A mechanical approach is needed for understanding anorectal function and defecation. Fecal continence is achieved by several interacting mechanisms including anatomical factors, anorectal sensation, rectal compliance, stool consistency, anal muscle strength, motility, and psychological factors. The balance is easily disturbed, resulting in symptoms such as fecal incontinence and constipation. Novel technologies have been developed in recent years for studying anorectal function. Especially, the Fecobionics device, a simulated feces, has gained attention recently. This facilitates new analysis of anorectal mechanical function. In this study, a theoretical model is developed to analyze anorectal mechanophysiological data generated by the Fecobionics device. Theoretical approaches can enhance future interdisciplinary research for unraveling defecatory function, sensory-motor disorders, and symptoms. This is a step in the direction of personalized treatment for gastrointestinal disorders based on optimized subtyping of anorectal disorders.

## Introduction

Inaccessibility of the gastrointestinal tract and the unavailability of gastrointestinal tissue force the modern investigator to develop new device innovations, mathematical modeling, and simulations to examine gastrointestinal sensory-motor function. Gastroenterology is an important area from a societal and clinical viewpoint, as an example, 15.3% of the U.S. population over 70 years of age and up to 9.5% below age 70 suffer from fecal incontinence [1,2]. Study of the mechanical function of the gastrointestinal tract is important as it serves to transport ingested materials and secreted fluids through the tract. Mechanical analysis including modeling and simulations requires geometric and mechanical data obtained from real tissues and experiments using advanced high-resolution technologies and imaging. New technology can advance our knowledge if it is properly applied. However, this will require a general appreciation for bioengineering, modeling, and simulation in gastroenterology.

Defecation and continence depend on several interacting mechanisms including the ability to create a high intra-abdominal pressure, colorectal motility, stool consistency, rectal capacity, rectal distensibility, anorectal sensitivity, anal muscle strength, anorectal angle, coordination of pelvic floor muscles and anal sphincter, and psychological factors [3–6]. The homeostatic balance is easily disturbed, resulting in symptoms such as fecal incontinence, constipation, or painful defecation [7–10]. Technologies are available for studying anorectal function [11]. However, the conventional technologies do not provide measurements that allow useful mechanical analysis.

This paper briefly describes conventional technologies and the Fecobionics technology. Fecobionics provides measurements that combine distension of an intraluminal bag with pressure recordings and geometric data, medical imaging based on electrical impedance measurements, three-dimensional (3D)-modeling, and new opportunities to combine data on tissue properties and luminal flow [12–14]. In this paper, we developed a theoretical model for analyzing anorectal mechanophysiological data generated by the Fecobionics device.

## Conventional Anorectal Technologies

*p*and Δ

*d*are the pressure and diameter change during the distension, respectively.

*d*

_{0}is the diameter at the reference state [12,25–29]. The pressure–strain modulus is more reliable than the simple distensibility measures. Yet other studies defined a proxy of the flow resistance of the anal canal (

*R*) during FLIP distension. This can be obtained from the anal canal length (

*L*), the middle part diameter of the anal canal (

*D*), and the dynamic viscosity of the inflated bag (

*η*) as [30–32]

## Fecobionics

Limitations with the abovementioned technologies warranted the development of integrated technology that provides measures under much more physiological and pathophysiological conditions [11].

Fecobionics is a simulated stool, a bionics or biomechatronics device, that enables dynamic measurements of a variety of variables during evacuation from rectum through the anal canal [33–36]. Fecobionics imitates the defecation process in a single examination and provides manometric profiles and geometric mapping. The device has the consistency and shape of normal stool (types 3–5 on the Bristol stool scale [37]. It records pressures, CSA from electrical impedance measurements, orientation, bending, and viscoelastic properties during defecation as well as the patients can report symptoms. The device is 10 cm long and 12 mm wide with a core of medical grade resin that contains the sensors and printed circuit boards. A bag is mounted on the bendable core for distension. Sensors such as pressure transducers are placed at the front, rear, and inside the bag, two gyroscopes at the two ends for orientation and angle measurements, and impedance electrodes for CSA measurements. Fecobionics measures front and rear pressures in the direction of the flow in contrast to the radial pressure measurements in other devices. The published prototypes have been wired but wireless prototypes are now becoming available.

Fecobionics enables the measurement of high-resolution pressure and CSA profiles as well as the anorectal angle during defecation [33,34,36]. The CSA profiles are simulated in various ways, i.e., as semi-3D plots, video clips, or as color contour plots. The expulsion velocity can be assessed from changes in CSA during defecation or from data from the pressure sensors and the accelerometers. In addition to the CSA plots, promising physiological data were obtained from the pressure sensors, which allowed defecation to be divided into five distinct phases [33,34,36]. The expulsion time is comparable to that recorded with BET and the bending angle corresponds to anorectal angles reported in the literature (unpublished data). Hence, Fecobionics data are consistent with the current standards, and it integrates the current tests and provides new parameters hitherto unmeasurable.

## New Analytical Approach to Fecobionics Measurements Based on Anorectal Tissue Deformation and Stress During Fecobionics Testing

As Fecobionics moves through the rectum and anal canal during defection, it will stress and deform anorectal tissue. Hence, computations and models that can be used to predict the tissue mechanical behavior in response to loading are important.

### Geometry of the Curved Thin-Walled Shell of Revolution.

The theory outlined below is borrowed from our previous study on distension in a straight hollow visceral organ [38]. However, anorectum is a hollow organ with a geometry of variable cross section and is rotationally symmetric with a curved central line. Consequently, tension calculated based on an arbitrary surface coordinate system should be used [39].

It is assumed that the Fecobionics bag and anorectum form a tube of revolution during Fecobionics movement. Furthermore, the bag size must be larger than the size of the distended anorectum to avoid pressure drop across the bag wall. The anorectal wall resists the pressure induced by the bag distension and the shear stress through the friction between the bag and the tissue wall. The given curve of the anorectal wall is called the curve of symmetry of the reference surface. The coordinates of the reference surface will be the parameter *s*, which determines a point on the curve of symmetry, and the angle *θ*, which is measured within the normal plane from the principal normal of the curve of symmetry (Fig. 1).

*t*is given by

**i**,

**j**, and

**k**are unit vectors of

*x*,

*y*, and

*z*; $x\u2032,y\u2032,\u2009and\u2009z\u2032$ are

**b**is defined as

where **n** is the unit principal normal.

**R**can be expressed in local coordinates as (Fig. 1)

**p**is the vector of the cross point between the cross section at

*s*and the curve of symmetry, and

*r*is the radius of the cross section at

*s*. For a curved shell of revolution, the base vector along the

*s*and

*θ*direction of the surface can be denoted as

*c*is the circular curvature of the curve

*αs*and

*αθ*can be calculated as

*R*and

_{s}*R*can be calculated as

_{θ}### Determination of the Membrane Tension.

where *f _{w}* is the distributed force across the tissue wall, and

*f*and

_{s}*f*are the distributed force (force per unit area) between Fecobionics and the wall tissue along the

_{θ}*s*and

*θ*directions, respectively.

As that is shown in Fig. 1, the membrane stress resultants are *N _{s}*,

*Ns*, and

_{θ}*N*. The boundary condition for Fecobionics in the anorectal segment is $Ns=Ns\theta =N\theta =0$ when $s\u2192\u221e$. During Fecobionics movement, the wall is deformed and stressed by the distension, contractile force from the anorectal muscles, and the forces from Fecobionics. For anorectum, we assume that the forces across the wall, such as the bag pressure and the contractile force, are represented by the recorded bag pressure. Hence, with the estimated forces from Fecobionics, the membrane stress resultants of the anorectum can be computed as previously outlined [38].

_{θ}### Determination of Forces Acting on Fecobionics.

For Fecobionics to move along the anorectal segment, it has to overcome a variety of forces acting on it. These forces include the contractile forces from the segment (*P _{w}*), the pressure in the bag (

*P*), the friction force between the surface and the wall (

_{b}*F*) [40], the pressure from the fluid within the segment at the inlet (rear pressure,

_{f}*P*), the pressure from the segment and the atmosphere at the outlet (front pressure,

_{r}*P*), and also the gravity (

_{f}*G*) of Fecobionics (Fig. 2).

*m*is the mass of the Fecobionics,

*v*is the expulsion velocity of Fecobionics, $v\u02d9=dv/dt$ is the acceleration of Fecobionics moving, $\u2211Fs$ the resultant force along the

*s*direction, and $Gs$ the gravity component in the

*s*direction. Hence, the force distribution (force per unit area,

*fs*, in Eq. (11)) in the

*s*direction between the Fecobionics and the tissue can be calculated as

where *A*_{surface} is the contact surface area between the Fecobionics and the anorectal segment. In other words, the friction force can be calculated from the front and rear pressures, gravity, and the velocity during evaluation of the device.

## The Future of Anorectal Functional Studies

Anorectal testing is directed toward high-resolution technologies that provide physiological data useful for modeling purposes. Mechanical data and models are highly needed since defecation is a mechanical event.

The Fecobionics device provides several innovative features from a bionics point of view when compared to the current anorectal assessment technologies. Such features include (a) mechanical device properties that mimic normal stool, (b) objective electronic measurement of anorectal angle independent of direction/rotation or on interpersonal interpretation of defecographic images, (c) wireless device that avoids wires and tubes that potentially could influence the mechano-sensory properties in the anorectal region, (d) pressure measurements integrated with geometric profile data and bending data, and (e) assessment of length–tension properties from the reconstructed organ shape and pressures during defecation. Fecobionics represents a disruptive technology in its infancy. It is awaiting approval by the Food and Drug Administration and hence is not yet commercially available.

It is envisaged that anatomy-based mechanophysiological models of the anorectum using data input from high-resolution integrated tests will enter the field. The present paper suggests a path for future analysis based on Fecobionics data. Profiling and modeling will have a role in future studies in the diagnosis, monitoring, and treatment of gastrointestinal diseases. This will provide better models for the Human Physiome project.^{2} Recent initiatives such as the GIOME [41] and Esophagiome projects [42] will in time lead to smarter, more precise, and tailored devices and treatments.

## Acknowledgment

Professor Gregersen worked for several years in the lab of Professor Y. C. Fung. This paper build on top of work on the determination of membrane tension coauthored by Dr. Fung [38].

## Funding Data

The Chinese University of Hong Kong (strategic recruitment funding, Funder ID: 10.13039/501100004853).

RCG (Grant No. 14106717).

Karen Elise Jensen`s Foundation and SBIR-NIH R43 DK112543 (phase 1) Grant (Funder ID: 10.13039/501100004046).