,ηnh)=Δt(fnΠ0Tfn,vΠTv)+Δtb(v,ηn)(ununh,v)+(un1un1h,v)(unhun1hΠ0T(unhun1h),vΠTv)Δta(ununh,v).

    This equation is derived by expanding the difference between the bilinear forms involving ηn and ηnh, and then rearranging the terms. Applying the discrete infsup condition (4.1), we derive the following inequality from the above equation:

    Δtηnh0Ch2Δtfn1+Δtηn0+ununh0+un1un1h0+Ch2|unhun1h|1+Δtμ|ununh|1.

    This inequality, when combined with the results of the first estimate in this theorem, leads to the following result:

    Δtηnh0Ch2Δtfn1+Δtηn0+Ch2+Ch2|unhun1h|1+CΔt12h2. (5.12)

    By utilizing the inverse inequality and the results of the first estimate of this theorem, it can be deduced from estimate (5.11) that

    Ch2|unhun1h|1Ch(enh0+en1h0+hΔt)C(h2+h2Δt).

    Substituting this into (5.12), we obtain

    Δtηnh0C(h2+Δt12h2+Δth2+Δtηn0).

    Applying the triangle inequality, we have

    Δtpnpnh0Δtηn0+Δtηnh0Ch2.

    This is achieved using the estimation ηn0Ch2pn2 and the condition ΔtT. This completes the proof.

    This theorem demonstrates that the fully discrete FVEM scheme, as detailed in (5.3), achieves optimal order error estimates for the spatial variables associated with the velocity in the H1-norm and the pressure in the L2-norm, aligning with the error estimates of the corresponding FEMs.

    It is worth noting that the smoothness of the solution to problem (2.1) guarantees that the semi-discrete scheme (3.1) maintains the same level of smoothness in the temporal domain. By combining Theorem 2 with Theorem 4, we arrive at the following principal results.

    Theorem 5. Let (u,p) be a solution to (2.1) with (u,p)(H10(Ω)H3(Ω),L20(Ω)H2(Ω)) for all t(0,T], and (unh,pnh)(UT,QT) for nZM is the solution for the fully discrete FVEM scheme (5.3). If u0H20(Ω) and fH1(Ω) for every t(0,T], the following error estimates are valid:

    u(tn)unh20+μΔtni=1|u(ti)uih|21C(h4+Δt2),Δtp(tn)pnh0C(h2+Δt),

    where C denotes a constant that is independent of the mesh size h and the time step Δt.

    Regarding the FVEM scheme presented in (4.10), with different values of the mesh parameter α(16,12), similar theoretical estimates can be achieved through analogous approaches. However, the proof process may be somewhat intricate and laborious. Readers interested in exploring this further are encouraged to attempt it independently. It is worth noting that the FVEM scheme (4.10) is equivalent to the FVEM scheme (4.3). This equivalence demonstrates that the FVEM scheme (4.3) also possesses optimal order error estimates. The subsequent section will provide numerical results that elucidate this point.

    This section provides two numerical experiments designed to validate the theoretical results discussed in the preceding sections. Additionally, a cavity flow test is executed to demonstrate the practicality and effectiveness of the FVEM scheme (4.3) for solving non-stationary Stokes equations numerically. Throughout these experiments, the mesh parameters associated with the dual partition T are set to α(16,12), and the corresponding value of β is calculated as β=116α. The experiments were conducted on a personal computer running Ubuntu OS version 16.04, equipped with an Intel(R) Xeon(R) Silver 4110 CPU operating at 2.10 GHz and a Quadro P4000 GPU.

    In our first example, we examine the error estimations for spatial variables in the FVEM scheme presented in (4.3), and compare them with those of a fully discrete FEM scheme as follows:

    {(dtunh,v)+a(unh,v)b(v,pnh)=(fn,v),  for all vUT,b(unh,q)=0,  for all qQT,u0h=Πhu(x,0),  xΩ. (6.1)

    As established in [35], the FEM scheme (6.1) is known for its stability and possesses optimal error estimates for the non-stationary Stokes equations. The numerical outcomes were achieved using MATLAB software version 7.11.0 (R2023a), which solved the linear systems derived from the FVEM scheme (4.3) and the FEM scheme (6.1).

    Example 1. We consider the non-stationary Stokes equations (2.1), which are defined within the domain Ω=(0,1)×(0,1). The viscosity of the fluid is set to μ=1, and the body force f(x,t) is specified such that the exact solution is given by u(x,t)=(u1(x,y,t),u2(x,y,t)) where

    u1(x,y,t)=2πcos(πy)sin(πx)2sin(πy)cos(t),  u2(x,y,t)=2πcos(πx)sin(πx)sin(πy)2cos(t),

    and

    p(x,t)=cos(πx)cos(πy)cos(t).

    The initial condition u0 is selected to be the exact solution evaluated at t=0, i.e., u0=u(x,0).

    Figure 4 illustrates the primary partition T of the unit square domain Ω, featuring a mesh size of h=825. This partition was generated by the GMSH software version 2.5.0 (2016) through the application of barycentric refinement methods, ensuring that the primary partition TT exhibits good shape regularity.

    Figure 4.  Primary partition T for Example 1.

    The subsequent figures, Figures 5, 6, 7, and 8, depict the error curves for the velocity (H1-norm) and pressure (L2-norm) approximations resulting from the FVEM scheme (4.3). These curves are plotted for various values of the mesh parameter α(16,12) and at time points t(0,1], with a time step size of Δt=0.005. It is evident from the figures that both the FVEM scheme (4.3) and the FEM scheme (6.1) exhibit decreasing errors for velocity and pressure approximations as the time level advances, confirming the stability of the FVEM scheme (4.3) as predicted theoretically. It is easy to understand that, due to the interpolation error of the initial values constructed here decaying over time, the velocity and pressure errors will also show a decreasing trend over time. The numerical results presented in the figures demonstrate that these FVEM schemes exhibit no significant difference in velocity approximation errors compared to the corresponding FEM scheme, except for the FVEM scheme with α=13, which displays slightly higher numerical errors. This indicates that the FVEM schemes achieve computational accuracy comparable to the corresponding FEM scheme, while additionally preserving local physical conservation on dual elements - an inherent advantage of the finite volume framework that is absent in FEM implementations.

    Figure 5.  Error of the FVEM with α=15.
    Figure 6.  Error of the FVEM with α=1236.
    Figure 7.  Error of the FVEM with α=14.
    Figure 8.  Error of the FVEM with α=13.

    To demonstrate the local mass conservation property of the discrete velocity solutions in the FVEM schemes, Figure 9 presents a scatter plot of the absolute values of the integral of the divergence for velocity solutions versus times obtained by the FVEM schemes (under different dual partitions) and the FEM scheme. Considering that in practical numerical computations, factors such as discretization errors, integration approximations, and mesh conditions collectively prevent the divergence integral of the discrete solution from being strictly zero, the results in the figure reveal that the divergence integral of the velocity solutions generated by FVEM schemes with varying dual partitions remains at the level of round-off errors, specifically on the order of 1016, which is equivalent to the corresponding FEM scheme, consequently achieving local mass conservation of the velocity.

    Figure 9.  Divergence for discrete velocity solutions.

    Our second numerical example aims to verify that the numerical results from the FVEM scheme presented in (4.3) achieve the optimal convergence order for the error estimates in the H1-norm for the velocity and the L2-norm for the pressure within the spatial discretization.

    Example 2. This example supposes that the viscosity of the fluid in the non-stationary Stokes equations (2.1) is μ=1 and the exact solution is given by u(x,t)=(u1(x,y,t),u2(x,y,t)), where

    u1(x,y,t)=10etx2y(2y1)(x1)2(y1),  u2(x,y,t)=10etxy2(2x1)(x1)(y1)2,

    and p(x,t)=10et(2x1)(2y1). The initial condition u0 is selected as the exact solution evaluated at t=0, and the computational domain Ω is identical to that used in Example 1.

    Figure 10 illustrates the initial primary partition T of the unit square domain Ω, utilizing a mesh size of h=110. In contrast, Figure 11 depicts the final refined primary partition, which employs a finer mesh with h=120.

    Figure 10.  Initial primary partition with h=110.
    Figure 11.  Refined primary partition with h=120.

    The convergence order of the FVEM scheme with the spatial mesh size h is determined using the following formula:

    r=log(EiEi+1)log(hihi+1),

    where Ei and Ei+1 denote the errors associated with the FVEM scheme for mesh sizes hi and hi+1, respectively.

    In Table 1, we define N=1h. The table presents the optimal convergence order O(h2) for the error estimates of the H1-norm of the velocity and the L2-norm of the pressure, considering various mesh parameters α(16,12), and a time step size of Δt=h2 at the time level t=1. This validates the convergence analysis of the FVEM scheme (4.3) for the non-stationary Stokes equations.

    Table 1.  Errors and convergence orders for Example 2 at t=1 with Δt=h2.
    α N |u(1)uN2h|1 r1(u) p(1)pN2h0 r0(p) u(1)uN2h0 r0(u)
    1236 10 2.31976e-03 - 2.01152e-02 - 2.01636e-05 -
    20 5.80996e-04 1.997373 4.82871e-03 2.058575 2.45670e-06 3.036963
    15 10 2.34808e-03 - 1.99559e-02 - 2.53152e-05 -
    20 5.88695e-04 1.995886 4.76476e-03 2.066340 4.34228e-06 2.543478
    14 10 2.26614e-03 - 2.05786e-02 - 3.37070e-05 -
    20 5.67719e-04 1.996984 5.00902e-03 2.038548 8.17378e-06 2.043971
    13 10 2.26113e-03 - 2.12516e-02 - 7.78306e-05 -
    20 5.70959e-04 1.985587 5.26001e-03 2.014435 2.09111e-05 1.896066

     | Show Table
    DownLoad: CSV

    Furthermore, the error order curves depicted in Figures 1215 below, respectively, indicate that the numerical solutions of (4.3) exhibit optimal error estimates at the time levels t[0.1,1] for various values of the mesh parameter α{15, 1236, 14, 13}. These numerical findings align perfectly with our theoretical predictions, confirming that the proposed FVEM scheme is capable of achieving the optimal error convergence order that matches the corresponding FEM schemes.

    Figure 12.  Convergence order of the FVEM with α=15.
    Figure 13.  Convergence order of the FVEM with α=1236.
    Figure 14.  Convergence order of the FVEM with α=14.
    Figure 15.  Convergence order of the FVEM with α=13.

    In our concluding numerical example, we will conduct a cavity flow analysis to demonstrate the efficiency and practicality of the FVEM scheme in tackling non-stationary Stokes equations. To visualize the numerical results resulting from the FVEM scheme, we will utilize the software TECPLOT version 360EX.

    Example 3. This example considers the cavity flow for the problem defined in (2.1), under the conditions of μ=1 and f=0 on the domain Ω=([1,2]×[0,1])([0,1]×[1,0]). At the left entrance, where x=1, the initial function u(x,0) and the boundary value function u(x,t) are both set to u0(x)=(0,y(1y)). Similarly, at the right exit, where x=2, these functions are set to u0(x)=(0,2). Elsewhere on the boundary, the boundary velocities are maintained at 0.

    In this example, we utilize unstructured triangular meshes as the primary partition T for the domain Ω, as illustrated in Figure 16. For the dual partitions T of the FVEM scheme, we select the mesh parameter to be α=1236. The time step size remains at Δt=0.005. Figures 17 and 18 present the pressure contours obtained through the FVEM scheme at time points t=0.01 and t=1, respectively. Comparing these figures, it is evident that the pressure contour lines have become less pronounced.

    Figure 16.  Primary partition T for Example 3.
    Figure 17.  Pressure contours at t=0.01.
    Figure 18.  Pressure contours at t=1.

    Figures 19 and 20 illustrate the streamline and flow patterns at time instances t=0.01 and t=1, respectively. Comparing Figure 19 with Figure 20, it can be intuitively observed that the streamline and flow field obviously and deterministically shift from the bottom wall of the cavity to the two side walls. This observation suggests that the FVEM scheme we propose is both stable and efficient in tackling the non-stationary Stokes equations. To learn more information on the fluid mechanics of driven cavities, readers are encouraged to consult [45] and its related references.

    Figure 19.  Velocity streamlines and vectors at t=0.01.
    Figure 20.  Velocity streamlines and vectors at t=1.

    In this paper, a novel fully discrete spatial-temporal FVEM scheme, utilizing the LC element pair, has been developed and investigated for solving the non-stationary Stokes equations on barycenter-refined triangular meshes. We first derived a semi-discrete temporal scheme for the non-stationary Stokes equations, followed by directly constructing the fully discrete FVEM scheme from the semi-discrete temporal scheme, thereby avoiding the establishment of a semi-discrete spatial FVEM scheme. Employing the theoretical analysis techniques of classical FEMs, we established the stability of the fully discrete FVEM scheme, as well as the existence and uniqueness of the discrete solution, and derived the optimal order error estimate for spatial variables. The discrete velocity solution obtained from the FVEM scheme exhibits the property of local mass conservation. Numerical experiments have been conducted to confirm that the numerical errors between the discrete FVEM solutions and the exact solutions align with the theoretical findings presented earlier. Furthermore, a numerical simulation of flow within a cavity demonstrates the feasibility and efficiency of the fully discrete FVEM scheme in computing numerical solutions for the non-stationary Stokes equations. The methods and concepts presented in this paper can be extended to other time discretization schemes, such as the Crank-Nicolson FVEM scheme with second-order temporal accuracy. Given the benefits of higher-order approximations in fluid dynamics applications, the proposed scheme deserves further investigation. Future research should extend the application of this scheme to the non-stationary Navier-Stokes equations and broader computational fluid dynamics problems, while systematically addressing potential singularities caused by geometric discontinuities near the corners of the computational domain.

    The author(s) declare(s) they have no used Artificial Intelligence (AI) tools in the creation of this article.

    The author would like to express the deepest gratitude to the anonymous referees for their careful reading of the manuscript, several valuable comments, and suggestions for its improvement. This work is partly supported by the Foundation Research Project of Kaili University (grant no. 2024ZD007) and by the Famous Teacher Studio Project of Guizhou Province (grant no. MSGZS-SJ-2024003).

    The author declares that he has no potential conflict of interest or personal relationships that could have appeared to influence the work reported in this paper.

    Proof. We first present the existence of the solution to Eq (3.1). Let A(un,v)=(un,v)+Δta(un,v) and F(v)=(Δtfn+un1,v) for any (v,q)(H10(Ω),L20(Ω)). It is easy to see that A(un,v) is a bounded bilinear form satisfying A(un,v)Cun1v1, and there exists a positive constant c such that A(un,un)=Δtμ|un|21+un20cun21. For given un1 and f, we know F(v) is a continuous function on L2(Ω). It follows from (2.5) that b(un,q) satisfies the infsup stability condition for any (un,q)(H10(Ω),L20(Ω)). Thus from the theory of existence and uniqueness of the solution for the mixed variational problem, Equation (3.1) has a unique series of solutions (un,pn)(H10(Ω),L20(Ω)), nZM.

    We next consider the estimates. Choosing v=un, q=pn in (3.1), we have

    un20+Δtμ|un|21=(Δtfn,un)+(un1,un).

    Applying the Cauchy-Schwartz inequality, Yang's inequality and the Poincaré inequality to the right-hand term of the equation above yields

    un20+Δtμ|un|21Δtfn0un0+un0un1012Δtμ1fn20+12Δtμ|un|21+12un20+12un120,

    and thus un20+Δtμ|un|21Δtμ1fn20+un120. Observe that u0=u0. Summing the above inequalities from 1 to n yields the first estimate of this theorem, which implies

    μΔtni=1|ui|21u020+μ1Δtni=1fi20. (A.1)

    We now analyze the second estimate. To this end, we first show the estimate dtun0. Note that (un,pn)(H10(Ω),L20(Ω)) for any nZM is the solution of (3.1), and this means b(un,q)=b(un1,q)=0, for all qL20(Ω). This combines with (3.1) to yield that for all (v,q)(H10(Ω),L20(Ω)),

    (dtun,v)+a(un,v)b(v,pn)+b(dtun,q)=(fn,v).

    Choosing v=dtun, q=pn in the above equation gives us

    (dtun,dtun)+a(un,dtun)b(dtun,pn)+b(dtun,pn)=(fn,dtun),

    which is equivalent to Δtdtun20+a(un,un)a(un,un1)=Δt(fn,dtun). Applying the Cauchy-Schwartz and Young inequality to the above equation, we get

    Δtdtun20+μ2(|un|21|un1|21)Δt2fn20+Δt2dtun20.

    Summing the above inequalities from 1 to n yields

    Δtni=1dtui20+μ|un|21μ|u0|21+Δtni=1fi20,

    which implies

    Δtni=1dtui20C(|u0|21+Δtμ1ni=1fi20). (A.2)

    It is our turn to present the estimate pn0. Applying the infsup condition (2.5) to the first equality in (3.1), it yields pn20C(dtun20+μ|un|21+fn20). By summing the above inequalities from 1 to n, we obtain

    Δtni=1pi20C(Δtni=1dtui20+μΔtni=1|ui|21+Δtni=1fi20).

    Applying the results of (A.1) and (A.2) to the above right-hand term yields the second desired result. This completes our proof.

    Proof. Note that (u,p)(H10(Ω),L20(Ω)) for any t(0,T] is the solution of the problem (2.1) and thus satisfies the variational form (2.2). Taking t=tn in (2.2) yields

    {(ut(tn),v)+a((u(tn),v)b(v,p(tn))=(f(tn),v),for all vH10(Ω),b(ut(tn),q)=0,for all qL20(Ω),u(x,0)=u0(x),for all xΩ. (B.1)

    Subtracting (3.1) from (B.1), and then taking v=u(tn)un and q=p(tn)pn, we obtain

    (ut(tn)dtun,u(tn)un)+μ|u(tn)un|21=0,

    where we used the fact that f(tn)=fn. Denote en=u(tn)un, using the definition of dtun and the result of (3.2), and it follows that

    1Δt(enen1,en)+μ|en|21=12Δt(tntn1utt(t)(ttn1)2dt,en). (B.2)

    Note that ttn1Δt and ttn1τ(t) for any t[tn1,tn], nZM. An application of the Cauchy-Schwartz inequality, Yang's inequality, and the Poincaré inequality to the right end term of the above equation obtains

    12Δt(tntn1utt(t)(ttn1)2dt,en)CΔt2μtntn1τ(t)utt(t)20dt+μ2|en|21,

    where we used the fact that

    tntn1τ(t)|utt(t)|dt20Ω(Δttntn1τ2(t)|utt(t)|2dt)dxΔttntn1τ(t)utt(t)20dt. (B.3)

    Note that 12Δt(en20en120)1Δt(enen1,en). By substituting the above two inequalities into the right and the left ends of equation (B.2) respectively, we obtain

    12Δt(en20en120)+μ2|en|21CΔt2μtntn1τ(t)utt(t)20dt.

    By summing the inequality above from 1 to n and using the fact that e0=0, we gain

    12Δten20+ni=1μ2|ei|21CΔt2μT0τ(t)utt(t)20dt,

    which implies for any nZM,

    en20+ni=1μΔt|ei|21CΔt2μT0τ(t)utt(t)20dt. (B.4)

    We next consider the estimate of ηn=p(tn)pn. Note that (un,pn)(H10(Ω),L20(Ω)) for any nZM is the solution of (3.1), and (u(t),p(t))(H10(Ω),L20(Ω)) for any t(0,T] satisfies the variational form (2.2), which leads to b(enen1,q)=0 for all qL20(Ω). Subtracting (3.1) from (B.1) again, and then choosing v=enen1 and q=p(tn)pn, yields (ut(tn)dtun,enen1)+a(en,enen1)=0. Then it holds that

    1Δtenen120+μ2(|en|21|en1|21)12Δt(tntn1utt(t)(ttn1)2dt,enen1). (B.5)

    Again an application of the Cauchy-Schwartz inequality, Yang's inequality, and the inequality (B.3) to the right end term of the above equation obtains

    12Δt(tntn1utt(t)(ttn1)2dt,enen1)Δt22tntn1τ(t)utt(t)20dt+12Δtenen120.

    This means the inequality (B.5) can be written as

    1Δtenen120+μ2(|en|21|en1|21)Δt22tntn1τ(t)utt(t)20dt+12Δtenen120.

    By summing the inequality above from 1 to n and using the fact that e0=0, we gain

    12Δtni=1enen120+μ2|en|21Δt22T0τ(t)utt(t)20dt. (B.6)

    On the other side, the difference between (3.1) and (B.1) leads to

    1Δt(enen1,v)+a(en,v)b(v,ηn)=12Δt(tntn1utt(t)(ttn1)2dt,v),

    where the equality (3.2) was used. Note that

    12Δt(tntn1utt(t)(ttn1)2dt,v)12tntn1τ(t)|utt(t)|dt0v0C2tntn1τ(t)|utt(t)|dt0|v|1

    and observing the infsup condition (2.5) yields

    Δtηn0C(enen10+Δtμ|en|1+Δt2tntn1τ(t)|utt(t)|dt0).

    Then applying inequality (B.3) again, we have

    Δt2ηn20C(enen120+Δt2μ|en|21+Δt2tntn1τ(t)|utt(t)|dt20)C(enen120+Δt2μ|en|21+Δt3tntn1τ(t)utt(t)20dt).

    Considering the estimates (B.4) and (B.6), summing the above inequalities from 1 to n yields

    Δt2ni=1ηi20CΔt3T0τ(t)utt(t)20dt.

    This finishes the proof of this theorem.



    Use of AI tools declaration



    The authors declare they have not used Artificial Intelligence (AI) tools in the creation of this article.

    Conflict of interest



    The authors declare no conflict of interest.

    Author contributions



    Tanishka Taori: Conceptualization and design of the review article including selection of the topic of article, literature search and acquisition of relevant articles, Analysis and synthesis of the collected literature, including the identification of key themes or trends, writing and editing of all the sections including the drafting of specific sections and sub sections, critical revision of the manuscript.
    Shefali Maheshwari: Literature search and acquisition of relevant articles, analysis and synthesis of the collected literature, writing and editing of specific sections.
    Anjali Borle: Conceptualization and design of the review article including selection of the topic of article, literature search and acquisition of relevant articles, Analysis and synthesis of the collected literature, including the identification of key themes or trends, critical revision of the manuscript, providing guidance and expertise in the specific field.
    Amit Reche: Literature search and acquisition of relevant articles, analysis and synthesis of the collected literature, supervision and coordination of the overall review article project.

    [1] KTevlin R, McArdle A, Atashroo D, et al. (2014) Biomaterials for craniofacial bone engineering. J Dent Res 93: 1187-1195. https://doi.org/10.1177/0022034514547271
    [2] Chan BP, Leong KW (2008) Scaffolding in tissue engineering: general approaches and tissue-specific considerations. Eur Spine J 17: 467-479. https://doi.org/10.1007/s00586-008-0745-3
    [3] Arif ZU, Khalid MY, Noroozi R, et al. (2022) Recent advances in 3D-printed polylactide and polycaprolactone-based biomaterials for tissue engineering applications. Int J Biol Macromo 218: 930-968. https://doi.org/10.1016/j.ijbiomac.2022.07.140
    [4] Hsu EL, Ghodasra JH, Ashtekar A, et al. (2013) A comparative evaluation of factors influencing osteoinductivity among scaffolds designed for bone regeneration. Tissue Eng Part A 19: 1764-1772. https://doi.org/10.1089/ten.tea.2012.0711
    [5] Keane TJ, Badylak SF (2014) Biomaterials for tissue engineering applications. Semin Pediatr Surg 23: 112-118. https://doi.org/10.1053/j.sempedsurg.2014.06.010
    [6] Jafari M, Paknejad Z, Rad MR, et al. (2017) Polymeric scaffolds in tissue engineering: a literature review. J Biomed Mater Res Part B: Appl Biomater 105: 431-459. https://doi.org/10.1002/jbm.b.33547
    [7] Schulte M, Schultheiss M, Hartwig E, et al. (2000) Vertebral body replacement with a bioglass-polyurethane composite in spine metastases–clinical, radiological and biomechanical results. Eur Spine J 9: 437-444. https://doi.org/10.1007/s005860000162
    [8] Elisseeff J, Puleo C, Yang F, et al. (2005) Advances in skeletal tissue engineering with hydrogels. Orthod Craniofac Res 8: 150-161. https://doi.org/10.1111/j.1601-6343.2005.00335.x
    [9] Arvidson K, Abdallah BM, Applegate LA, et al. (2011) Bone regeneration and stem cells. J Cell Mol Med 15: 718-746. https://doi.org/10.1111/j.1582-4934.2010. 01224.x
    [10] Moshiri A, Oryan A (2012) Role of tissue engineering in tendon reconstructive surgery and regenerative medicine: current concepts, approaches and concerns. Hard Tissue 1: 11. https://doi.org/10.13172/2050-2303-1-2-291
    [11] Khalid MY, Arif ZU (2022) Novel biopolymer-based sustainable composites for food packaging applications: a narrative review. Food Packag Shelf Life 33: 100892. https://doi.org/10.1016/j.fpsl.2022.100892
    [12] Khalid MY, Al Rashid A, Arif ZU, et al. (2021) Natural fiber reinforced composites: Sustainable materials for emerging applications. Results Eng 11: 100263. https://doi.org/10.1016/j.rineng.2021.100263
    [13] Arif ZU, Khalid MY, Sheikh MF, et al. (2022) Biopolymeric sustainable materials and their emerging applications. J Environ Chem Eng 10: 108159. https://doi.org/10.1016/j.jece.2022.108159
    [14] Arif ZU, Khalid MY, Noroozi R, et al. (2023) Additive manufacturing of sustainable biomaterials for biomedical applications. Asian J Pharm Sci 2023: 100812. https://doi.org/10.1016/j.ajps.2023.100812
    [15] Kang BJ, Kim Y, Lee SH, et al. (2013) Collagen I gel promotes homogenous osteogenic differentiation of adipose tissue-derived mesenchymal stem cells in serum-derived albumin scaffold. J Biomater Sci Polym Ed 24: 1233-1243. https://doi.org/10.1080/09205063.2012.745717
    [16] Ferreira AM, Gentile P, Chiono V, et al. (2012) Collagen for bone tissue engineering. Acta Biomater 8: 3191-3200. https://doi.org/10.1016/j.actbio.2012.06.014
    [17] Kadler K (2004) Matrix loading: assembly of extracellular matrix collagen fibrils during embryogenesis. Birth Defects Res C 72: 1-11. https://doi.org/10.1002/bdrc.20002
    [18] Quinlan E, Thompson EM, Matsiko A, et al. (2015) Functionalization of a collagen-hydroxyapatite scaffold with osteostatin to facilitate enhanced bone regeneration. Adv Healthcare Mater 4: 2649-2656. https://doi.org/10.1002/adhm.201500439
    [19] Zhou C, Ye X, Fan Y, et al. (2014) Biomimetic fabrication of a three-level hierarchical calcium phosphate/collagen/hydroxyapatite scaffold for bone tissue engineering. Biofabrication 6: 035013. https://doi.org/10.1088/1758-5082/6/3/035013
    [20] Noori A, Ashrafi SJ, Vaez-Ghaemi R, et al. (2017) A review of fibrin and fibrin composites for bone tissue engineering. Int J Nanomed 12: 4937. https://doi.org/10.2147/IJN.S124671
    [21] Siddiqui N, Pramanik K (2015) Development of fibrin conjugated chitosan/nano β-TCP composite scaffolds with improved cell supportive property for bone tissue regeneration. J Appl Polym Sci 132: 41534. https://doi.org/10.1002/app.41534
    [22] Kim BS, Sung HM, You HK, et al. (2014) Effects of fibrinogen concentration on fibrin glue and bone powder scaffolds in bone regeneration. J Biosci Bioeng 118: 469-475. https://doi.org/10.1016/j.jbiosc.2014.03.014
    [23] Wong M (2004) Alginates in tissue engineering. Biopolymer Methods in Tissue Engineering. Methods in Molecular Biology™ . Switzerland: Humana Press 77-86. https://doi.org/10.1385/1-59259-428-X:77
    [24] Venkatesan J, Bhatnagar I, Kim SK (2014) Chitosan-alginate biocomposite containing fucoidan for bone tissue engineering. Marine Drugs 12: 300-316. https://doi.org/10.3390/md12010300
    [25] Valente JFA, Valente TAM, Alves P, et al. (2012) Alginate based scaffolds for bone tissue engineering. Mater Sci Engi C 32: 2596-2603. 10.1016/j.msec.2012.08.001
    [26] Kim M, Jung WK, Kim G (2013) Bio-composites composed of a solid free-form fabricated polycaprolactone and alginate-releasing bone morphogenic protein and bone formation peptide for bone tissue regeneration. Bioprocess Biosyst Eng 36: 1725-1734. https://doi.org/10.1007/s00449-013-0947-x
    [27] Pina S, Rebelo R, Correlo VM, et al. (2018) Bioceramics for osteochondral tissue engineering and regeneration. Osteochondral Tissue Engineering. Advances in Experimental Medicine and Biology . Cham: Springer 53-75. https://doi.org/10.1007/978-3-319-76711-6_3
    [28] Li DW, He J, He FL, et al. (2018) Silk fibroin/chitosan thin film promotes osteogenic and adipogenic differentiation of rat bone marrow-derived mesenchymal stem cells. J Biomater Appl 32: 1164-1173. https://doi.org/10.1177/0885328218757767
    [29] Aliramaji S, Zamanian A, Mozafari M (2017) Super-paramagnetic responsive silk fibroin/chitosan/magnetite scaffolds with tunable pore structures for bone tissue engineering applications. Mater Sci Eng C 70: 736-744. https://doi.org/10.1016/j.msec.2016.09.039
    [30] Zhang W, Ahluwalia IP, Literman R, et al. (2011) Human dental pulp progenitor cell behavior on aqueous and hexafluoroisopropanol based silk scaffolds. J Biomed Mater Res A 97: 414-422. https://doi.org/10.1002/jbm.a.33062
    [31] Collins MN, Birkinshaw C (2013) Hyaluronic acid-based scaffolds for tissue engineering—a review. Carbohydr Polym 92: 1262-1279. https://doi.org/10.1016/j.carbpol.2012.10.028
    [32] Seol YJ, Lee JY, Park YJ, et al. (2004) Chitosan sponges as tissue engineering scaffolds for bone formation. Biotechnol Lett 26: 1037-1041. https://doi.org/10.1023/B:BILE.0000032962.79531.fd
    [33] Balagangadharan K, Dhivya S, Selvamurugan N (2017) Chitosan based nanofibers in bone tissue engineering. Int J Biol Macromol 104: 1372-1382. https://doi.org/10.1016/j.ijbiomac.2016.12.046
    [34] Shalumon KT, Sowmya S, Sathish D, et al. (2013) Effect of incorporation of nanoscale bioactive glass and hydroxyapatite in PCL/chitosan nanofibers for bone and periodontal tissue engineering. J Biomed Nanotechnol 9: 430-440. https://doi.org/10.1166/jbn.2013.1559
    [35] Wang F, Zhang YC, Zhou H, et al. (2014) Evaluation of in vitro and in vivo osteogenic differentiation of nano-hydroxyapatite/chitosan/poly (lactide-co-glycolide) scaffolds with human umbilical cord mesenchymal stem cells. J Biomed Mater Res A 102: 760-768. https://doi.org/10.1002/jbm.a.34747
    [36] Khalid MY, Al Rashid A, Arif ZU, et al. (2021) Recent advances in nanocellulose-based different biomaterials: types, properties, and emerging applications. J Mater Res Technol 14: 2601-2623. https://doi.org/10.1016/j.jmrt.2021.07.128
    [37] Arif ZU, Khalid MY, Sheikh MF, et al. (2022) Biopolymeric sustainable materials and their emerging applications. J Environ Chem Eng 10: 108159. https://doi.org/10.1016/j.jece.2022.108159
    [38] Burdick JA, Anseth KS (2002) Photoencapsulation of osteoblasts in injectable RGD-modified PEG hydrogels for bone tissue engineering. Biomaterials 23: 4315-4323. https://doi.org/10.1016/s0142-9612(02)00176-x
    [39] Lin WJ, Flanagan DR, Linhardt RJ (1999) A novel fabrication of poly (ϵ-caprolactone) microspheres from blends of poly (ϵ-caprolactone) and poly (ethylene glycol) s. Polymer 40: 1731-1735. https://doi.org/10.1016/S0032-3861(98)00378-4
    [40] Nair LS, Laurencin CT (2007) Biodegradable polymers as biomaterials. Prog Polym Sci 32: 762-798. https://doi.org/10.1016/j.progpolymsci.2007.05.017
    [41] Ramesh N, Moratti SC, Dias GJ (2018) Hydroxyapatite–polymer biocomposites for bone regeneration: A review of current trends. J Biomed Mater Res Part B 106: 2046-2057. https://doi.org/10.1002/jbm.b.33950
    [42] Yang C, Unursaikhan O, Lee JS, et al. (2014) Osteoconductivity and biodegradation of synthetic bone substitutes with different tricalcium phosphate contents in rabbits. J Biomed Mater Res Part B 102: 80-88. https://doi.org/10.1002/jbm.b.32984
    [43] Özcan M, Hämmerle C (2012) Titanium as a reconstruction and implant material in dentistry: advantages and pitfalls. Materials 5: 1528-1545. https://doi.org/10.3390/ma5091528
    [44] Anil S, Anand PS, Alghamdi H, et al. (2011) Dental implant surface enhancement and osseointegration. Implant Dentistry—A Rapidly Evolving Practice . Europe: InTech 83-108. https://doi.org/10.5772/16475
    [45] Wen CE, Yamada Y, Shimojima K, et al. (2002) Novel titanium foam for bone tissue engineering. J Mater Res 17: 2633-2639. https://doi.org/10.1557/JMR.2002.0382
    [46] Özkurt Z, Kazazoğlu E (2011) Zirconia dental implants: a literature review. J Oral Implantol 37: 367-376. https://doi.org/10.1563/AAID-JOI-D-09-00079
    [47] Abhay SS, Ganapathy D, Veeraiyan DN, et al. (2021) Wear resistance, color stability and displacement resistance of milled PEEK crowns compared to zirconia crowns under stimulated chewing and high-performance aging. Polymers 13: 3761. https://doi.org/10.3390/polym13213761
    [48] Arif ZU, Khalid MY, ur Rehman E (2022) Laser-aided additive manufacturing of high entropy alloys: processes, properties, and emerging applications. J Manuf Process 78: 131-171. https://doi.org/10.1016/j.jmapro.2022.04.014
    [49] Arif ZU, Khalid MY, Al Rashid A, et al. (2022) Laser deposition of high-entropy alloys: a comprehensive review. Opt Laser Technol 145: 107447. https://doi.org/10.1016/j.optlastec.2021.107447
    [50] Arif ZU, Khalid MY, ur Rehman E, et al. (2021) A review on laser cladding of high-entropy alloys, their recent trends and potential applications. J Manuf Process 68: 225-273. https://doi.org/10.1016/j.jmapro.2021.06.041
    [51] Skallevold HE, Rokaya D, Khurshid Z, et al. (2019) Bioactive glass applications in dentistry. Int J Mol Sci 20: 5960. https://doi.org/10.3390/ijms20235960
    [52] Alqurashi H, Khurshid Z, Syed AUY, et al. (2021) Polyetherketoneketone (PEKK): An emerging biomaterial for oral implants and dental prostheses. J Adv Res 28: 87-95. https://doi.org/10.1016/j.jare.2020.09.004
    [53] Cheng X, Wan Q, Pei X (2018) Graphene family materials in bone tissue regeneration: perspectives and challenges. Nanoscale Res Lett 13: 289. https://doi.org/10.1186/s11671-018-2694-z
    [54] Borrelli MR, Hu MS, Longaker MT, et al. (2020) Tissue engineering and regenerative medicine in craniofacial reconstruction and facial aesthetics. J Craniofac Surg 31: 15-27. https://doi.org/10.1097/SCS.0000000000005840
    [55] Khalid MY, Arif ZU, Noroozi R, et al. (2022) 4D printing of shape memory polymer composites: A review on fabrication techniques, applications, and future perspectives. J Manuf Process 81: 759-797. https://doi.org/10.1016/j.jmapro.2022.07.035
    [56] Thrivikraman G, Athirasala A, Twohig C, et al. (2017) Biomaterials for craniofacial bone regeneration. Dent Clin 61: 835-856. https://doi.org/10.1016/j.cden.2017.06.003
    [57] Khalid MY, Arif ZU, Ahmed W (2022) 4D printing: technological and manufacturing renaissance. Macromol Mater Eng 307: 2200003. https://doi.org/10.1002/mame.202200003
    [58] Arif ZU, Khalid M Y, Zolfagharian A, et al. 4D bioprinting of smart polymers for biomedical applications: Recent progress, challenges, and future perspectives. React Funct Polym 179: 105374. https://doi.org/10.1016/j.reactfunctpolym.2022.105374
    [59] Mijiritsky E, Ferroni L, Gardin C, et al. (2017) Porcine bone scaffolds adsorb growth factors secreted by MSCs and improve bone tissue repair. Materials 10: 1054. https://doi.org/10.3390/ma10091054
    [60] Shakya AK, Kandalam U (2017) Three-dimensional macroporous materials for tissue engineering of craniofacial bone. Brit J Oral Max Surg 55: 875-891. https://doi.org/10.1016/j.bjoms.2017.09.007
  • Reader Comments
  • © 2023 the Author(s), licensee AIMS Press. This is an open access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/4.0)
通讯作者: 陈斌, bchen63@163.com
  • 1. 

    沈阳化工大学材料科学与工程学院 沈阳 110142

  1. 本站搜索
  2. 百度学术搜索
  3. 万方数据库搜索
  4. CNKI搜索

Metrics

Article views(2321) PDF downloads(118) Cited by(0)

/

DownLoad:  Full-Size Img  PowerPoint
Return
Return

Catalog