Case-study of a user-driven prosthetic arm design: bionic hand versus customized body-powered technology in a highly demanding work environment

Wolf Schweitzer; Michael J. Thali; David Egger

doi:10.1186/s12984-017-0340-0

Research
Open Access
Published: 03 January 2018

Case-study of a user-driven prosthetic arm design: bionic hand versus customized body-powered technology in a highly demanding work environment

Wolf Schweitzer¹,
Michael J. Thali¹ &
David Egger²

Journal of NeuroEngineering and Rehabilitationvolume 15, Article number: 1 (2018) | Download Citation

Abstract

Background

Prosthetic arm research predominantly focuses on “bionic” but not body-powered arms. However, any research orientation along user needs requires sufficiently precise workplace specifications and sufficiently hard testing. Forensic medicine is a demanding environment, also physically, also for non-disabled people, on several dimensions (e.g., distances, weights, size, temperature, time).

Methods

As unilateral below elbow amputee user, the first author is in a unique position to provide direct comparison of a “bionic” myoelectric iLimb Revolution (Touch Bionics) and a customized body-powered arm which contains a number of new developments initiated or developed by the user: (1) quick lock steel wrist unit; (2) cable mount modification; (3) cast shape modeled shoulder anchor; (4) suspension with a soft double layer liner (Ohio Willowwood) and tube gauze (Molnlycke) combination. The iLimb is mounted on an epoxy socket; a lanyard fixed liner (Ohio Willowwood) contains magnetic electrodes (Liberating Technologies). An on the job usage of five years was supplemented with dedicated and focused intensive two-week use tests at work for both systems.

Results

The side-by-side comparison showed that the customized body-powered arm provides reliable, comfortable, effective, powerful as well as subtle service with minimal maintenance; most notably, grip reliability, grip force regulation, grip performance, center of balance, component wear down, sweat/temperature independence and skin state are good whereas the iLimb system exhibited a number of relevant serious constraints.

Conclusions

Research and development of functional prostheses may want to focus on body-powered technology as it already performs on manually demanding and heavy jobs whereas eliminating myoelectric technology’s constraints seems out of reach. Relevant testing could be developed to help expediting this. This is relevant as Swiss disability insurance specifically supports prostheses that enable actual work integration. Myoelectric and cosmetic arm improvement may benefit from a less forgiving focus on perfecting anthropomorphic appearance.

Background

Work specific tasks [1] invariably define specific functional requirement profiles for workers (including prosthetic arms) [2]. Once a personal preference has expressed itself in the form of particular work choice, and once a person has acquired extensive experience and skills in a particular field, particular technical necessities often follow with little further options [3]. Then, various prosthetic solutions may be thought to be competing for better performance when in fact, the choice-dependent hard requirements for a viable prosthetic solution have already set the stage. Primarily, any competition seems to boil down to body-powered versus myoelectric technology [4]. Within body-powered control systems, voluntary opening (VO) and voluntary closing (VC) devices offer different profiles [5].

Assessment of current state and developments of prosthetic arms presented here has one particular aim. That aim is to enable the first listed author of this paper^{Footnote 1} to keep working, at the front, within one of the most modern forensic pathology institutes and projects [6]. Our focus, therefore, is the occupational rehabilitation for one particular profession. Since 2008, the first author develops, tests and refines solution oriented prosthetic arm components (as detailed in this case study)^{Footnote 2}.

With a generic task choice based on ADL (activities of daily living), the CYBATHLON 2016 [7] had provided a competitive demonstration of prosthetic arms in October 2016 in Zürich, Switzerland. There, competitors wearing prosthetic arms attempted both fast and precise manipulations performing light activities. A televised public arena setting [8] provided for a certain degree of intensity and stress. The winner wore a body-powered arm; the myoelectric arm users filled the remaining ranks.

Intensity in physically demanding tasks, such as discussed in this paper, will be a lot greater along more than one dimension. Dimensions include wider ambient temperature range, longer duration of work, heavy sweating and far larger pull or push weights. There is also a more existential aspect of manipulation content, i.e., an accidental drop of an expensive camera is penalized more unforgivingly than not winning a medal.

In this paper, we will employ the term “physically demanding work” (PDW) to denote physically intense, repetitive, hazardous, demanding, unforgiving, critical and otherwise extensively bi-“manual” work. It demands undivided attention, it does not provide extra time to troubleshoot the prosthesis, and it requires full reliability for pull, push, lift or grip manipulations [9].

What is the current requirement for prosthetic arm technology?

Individual job assignments determine tasks the arm amputee has to solve, and that their prosthesis must address. The majority of acquired adult major arm amputations are traumatic unilateral below elbow amputations (UBEA) (77% in [10]), with a predominance of blue collar^{Footnote 3} workers. In that community, occupation-specific manual tasks tend to be hazardous, repetitive, strenuous and hard [1, 11, 12]. These tasks then also should be at the core of rehabilitation; if they are not, unemployment and a need for re-schooling risk to follow [3].

The aspect of PDW is not likely to go away. Even in the light of ongoing automatization and technological advance, athletic, physical and manual skill requirements remain relevant while the demands for an extreme degree of fine manual skill is not excessive [13, 14]. Priorities are high reliability concerning device integrity, reliable control under physical strain even with sweaty skin [15] and reduction of overuse or asymmetry problems under full load and over time.

Evaluating the impact of wearing a prosthetic arm on overuse and asymmetry may require load and hazard stratification. There are studies that discuss overuse and asymmetry consequences [16, 17], also in the context of wearing a prosthetic arm [18–22]. They do not address the fact that for very intense work, it may make a significant difference for that individual whether a prosthesis is worn that actually supports intense work, and whether the individual trains to keep fit for that job.

One particularly exposed group of workers are farmers. They report a high degree of exposure with wide ambient temperature ranges, corrosive or damaging liquids, particles, biological and chemical contaminants as well as extensive wear and tear of general work. The exposure goes so far beyond the usual prosthetic technician’s scope that the authors of one farmer focused study called it ‘extraordinary’ [23].

Activities of daily living (ADL) such as putting on overalls, folding clothes, reading a newspaper, loading a vehicle with equipment, drinking water from a cup, showering or preparing a meal do require some degree of manual dexterity [24]. The same manipulations that make up the ADL inventory find themselves in considerably more unforgiving industrial variations across hazardous occupations, where they are performed with high frequency, with high load, under heat exposure and with far less tolerance as to errors [25]. A UBEA may well be able to provide full-time PDW by, e.g., repairing bicycles, working in a gastronomical kitchen, or, providing biology laboratory work. That individual then will be delivering adequate “motor performance” in a demanding environment. That person is not likely to experience any functional deficiencies concerning the more limited scope of “motor capabilities” required by ADL [26].

This is illustrated by the CYBATHLON 2016 Arm Prosthesis Race that was won by a 67-year old pilot equipped with a body-powered TRS Grip 5 Evolution Prehensor. That is a light build of the TRS Adult Prehensor, which features a metal frame. These VC devices allow for any grip between very subtle careful handling e.g. of a light bulb or an egg [27], up to regular and long term usage of shovels or picks or handling of heavy weights. Body-powered VC control transmits adequate proprioception [28], particularly as to grip strength, even under heavy sweat. At the CYBATHLON 2016, a light version of a body-powered prosthetic arm system fully geared towards PDW requirements made ADL-optimized systems pale within their own application domain.

Current prosthetic arms are weak especially in supporting industrial work such as machining, processing, and construction. After suffering an arm amputation, the category of workers formerly employed for heavy work is related to the highest fraction of industrial workers changing jobs [3]. However, re-schooling is both costly and risky as it can have serious complications (such as depression, increased divorce rate or increased mortality [29, 30]). Depression is already prevalent among arm amputees [31] and it adds to complicating prosthetic rehabilitation [32].

By law, insurances usually are restricted to financing cost-effective prostheses. Cost-relevant aspects are both the ability to return to work, where applicable also heavy work, and long term health in context of the prosthetic costs^{Footnote 4}.

The current requirement for prosthetic arm technology is to work particularly well under realistic conditions where bi-manual work is mandatory. These typically comprise high exposure and low failure tolerance.

What is the current acceptance for prosthetic arm technology under these requirements?

In the best case, a conventional prosthetic arm offers marginal functional improvements [33]. Subgroup rejections are reported to be as high as 59% (for amputations close to the wrist [34]) or 75% (for myoelectric prostheses [35]). As opposed to reported figures, realistic rates for rejection and non-usage have been estimated to be even higher due to absent contact between the clinic community and non-users [36]. A non-response following unsuccessful purchase as entity is generally kept proprietary and not released in the public domain, whereas 40% of dissatisfied customers were estimated do nothing about it and only 5% escalated their complaint to management [37]. The underlying mechanism likely is a significant degree of mutual disengagement [38, 39]. It therefore can be assumed that most arm amputees, particularly those that do not submit to heavy work, reject prosthetic arms.

The situation will be different for workers. Generally, across various physical activity levels of jobs, over half of the employed workers with amputations identified negative repercussions of their amputation, and one quarter employed at the time of the study had experienced unemployment lasting over six months since their amputation [3]. The lowest percentages of workers returned to “heavy” or “very heavy” work while the trend was that 75% of employed amputees returned to jobs that were less heavy but required greater intellectual ability [3].

A body-powered split hook or prehensor [40] dominates in successfully supplementing most users that are involved in PDW [3, 41–43], and not a myoelectric arm. If one focuses on body-powered technology and on adult below elbow amputees that are in the work force, one study [44] reported 10/10 of below elbow dominant arm amputees and 17/19 of all below elbow amputees having become users during a study period of 7 years. In another study, body-powered arms supported a majority of workers also delivering heavy variable work in excess of 8 hours per day [45], while work load as well as popularity was considerably lower for myoelectric or passive arms. This has not changed since the invention of myoelectric prostheses [44, 46].

Forensic medicine as a work environment

This section describes technical aspects of forensic medicine field work, office and laboratory work. It is physically and technically demanding. Requirements exceed the usual scope of amputee rehabilitation [47]^{Footnote 5}.

Routine death scene investigations involve handling, maintenance, cleaning and transport of equipment, They include carrying equipment also to remote locations. There is handling, undressing, turning and moving of bodies across the human weight range. Work is performed personally by the forensic pathologist, with a specific goal to not place new injuries on the body (Fig. 1). Work also entails bi-manual instrument handling and evidence collection (forceps, scalpel, dissection, syringes, swabs), One may have to manipulate fragile, putrefied, slippery or severely injured bodies and disjunct body parts. External factors may be wide ambient temperature ranges, fluid or gaseous biohazards, 24-h on-call work and wearing full body protective overalls. One requires a 24/7 fitness to drive at all weathers. The job entails associated heavy sweating [48]. In our institute, physical requirements have increased slightly over the years for the forensic pathologist as both average body weight [49] and deployment rates have gone up.

Potentially prosthesis-critical tasks for forensic field work, laboratory work and office work are summarized in Tables 1 and 2. The job description knows no specific requirement regarding which upper limb performs which work step. There is no explicit requirement or regulation as to wearing a prosthetic arm or using a particular terminal device. However, control and suspension issues as well as grip-specific differences result in different success rates across terminal devices (see Tables 1 and 2). Lack of bi-manual support is problematic for large weights and for some technical examination and handling steps.

Table 1 Prosthetic suspension, control and overall prosthesis related observations

Full size table

Table 2 Terminal device related observations

Full size table

Death scenes / field work

Retrospective evaluation of occupational aspects covered WS’ most recent 48 consecutive cases (notes, protocols). Duration of on-site work (deployment) ranged from 0.5 to 6 hours. Ambient temperature range was -14,5 to +30,3 deg C. Manner of death included mechanical violence with suspected homicide (10 cases), suicide (11), accident (5) and natural or poisoning (22). Weight of bodies was 77,5 (median; range: 50-130 kg). Manual handling of a body was aggravated by the body’s skin not being dry and clean (as it was in 21 cases): putrefaction (5 cases), charring/burning (1), significant amounts of blood (8) and slippery skin (13) due to various reasons (e.g., water). His own sweating being an actual issue for the investigator was noted where his clothes started to become soaked (dripping) (see Figs. 2, 3 and 4); there, breaks had to be taken to pour out excessive sweat from the prosthetic liner. Massive sweating for this protocol was defined as standard upper body clothing (two layers: T-shirt, long sleeve shirt) being still visibly wet after around 30 min after the effort. No easy to apply objective heat exposure rating exists, but subjective rating which we used for this report has been shown to be just as effective [50, 51]. Physical strain was typically not restricted only to WS in his role as field forensic pathologist: other specialists, such as forensic scientists, all working in protective gear, were usually soaked, too. A manual skill level (MSL) was subjectively judged to range from 1 to 10, with 10 being difficult given experience (similar to Task Difficulty in [52]). MSL has been rated higher for higher body weights, the presence of single pieces of evidence to be handled below ∼ 3 cm diameter, tight clothing on the body, narrow or tight space, and wet or slippery surfaces. Clean/dry bodies averaged an MSL of 4.2 versus an 8.3 score for non-clean/non-dry bodies (Wilcoxon p< 0.0001). Clean and dry bodies were substantially more frequently part of the natural or poisoning manner of death, whereas accidental, suicidal and suspected homicidal death cases (working categorization) contributed to significantly more bodies with a non-clean body surface (Chi-Square p = 0.009). The working categories of manners of death (in a sequence of decreasing average MSL) were suspected homicide, accident, suicide, and natural or poisoning (Fig. 3). Massive sweat issues occurred (in decreasing percentage of cases) in suspected homicides (100%), accidents (80%), suicides and natural or poisoning cases (about 50%). The necessity to undress a body was noted as a factor for all death scenes where the body was found not naked. All numerical results were non-normally distributed. Further documentation was obtained using a socket mounted video camera. That work caused collateral efforts, including exposure to relevant weekly laundry volumes. Additionally, clothing was state of the art professional work gear that was adapted to the environment, including shoes with safe soles and zipped with lock laces, battery heated switchable jackets for winter and evaluated protective clothing for critical death scenes [53].

Office, research and laboratory work

(1) Typing: our department^{Footnote 6} issues all forensic and medico-legal output, quality management, accreditation, correspondence, course and education related as well as scientific work, in typed-up form. This task may require 8 to 10 hours a day of constant text creation and editing. Voice recognition is not always an option. (2) Research and laboratory work also requires handling of small, slippery, expensive or fragile objects. These may comprise containers, substances, tissues, glass slides, cameras, scanners, microscopes, pump devices, large containers with special liquids, and at times must not be contaminated during manipulation. A “no failure” requirement exists for most grasp, transport or other manipulation tasks regarding falls or drops, spillage and other handling accidents such as contamination. (3) Meetings, presentations, negotiations. There, a prosthetic arm may be expected to “hide” the potentially visually offensive handicap, to reduce distraction and allow others to better focus on any relevant topics “at hand”.

Mapping of forensic medicine tasks to academic tests of prosthetic arms

Outcome evaluation of prosthetic arms was performed with a focus to the PDW aspects outlined here. No previously published academic tests were employed, mainly because they do not adequately reflect the intense level of exposure in the user domain and are thus irrelevant for this application domain. The Carroll test specifies a range of objects (weight range 0,34 to 576 grams; size up to 10 cm) for manipulations as prosthetic gripper performance indicators [54], whereas for PDW, a wider weight range in a broader range of shapes are the norm. For the Carroll or SHAP test, the user is placed in a chair in front of a table whereas in PDW situations, manipulating or holding activities occur from various body positions and also dynamically. The descriptions of SHAP objects (coins, buttons, food, jar, jug, carton, tin, jar) [55] as well as clothespins [56] do not claim specified or standardized shapes, dimensions or forces. However, these tests also are largely irrelevant for many actual prosthetic arm use situations due to conceptual issues. That is not a common problem for all prosthetic limbs: with relevant device performances along just a few metric dimensions, prosthetic leg components can be evaluated with well-defined tests [57].

As opposed to that, ADL confront the daily prosthetic arm user with a complex range of non-formalized [58, 59] manifestations of cultural artifacts (e.g. [60, 61]; “endless variations” [62]; “(..) designs things that are easily and inexpensively manufactured” [63]). One particular example for a culturally and practically relevant ADL that evades technical standardization is the opening of a jar by turning its lid: the SHAP instructions state that “the lid should be placed on the empty glass jar and tightened only with sufficient force as would be expected for everyday use/self storage” [64]. Now, the televised footage of the CYBATHLON 2016 showed one pilot failing to open a jar lid using an iLimb prosthetic hand [8], so obviously, force is a key issue here. So, it will be of essence who closed the lid and how, with remaining uncertainty: lid closing or opening forces vary widely because when applied to jar lids, grip torque ranged between 0.86 and 6.56 Nm, across sex, age and grip type used [65, 66]. The high dimensionality of grasp-object-situation spaces thus may ideally be reduced for relevant (rather than highly collinear [67]) situation, grip and object specifications particularly in the context of work-specific prosthetic arm use [68, 69].

Relevance in the context of testing prosthetic arms meant for work integration can, logically, only apply to work relevant function. For the currently known clinical prosthetic arm tests, the test user is not explicitly designated or meant to sweat, to walk an hour carrying equipment beforehand, or to handle slippery bodies of a median weight of 77kg. Published tests also lack serious penalties of PDW. In real life, one cannot just drop expensive equipment such as cameras without expecting a relevant penalty. Thus, we applied a “not acceptable for this line of work” judgment for some performance failures (see Table 1). So the current lack of applicable scope with conceptual lack of relevant standardization imply that reports such as this – referring to what may seem to be non-standardized situations such as death scenes, office or lab work – will be at least equally relevant from a testing perspective for the interest groups related to prosthetic arms (see also “Discussion” section).

Methods

Description of problem domain

Body-powered technology

The medical care official of the employer was aware of the first author’s disability. Before user driven developments (see below) were initiated, we saw considerable problems in the work usage of prosthetic arms.

Work typical grip frequencies would wear down conventional cable sheaths with cable breaks, typically within 4 to 10 days, due to friction, also causing down time of a few days up to a week until repairs could be made. At that point, only terminal devices with manufacturer loaded springs (Otto Bock (OB: Otto Bock, Duderstadt, Germany) hands or split hooks) were used (and not devices with the option of user defined increase of grip strength and cable loading). Thus, the cables were only exposed to manufacturer limited loads.

The first two years after below elbow amputation in 2008 saw at least 46 prosthetist appointments of about 3 h each, including travel, mostly for cable repairs. On top, the user conducted a considerable number of cable replacements by himself. An informal survey across local and international prosthetists indicated that there was no current technical solution available to remedy cable shredding effectively, and no solution was available to order or even just to test.

Terminal devices and the wrist connector failed at various points. An OB double cable hand (model 8K24 [70]) irreversibly jammed within minutes of first use. An OB single cable hand (model 8K22) would break within a few months, and after replacement, with the same type of mechanism failure. An OB MovoWrist (model 10V39) irreversibly jammed within seconds of first use. An OB Rachetless Wrist Joint (model 10V10) with a spring fixing a threadless stud (model 10A44) would dilate over a few months and lose function. Various OB hook models exhibited a range of problems, containing temperature dependent jamming, hook joint wiggle, or breaks of steel cable connections. Terminal device adapter bolts did not exhibit the same diameters across instances but varied significantly, according to our own measurements (OB model 10A44), so some studs were not fastened, others jammed the wrist mentioned above (OB model 10V10).

The components had most likely not been designed for PDW. As one example, the wrist product sheet (OB model 10V10) [71] declared that the wrist component was intended for everyday use but not for extreme sports such as free-climbing. It had not become clear what the difference was between lifting part of another body’s weight (an everyday activity in forensic medicine) and part of one’s own body weight (climbing). An informal user survey showed that other commercial quick adapters for wrist units also tended to wiggle early into heavy use. A failing prosthetic wrist connector as weakest link, therefore, was a small part in a larger picture. Contact with commercial providers did not indicate availability of any better wrist adapters and thus initiated user driven development of a newly built wrist and adapter setup.

Wrist instability, carpal tunnel syndrome, double crush injury with plexus compression and episodes of lateral elbow epicondylitis of the anatomically intact arm warranted physiotherapy treatments. A dermatologist was involved in reviewing the liner and socket revisions required to address congestion eczema. Neurologist, orthopedic surgeon and radiologist consultations were performed as the user initiated the development of an insurance funded custom shoulder brace.

Myoelectric technology

Based on pre-evaluation, promotional and technical assertions, stump length, hand size and wrist connector considerations, a myoelectric iLimb Revolution model (Touch Bionics, Livingstone, UK) was acquired. Early tests using myoelectric technology had failed due to the hard socket not providing reliable skin contact when exceeding pull forces over ∼ 2kg, exacerbated by sweat. When the myoelectric socket was fit tightly for better slip control, excessive bruising occurred above the elbow. With very narrow liners or sockets, slips could be prevented, but severe stump pain ensued due to boney rather than soft tissue covered elbow region; also, socket-imposed elbow motion range restrictions rapidly caused shoulder muscle overuse. Extensive variations of technical suspension aspects with different hard socket designs or custom silicon liners were not successful during intensive development and testing over about four months. Dry skin [72] contributed to low myoelectric contact quality, requiring repeated re-adjustment with the liner skin interface during usage.

Funding

Insurance funding was obtained for both body-powered and myoelectric technology, including various custom silicone liners as well as custom-built shoulder brace and custom-built wrists. In addition, the first author so far privately invested about 6’000 CHF in myoelectric socket and technology trials and 2’000 CHF for supplementary body-powered components, supplementing insurance funding. Costs were kept down and time spent on revisions was low by re-using or scavenging of all those components whose life span exceeded the life span of the prosthetic arm as a whole [73]. User driven repairs evolved into user driven prototype designs. Also as a result of that, the initially integrated build and design of the body-powered prosthesis became modular.

Training aspects

There was considerable dedicated training particularly for the myoelectric arm, including a number of full day workshops for prosthetic use hosted by Balgrist Tec^{Footnote 7}. There was physiotherapist initiated home training, whereas whole areas - kitchen, laundry zones, garden work, car washing - were designated to train prosthetic use in a drill type fashion. Myoelectric arm training had been performed for about three years, body-powered use exceeded over four years in the current configuration.

Muscle power to provide the necessary grip, push or lift forces for body-powered technology was no issue. The first author keeps reasonably fit by performing regular and extensive sports routines. This effort is in line with performing a physically demanding job.

Choice of user driven innovations

Several prosthetic technicians, manufacturers, developers, and researchers had been contacted throughout the years in search for solutions for various problems described here. The first author of this study furthermore personally cooperated in a considerable number of prosthetic arm related research and development projects [74–81], also as a volunteer for feasibility or pre-test examinations.

Despite a wide ranging search, no solution to the failure of prosthetic components under PDW loads became apparent. User initiated development was chosen as the logical solution to address the known technological deficits [82], yielding the solutions specified here.

Prosthetic arm comparison, training and assessments

We compared a “bionic” myoelectric iLimb Revolution (Touch Bionics, Livingston, Great Britain) (TBI) and a customized body-powered arm (CBPA). The CBPA contains a number of new developments initiated or developed by the user, whereas the last author assembled the prostheses. Both systems underwent extensive trouble-shooting and problem resolution. On the job usage of both technologies over a few years was then supplemented with dedicated and focused intensive use of these devices for 12-14 hours a day for two weeks under PDW conditions.

During that period and later, due to various reasons, all work also had to be performed without prosthesis on, resulting in similar work exposure for non-use of a prosthetic arm (see Tables 1 and 2).

Grip strengths were measured with a Camry 200Lbs/90kg digital hand dynamometer (Camry, Kowloon, Hongkong). Noise assessment with mobile phone application in non shielded quiet cellar room on a soft padded sofa (base level <1 dB, mean difference to reference method ± 2 dBA [83]) (Sound Meter Pro 2.5.2, Smart Tools Co, on cell phone Huawei (Huawei Technologies, Shenzhen, Guangdong, China) under Android 7). Statistics and diagrams with JMP (SAS Institute, Cary, NC, USA). Socket side videos captured with Mobius ActionCam / Innoovv C3 camera (same camera type; Innovv, Hizhou City, Guangdong, China).

Characterization off-shelf myoelectric technology / TBI problems

(TBI-1) sweat interference with the electrode function of the TBI with electrode malfunction after 10 minutes [84, 85] (3 trials, see Fig. 2 for context) and in context of sweat, decreased tendency of suspension to support heavy weight lifts or pulls; (TBI-2) glove durability: gloves would deteriorate to the point of requiring replacement as early as after 10 min of car washing [86, 87] or when left alone [88], without option to use gloves not issued by manufacturer [89]; (TBI-3) limb positioning interference with grip function causing inability to let go or hold grip [90, 91]; (TBI-4) general lack of reliable electrode function [85] and disconnection of electrodes with excessive pull [92]; (TBI-5) weak grip and weak hand (with low hand weight and low grip force being mutually exclusive constraints) [87] as issue for some (but not all) body transport or laboratory work; (TBI-6) lack of reliable precision grip and within-grip-activity change of grip configuration [87, 93] due to uncoordinated iLimb hand motors with the only synchronicity being simultaneous start and stop; (TBI-7) mechanical skin blisters after 10 hours of wearing the TBI for office work [72, 94]; (TBI-8) center of gravity (COG) too distally located causing painful shoulder and elbow tension after a few hours of typing already [87]; (TBI-9) irreconcilable use vs. warranty issues such as risk to inflict damaged cover, risk to use tools not “approved” by Touch Bionics, risk to exposure to moisture, dust or vibration [82, 89] and (TBI-10) problems with battery function at colder ambient temperatures ranging down to -15 deg C [95]; (TBI-11) Loud / irritating noise that distracts others (1) in meetings and (2) when working in the office or at home, emitting up to 72 dB [96, 97] and (TBI-12) use with a low degree of sweat but no control disruption over a whole day incurred electric burn type skin injuries with tiny blisters that took about six weeks to heal (encountered twice) [98–100].

Characterization off-shelf body-powered technology/ CBPA problems

(CBPA-1) Cable tear down every 4-10 days using Otto Bock (OB) standard components [70, 87] with particularly rapid wear down of components of cable housing or sheaths. (CBPA-2) Prosthetic wrist unit spring dilation and insufficiently large diameter variation range of adapter componentry caused the start of an irritating wiggle after a few weeks and loss of bolt fixation after two to three months [87] (both cable and wrist are well-known points of failure of body-powered arms [82]). (CBPA-3) Nerve compression using figure-nine harness (F9H) after prolonged usage of grippers with high voluntary opening grip forces [101] causing carpal tunnel syndrome in a double-crush injury constellation (there, radiologic, orthopedic and neurological examinations were obtained) [102, 103] (Fig. 8). (CBPA-4) Friction/sweat rashes occurred every 1-2 weeks, forced a pause from wearing the prosthetic arm usually for 3-5 days and required treatment; Ossur Iceross Upper-X liners caused congestion eczema at the end of the stump due to a mismatch of a more cylindrical liner shape and a more conical stump shape [72]. (CBPA-5) Frequent deterioration of grippers of OB (hands, split hooks) caused repair down times. (CBPA-6) On top of the cable sheath as point-of-failure also orthopedic cable clamps (OB, 10Y3, the only cable clamp offered for both nylon and steel cables) appeared to prematurely damage steel control cables (21A 4=2), starting with early single wire breaks, to the point of sudden cable rupture usually within less than two weeks of use.

Solutions for body-powered arm and user-driven modifications (CBPA)

The CBPA was built with a carbon fiber socket, a pin-lock (Icelock, Ossur, Iceland), a lamination ring (OB 11D20=50), and a coupling used for quick connection of terminal devices (OB 21A7). Extensive user driven innovation was employed here (Figs. 5, 6, 7, 8, 9 and 10). A particular goal was increasing performance and reliability while reducing cost (which includes wear-down, repairs, replacements and down time). A modular rather than an integrated build was achieved to also allow for user accessibility, repairs, and component or part exchange. The cable control unit was fixed to the socket with just two screws. The cable or sheath exchange now can be done by the user without having to wear another prosthesis. (CBPA-1) The cable mount was modified to incorporate Bowden cable principle on flexible soft body curve shapes. The design introduced nonlinear rather than unilateral curved force distribution [104, 105], see Fig. 9 9 B/C and Fig. 10, with maximal cable force delivery exceeding 250N and unserviced operation of up to 9 months under described work conditions. Steel rather than perlon control cables were used for higher strength. Cable sheath material were Shimano pre-lubricated brake cable sheaths (Shimano, Osaka, Japan). At the end of the lifetime of the cable sheath, the cable deterioration would announce itself over hours or days rather than causing sudden rupture. For this, the sheath ends were regularly checked for visible sheath wire breaks. (CBPA-2) A quick lock steel wrist unit “PUPPCHEN” was developed after WS’ specifications [106] (Figs. 6, 7, 8 and 9) allowing an unserviced use of at least four years under described work conditions. A low profile fit was necessary to avoid excessive length. Wrist materials were aluminum (cover/lid) and Ramax (Uddeholm, Düsseldorf, Germany). Within the domain of withstanding hazardous conditions, a first prototype of our wrist featured a helicline mechanism; that was not sensitive to sand or dust, but only allowed for six discrete rotational settings. The current version is more sensitive to sand or dust, but allows for continuous rotational positions, while requiring cleaning of the lock mechanism after four years. (CBPA-3) A cast shape modeled shoulder anchor (CSMSA) was developed to avoid nerve compression typical for conventional F9H. The CSMSA shifted the harness pressure point from a soft compressible area of ∼ 15 cm² in the anterior axillary fold overlying the brachial plexus to an area exceeding ∼ 60 cm² overlying the less compressible deltoid muscle and shoulder. That decreased the required arm extension to open the gripper from around 12-15 cm (F9H) to around 5 cm [107] (Fig. 8). This significantly improved postural changes required to open a voluntary opening or close a voluntary closing device. It also allowed for relatively heavy overhead work. The carpal tunnel syndrome incurred by F9H afterward almost fully resolved by itself despite ongoing work. Insurance funding was obtained for this. – No particular innovation by the authors was necessary when improving upon the following problems: (CBPA-4) Suspension inherent complications (congestion or friction) on the stump were dramatically improved by modifying the liner layering. We employed a soft double layer whereas a tube gauze (Tubifast, Molnlycke, Norcross, Georgia, USA) is worn on the skin, underneath a gel liner (Ohio Willowwood Alpha liner), initiated by DE (white sock like parts in Fig. 9 b). (CBPA-5) The improved device choice contained Hosmer split hooks (models 5, 5XA, 6(containing a user-tweak [108]); Hosmer, USA), V2P (Toughware PRX, USA), Adult Grip Prehensor 3s (TRS, Boulder, CO, USA) [40] and Becker hands (Becker Mechanical Hands, USA). Cooperation of WS with Bradley Veatch when developing the V2P [74]. Support by John Becker on grip force tuning issues of the Becker Hand [109, 110]. These devices were equipped with gripper surface modifications to enhance grip performance [111]. (CBPA-6) Consultation with wire mount specialists was obtained for adequate steel cable rigging. This included protection using softeners and avoiding sharp bends, corners, adequately sizing sling eyes and correctly mounting clips. In that context, orthopedic cable clamps (OB model 10Y3 [70]) were replaced with regular cable thimbles and cleats [112].

Revised cable sheath mounts and adequate steel cable rigging avoided shredding, extending un-serviced cable lifetimes to over nine months under full load. In conjunction with the shoulder anchor, grip strengths for both VC and VO devices were increased. All materials worn directly on the skin were chosen for optimized stain and odor behavior. A shift towards modular design shortened repair times from a week to 1-2 days for critical repairs.

Solution for myoelectric arm (TBI)

Ultimately, the TBI was mounted on an epoxy socket via a fixed wrist adapter due to length constraints (stump too long to fit a powered wrist) and a lanyard-fixed liner (Ohio Willowwood, USA) containing magnetic electrodes (Liberating Technologies, USA). Hard double layer sockets had failed due to thin skin around elbow and rapid extensive bruising. Custom liner solutions failed due to elasticity restrictions of processed materials (liners were either too narrow causing pain or too wide, not providing effective suspension). Battery placement was towards the elbow for a less distal COG. (TBI-7) Mechanical skin damage was mildly improved with the gel liner.

No further improvements resulted due to both inherent technology limitations (ILT) or manufacturer’s restrictions (MR): (TBI-1) Sweat interference and skin effects as well as ILT. Larger weight lifts or pulls causing shift or detachment of suspension ILT. (TBI-2) Glove durability ILT. There were no manufacturer approved durable gloves, whereas thicker gloves would significantly impede the already low grip power. (TBI-3) Postural interference ILT. (TBI-4) Lack of electrode reliability ILT. (TBI-5) Raw grip weakness ILT. A stronger hand would be even more excessive in weight. Preliminary tests with nitrile covered work glove were successful as to improving grip, but could not be sustained due to warranty restrictions MR (TBI-6) Grip issues due to both uncoordinated motor control and free thumb swivel MR. (TBI-8) Distal COG caused muscle strain problems ILT. This issue had been addressed by proximal battery placement already from the beginning. (TBI-9) Warranty issues MR. (TBI-10) Ambient temperature range was influencing battery function ILT. (TBI-11) Noise reduction was reported to resale agent but never remedied (thus classified MR). (TBI-12) No solution available ILT.

Technology advantages weighed against each other

Posture and sweat interference for the TBI and grip geometry issues lead to failure of static holding requirements (TBI-3) in a workplace that generally is not set up to gracefully accept object drops.

The TBI suffered electrode malfunction and causes skin injury in sweaty situations which are a typical condition in this line of work (TBI-1, TBI-12). A weak grip force (TBI-9) was not always problematic, but it could be improved by using grip surface enhanced work gloves such as nitrile covered textiles. Due to warranty restrictions this was not a viable option.

Office work remained difficult due to mechanical damage of stump skin (TBI-7) when typing vigorously which, however, did not occur when wearing a tube gauze layered liner and light split hook of a body-powered arm (CBPA-4).

Physical and chemical exposure remained a tangible threat to the TBI hand that could only be equipped only with fragile gloves (TBI-2, TBI-9).

Pulling weight was not possible very well for some situations when handling bodies with the myoelectric arm (TBI-1, TBI-5) but could easily be achieved with an improved body-powered arm (CBPA-1, CBPA-2, CBPA-3, CBPA-4, CBPA-5).

TBI prosthetic arm malfunction often required a systematic troubleshooting approach [113] entailing access to and removal of the socket, fixing electrode positioning or re-placing liner. During PDW deployments and when wearing protective gear, that was disruptive and time consuming. CBPA advantages were a close, snug, swift and immediate feel to the dynamic integration of the prosthetic control into body motion and a reliable function under all work conditions, as predicted by physiotherapists.

An attentively observed and tested TBI property was not so much its adaptive grip (a body-powered mechanical Becker hand [109, 110] has that as well) but the option to define and switch grips. With the option to passively rotate the TBI thumb or set finger position, an extra practical advantage for the application of automatic grip switching did not emerge; however, the on/off-switch was used often to block hand configuration or grips.

Other use than work and further developments

Once improved and tested for heavy, intense and extensive loads for workplace application, the resulting CBPA was also used for intensive applications outside work. It was used for bicycling (highlights include Stelvio pass, moutain bike trips also in deep winter with spike tyres, using various bicycle adapters), garden work (∼ 2 h over 35 deg C ambient temperatures) as well as transporting and mounting furniture (up to total weight of ∼ 550 kg materials with single package weight up to ∼ 55 kg). No damage to the CBPA or skin rashes were noted even for that type and extent of usage.

Both body-powered and myoelectric systems remain under further development regarding problem identification and solution, and both systems remain in regular use, although with different frequency. Both systems are undergoing further developments.

Results

Quantitative aspects

Grip strength of TBI ∼ 1,6kg. Grip strength of CBPA: Hosmer work hook ∼ 5kg, TRS Prehensor ∼ 25kg. Grip strength of anatomically intact hand ∼ 47kg (above upper tertile for bimanual males at similar age [114]).

TBI weight 1030g (895g socket, battery, wrist and terminal device; 135g liner with electrodes, COG ∼ 6 cm distal to stump end. CBPA weight 755g (630g socket, wrist and Hosmer model 5XA split hook device; 125g liner;), COG ∼ 3cm proximal of stump end. Weight of single CBPA terminal devices: TRS adult prehensor 3s: 393g; Hosmer 5XA: 139g.

Qualitative aspects

Side by side comparison of overall usage experience (Table 1) and a more detailed terminal device appraisal (Table 2) shows that the CBPA provided more reliable, comfortable, powerful, light-weight, cost-effective service with less maintenance.

Most notably, CBPA grip reliability, grip force regulation, grip performance, center of balance, component wear-down, sweat and temperature independence as well as skin state were good. These results were mostly derived from wearing these devices for 12-14 hours a day for two weeks under PDW conditions while monitoring effects closely.

The option to switch VO and VC for body-powered arms introduced a breadth of control paradigms that was unmatched by myoelectric control. Terminal device swap from VO to VC control was preferably done after loading the car and driving to the location, and before going into examining a body (see also Table 2 for best terminal device performances). There was no overall single best terminal device for the CBPA if one optimizes for full performance. That was why the user driven wrist design had to allow for frequent quick swap of devices with full connector reliability. Increased grip performance by adding soft layers of materials weighed against the need of having to replace them frequently.

Overuse and asymmetry aspect: Severe shoulder and neck pain after office work (typing reports) with TBI already after 1 day; severe shoulder and neck pain using CBPA less accentuated, slowly building up over weeks and months under regular work loads, with about 4 critically painful days per year. Bi-manual support with body powered arm, particularly for heavy weight lift and handling, was supported best with VC device (see Table 2), resulting in perceptibly less tendon and muscle strain for the anatomically intact arm. Some laboratory work when assembling a series of device parts was further supported with a bench vice. Left arm wrist: chronic instability, pain severe after heavy one-armed lifting, significantly better when being able to use prosthetic arm. Left arm elbow: lateral epicondylitis, best addressed by sharing load for many repetitive tasks across both arms.

Skin: Blisters and rashes with relatively long healing time (up to 6 weeks) for TBI; rapidly healing friction rash with CBPA slowly building up over continuous heavy use after 4-5 work days with definitive need for a break of 2-3 days after continuous use of about 10-14 days.

Temperature: no control failure for CBPA even at very cold ambient temperatures.

Discussion

We initially encountered severe problems with both current body-powered and myoelectric technology. These were found to be not unusual as a general consumer experience. Subsequent prosthetic arm rejection is a logical and typical user reaction [115, 116]. Myoelectric technology may have a relevant role in supporting amputees with restricted capabilities to drive body-powered arms, including higher level amputations. But as stated initially, this article addresses the requirements for a particular intense work application from view of a UBEA.

In this instance, expert user driven innovations under permanent, intense and continuous testing on the job [117] resulted in the necessary improvements to achieve such a prosthesis.

Consideration of requirements of different interest groups

Tense contrasts exist between promises, hopes or predicted failures on the one hand, and technical realities on the other hand. The fact that current myoelectric technology lost the Arm Prosthesis Race of the CYBATHLON 2016 against body-powered technology contrasts with high hopes and promises going with the new “bionic” hands [7, 42]. The fact that body-powered prosthetic split hooks can be powerful prosthetic aids contrasts with the problem that they are vilified [32, 118, 119]. These contrasts affect various interest groups that relate to prosthetic arms differently.

UBEA often find that for ADL or light work, the stump is the best prosthesis [120]. In the age group 2–20 years, UBEA without prosthetic arm outperformed both wearers of prosthetic arms as well as people without disability for ADL across freely distributed bimanual tasks [121, 122]. Prosthetic arms are not of proven value to help psychosocial adjustments [123]. Moreover, arm amputees may regard not wearing a prosthetic arm as part of affirming a public image of different ability [124] particularly in the light of social pressure. The prevalent non-usage of prosthetic arms may be the best functional, economical, proudest and thus rational choice for ADL and light to moderate work [10].

Users that expose themselves to their devices may end up as the ultimate experts [4, 118]. They try to get their consumers’ complaints to be taken seriously, but there may be powerful social and neurological mechanisms that prevent this [125]. The bare arm amputee risks to upset others visually so much [119, 126], that expensive gadgets have now shifted towards the center of a sociological demarcation process [127]. Thereby, societal mechanisms exert a strong push towards amputees to stereotypically cover their stigma [126, 128]. Conversely, the few amputees that do feel personally concerned by that push may offer to comply with that request by exclusively accepting expensive or futuristic-looking rather than functional technology [129–131]. Within that discourse, raw mechanical functionality risks to deteriorate from being a core property to being, at best, a superficial label, while affinity-driven product ratings [132] may risk to distort public perception of their advertised (but not actual) technical performance. In a further twist of society attributing stereotypes, amputees wearing “bionic” hands risk to be perceived as “cold” and as “high-tech”, and thus as a social threat [133].

Families of amputees or prosthetic technicians have assumptions regarding the role of prosthetic arms that differ from those of amputees [123], as do engineers [134]. Current prosthetic arm research and development mainly focuses on myoelectric [118, 135, 136] technology and, more recently, 3D-printing [137]. If nothing else, these devices are marketed to conform to the requirement of a social standard of costly modern technology [32]. Myoelectric and 3D-printed arms are thus assumed to support at least light work or ADL. But only 23% of the users rated the weight of a myoelectric hand as acceptable [138]. Only 12% of the male users found the noise of their myoelectric hand to be not disturbing [138]. Usage of myoelectric arm was indicated most often for using cutlery (76% of men), handicrafts and even opening/closing doors (71%) [138].

A more definite role for myoelectric arms to play particularly in UBEAs’ lives may thus depend on what real needs this new technology manages to cover [128, 136, 139]. However, the list of known issues relating to current myoelectric arms, remains long. It contains electrode related skin rashes [98, 99], sweat interference with electrode functioning [84], postural interference [140], high weight and distal center of gravity, insufficient durability [47], noisy distraction [141], absent proprioceptive feedback [142], uncoordinated grips [93], fragile prosthetic gloves [143], extreme costs [144] and unattractive appearance [45, 145].

Arm amputees with PDW to deliver are far more constrained regarding the choice of their prosthetic arm build, controls or components: they will more likely have a vital need for prosthetic arms that function, also under harsh conditions. Body-powered arms also dominate the market of prosthetic arms that are indispensable for PDW as well as sports [3, 44, 146]. For work with occupational heat exposure, biological or chemical hazards, large weights or widely ranging ambient temperatures, there is no other technology. Development of body-powered technology currently is only conducted by a small number of individuals and groups (e.g., Randall Alley [147, 148], Bob Radocy [40, 149], Bradley Veatch [74, 150, 151], Dick Plettenburg’s group [152–156], Aaron Dollar’s group [157] and John Sensinger’s group [158]).

According to our results, even some of the current commercially available body-powered components are nowhere near sufficient for PDW as outlined here. When facing such a situation as a consumer, discarding the faulty product is a far more likely reaction than trying to fix it, which can be very difficult [159]. We worked on two fronts for that: we tried to optimize both body-powered and myoelectric technology, both within the available options.

Approaching solutions for a PDW workplace from a general development and research position, one will consider that most of the hazardous, intense, sweaty or manually challenging work aspects cannot be changed [160, 161]. Also in the future, decomposing, heavy and slippery bodies will be found, also in narrow confined spaces, also of messy premises. Also for years to come, lifting, retrieving, turning, undressing and examining bodies in such situations will remain strenuous and require tough, light weight, durable prosthetic arm components with high tensile and compressive strengths for the experts that perform these duties. Occupational tasks of this specialized and individual nature will require concessions and compromises also concerning posture [160]. One may have to work out regularly to achieve and maintain fitness for such work [162]. Long and drawn out death scene examinations when wearing protective gear have aspects of “mini-expedition” style missions: one goes in, then one is in there under full strain, with executive and manual challenges and responsibilities, without any easy option to exit or troubleshoot, until only hours later, when that mission is over. And so there are other instances where equipment has to conform to harsh occupational requirements, and equipment specifications seem not too different: for large expeditions, reducing weight, improving performance and extending longevity of equipment can attain game changing significance [163]. So, research and development has proven, elsewhere, that it can understand and integrate such concepts outside the circle of amputee problems.

Narrowing technical options

An ideal mission-critical design [164] – as a necessary property for a prosthetic arm – will deliver reliable and largely error-free performance that at least approximates industrial quality standards as well as delivering performance across the specified exposure. A conformant prosthetic arm is built to minimize ill side effects, bodily injury or damage. It is built with a modular design that allows fast user repairs with widely available and affordable materials. It offers protection from overuse in the light of bodily asymmetry and heavy bi-manual work [17, 19–22].

Studies that discuss prosthetic use and overuse never normalize or stratify for actual work exposure, prosthetic arm proficiency for intense work, and actually delivered manual work. In our case, a supportive prosthetic arm allowed to perform hard work at the same functional level as peers, whereas a wrong design would cause severe shoulder pains after 1 day of regular typing work.

Mission-critical design requirements are not met by some of the current prosthetic parts that we encountered. Clinically relevant side-effects are a reason to reconsider design aspects of a prosthetic arm once lesions take too long to heal or when they risk causing permanent damage. Sudden or erratic failure while wearing a prosthetic arm can be a dramatic and stressful event; this is remedied by pushing a system to exhibit graceful degradation, which gives the user time to intervene.

Body-powered prosthetic arms are very intuitive to use. But actual motor skills including fine motor skills are acquired only by sufficiently specific and sufficiently extensive training [165, 166]. To no surprise, absent proficiency of large shoulder and trunk muscles to perform fine grasps with a body-powered control in untrained non-amputees causes their control attempts to deteriorate at higher pinch forces in a study that makes a great case for training [156]. Also, absent sufficient specific training appeared to be the reason of fatigue in most non-using amputees when trying out body-powered arms, whereas the only actual daily user of a body-powered arm in that case series did not exhibit any significant restriction (study subject number seven [167]). The first user of this study had therefore been advised by his physiotherapists early on, to not just try out body-powered technology, but to really wear it for a few years. Ultimately, large arm, shoulder and trunk musculature may be trained for heavy lifting and subsequent fine control even more efficiently than hand muscles [168]. Conversely, electric motors or batteries may simply be dead weight for a UBEA that delivers PDW over years and that has sufficiently extensive and sufficiently specific strength to provide forceful body-powered grips.

Dermatological side-effects of prosthetic arms

Friction rashes are a frequent side-effect of wearing a prosthesis [72]. Conventionally, polyurethane or silicone liners are worn directly on the skin. When sweat disrupts close liner adherence to the skin, the sweat soaked outer layers of the skin will easily abrade and develop a rash or blisters, as early as after a few hours. It may take days for a rash or blisters to heal, during which the prosthesis should not be worn. Tight cotton is known to effectively treat ’acne mechanica’ in soccer players [169]. We employed tight tubular gauze to be worn under a gel liner. It interfaces with the skin through micro-compression by way of many tiny fabric strands. These swell up to a degree as sweat fills up the cotton, while the outer skin layers remain relatively dry [170]. With a body-powered arm, the socket does not contain electrodes that sit on the skin and provide ridges where soaked soft skin layers risk to get abraded. So protection from friction rashes can allow for far greater exposure under sweating with a body-powered arm.

Skin burns are not uncommon to develop in the vicinity of myoelectrodes [98, 99]. Here and under our observation, these lesions came about under moderate amounts of sweat that had not acutely disrupted myoelectric control and took about four to six weeks to heal. As described elsewhere, we also observed blister configurations as part of these burns. The underlying technical aspects of these burns appear to also affect implanted electrodes [171]. Furthermore, heavy sweating would disrupt myoelectric control as early as 10 min into PDW [84]. Research into non-electric modes of control of devices as so far yielded both subcutaneous [78] as well as surface shape [172, 173] derived control signals as viable alternatives, at least from an academic research angle. From a PDW aspect, too much equipment is not a practical option [174]. With regard to skin preservation under PDW conditions, we found that body-powered suspensions could be coerced to conform best.

Typing contains its own perils. A long duration of repetitive small stroke actions can be hazardous, so even small differences in weight amount to large effects at the end of a day. Myoelectrodes’ ridge structures pressing into the skin caused a significant friction rash and large blisters, just after one day in the office with typing work. The socket will experience larger repetitive motions also due to a higher myoelectric terminal device weight. A tightly fitted body-powered configuration with a light aluminum split hook performs with less amplitude and less momentum. This is the case particularly with deadline work and long hours of writing [175].

Sudden failure rather than graceful degradation

Graceful degradation of performance even under adverse conditions is essential for mission-critical reliability [164]. Research and development will have to address this aspect consciously.

A predictable grip geometry is required for efficient forward-planning of dynamic push-release or reach-grasp trajectories. A multi-articulated hand that lacks finger tip coordination cannot guarantee a reliably repeatable grip configuration [176]. Lack of geometry control invariably will cause grip failure that may surprise the user, causing “sudden” or at least unexpected problems on a functional level, as seen at the CYBATHLON 2016, where a rigid gripper with just two claws outperformed some of the demonstrated multi-articulated hands due to this problem [7, 177]. Plannable grips so far benefit from rigid or constrained grip geometries. This to a degree may explain the various split hooks’ models success within amputees [41–44, 146]. The design of multi-articulated hands could possibly be improved, as researchers have identified and understood this problem [93].

Posture or stump position may negatively interfere with myoelectric control. Even professional training levels and trained controlled circumstances cannot prevent sudden occurrences of this phenomenon [7]. Typical myoelectric control uses two electrodes to control a single degree of freedom. They are placed on the flexor and extensor locations with best signal-to-noise ratio. Incidentally, these locations typically contain muscles that are also activated during elbow flexion, extension, or during stump pronation or supination, regardless whether the user intends to open or close the myoelectric device. Flexing the elbow, standing up or changing the position of the torso while keeping the hand in a constant position (which will entail elbow extension or flexion) or other changes in the limb position risk to trigger unintended signals [91]. Different stump positions are also known to interfere with multi electrode control [140]. This problem results from employing intrinsically polyvalent muscle groups for single function controls [90]. Especially when the user is distracted, and during dynamic work, this can drive up myoelectric performance error rates fast. While body-powered arms exploit posture of elbow, shoulders and back to directly transmit their shape change to achieve an analog cable tension actuation, myoelectric arms exploit polyvalent forearm muscles for digital single function control in UBEA.

It is thus fair to say that myoelectric arms are or can be also, to a degree, body-powered [178]. The art consists in making that a wilful and consciously controlled act. With that, there are two distinct differences to proper body-powered control. In body-powered arms, cable tension is built up gradually, and there is considerable proprioception of the analog control state, to a degree where body-powered VC devices can be used to precisely vary grip power from very subtle [27] all the way to over 200N. Myoelectric arms lack an analog proprioception across any control range. Secondly, the muscles used for body-powered control allow for a relatively intuitive separation of gripper actuation versus limb position change. As a key property of the control system, it results that body-powered control degrades far more gracefully when changing limb or body position. The user always feels the cable tension. While it is a training paradigm that myoelectric arms allow for precise and fluid motions [179], we found that controlled stop-and-go procedures can be more effective to prevent the limb position effect.

With both myoelectric and body-powered systems following bodily motions, both can be thus used in a freestyle way, or ’tricked’. One useful posture trick, given conventional myoelectric systems, is for the user to not at all move the stump, elbow or shoulder while performing critical grip maneuvers. An elevated shoulder and stiff elbow in an attempt to avoid posture effects will eventually cause overuse symptoms on the shoulder and neck of the amputated side, but may be relatively efficient when carrying valuable items [178]. Another useful trick, for both body-powered and myoelectric controls, is to switch off or let go of the prosthetic actuation entirely, to avoid any postural interference with the gripper.

This has been the solution for the winner during the hot wire loop test at the CYBATHLON 2016 [7]: the pilot locked down his body-powered VC system’s control cable [180] before he started with the hot wire test. He was then free to focus on the loop position fully. He only unlocked the cable afterward. The other competitors did not appear to have visibly incorporated that body-powered aspect into their myoelectric race strategy [8].

Immediacy and option to manually intervene in real time, at every step of a manipulation, is far easier with body-powered arms. Being in full control over one’s own work pace is a key factor in successfully delivering PDW [181]. Manual overrides or visual signals could be added to myoelectric devices with little extra weight. Overall, due to a very intimate link between cable tension, proprioception and terminal device actuation, we found that a body-powered control was always far more reliable than a myoelectric system.

Grip quality and grip strength

Soft covers of grip devices are a relevant issue [111]: in the presence of friction, form closure of any object places less emphasis on the grip geometry (gripper shape, number of fingers or claws). There exists a negative relationship between softness and longevity of a gripper surface [182]. The softer the surface, the firmer an object may be held even at low grip forces, but the more frequently it decays and needs to be replaced. Then, user accessibility and very affordable materials become a critical issue.

For prosthetic hands, soft covers are typically gloves. The durability of gloves is important; it was mentioned as a relevant factor already in 1980 [143]. The constraints that exist are manifold: Firstly, manufacturers of prosthetic hands make narrow specifications for allowed gloves. Secondly, gloves mechanically impede actuation [183], so weak prosthetic hands are equipped with thin and fragile gloves. Thirdly, perforating damage usually calls for an immediate stop to usage as gloves protect the hand from dirt or fluid. With myoelectric hands being rather weak and heavy already, hand geometries deviate from a normal human hand in efforts to maximize efficient grip geometry. That again makes it hard or impossible to fit these hands with normal gloves that fit normal human anatomical hands. The softer the glove, the better the grip but the faster it is damaged [182] and needs replacement. Humanly proportioned gloves are mass produced at a wide range of makes and qualities for relatively low prices. Any terminal device that works without these constraints is at a clear advantage.

There is one adaptively gripping very precise and robust prosthetic hand that excels there. The body-powered Becker hand [109, 110, 184] is a very affordable, robust body-powered hand with a reliable precision grip and an adaptive grip, that fits standard gloves including regular work gloves, including those sold at convenience or hardware stores. Its mechanical design is technically very evolved. It is not clear why the 3d-printing community, that claims to search for affordable durable solutions with respect to prosthetic hands, has not identified that hand as an answer to their quest.

Equipping a standard metal split hook with silicone tubing or cutting sheet rubber to fit a V2P or TRS prehensor device is fast, supported by warranty regulations, and easy to perform for the user.

Considerations about testing and reliability

Proper testing procedures will automatically pave the correct way for component development. Our initial negative experience with some of the currently available conventional prosthetic components may be seen as a clear reflection of current testing and product development practice. While we did provide our own relevant user driven device improvements, we would never have identified the need for them, and we would never have refined them to their current performance level, without PDW application. This forced us to address obvious conflicts between reality and expectation.

Popularized testing

From a hard working user’s perspective, a prosthetic arm always has to serve a user’s occupational needs first. That is also the typical insurance perspective. Competitive challenges that serve these specific requirements will have to be accompanied by occupational therapy and professional task coach instructions, allow for sufficient training, allow for several repetitions with different approaches, also without the prosthesis on, and allow for a range of quantitative and qualitative job- and outcome relevant metrics.

An awkwardly positioned body posture for a few tasks scattered across a daily time line is of absolutely no concern whereas repetitive or heavy tasks require more focus on correct posture – a distinction currently absent from the literature [178]. Performance evaluations with an academic entitlement may require a fuller effort to document and evaluate control, grip, posture, failure and other performance characteristics across all pilots’ attempts. One will expect registration markers and multi-angle cameras [178] on every contestant, and several runs with the same contestants but different prostheses. There will be control runs with the contestants without prostheses and non-disabled controls. Sensible rating may be conceptually difficult as time is often of no actual concern, nor will an arbitrary pre-defined task or arbitrary weight leveling for bi-manual tasks be of relevance to many PDW situations.

Popularized entertainment style prosthetic comparisons [7, 55] could be re-defined, to cover at least some of these aspects. Even despite the CYBATHLON 2016 focus on comparing arm amputees’ performances related to activities daily living (ADL) “as entertainment” [185], more intense work could be additionally popularized, for example as an added CYBATHLON 2016 “lumberjack” show [186].

Occupational task oriented testing – lowering error rates towards “Six Sigma”

The usual ADL focus of occupational therapy [187] has not been shown to effectively facilitate PDW rehabilitation [25, 188]. Prosthetic arm testing so far avoids heavy or highly repetitive bi-manual work specific tasks including performance under sweat [189]. Upper extremity prosthesis user satisfaction surveys, while sometimes employing academic test tools such as the DASH inventory, SHAP or Box and Block test, systematically omit relevant details regarding their research subjects’ profession, job or occupation [190–193]. Hazardous conditions and large slippery objects are lacking; there is not even a true-to-life secretary typing contest for arm amputees.

Relevant testing in any laboratory setting will have to approximate PDW style tasks, just as testing people or equipment for space missions entail well engineered simulations [162, 194]. From a PDW user view, the functional focus may be on safe, secure, fluid and uninterrupted completion of difficult bi-manual work tasks. Lifting tests, for example, may focus on weighty slippery objects such as lifting oily sheet metal, lifting tasks encountered in forensic medicine, or lifting a large heavy box. Holding and handling tests may focus on chunky but valuable or fragile equipment, such as large mirror reflex cameras or laptops including cabling, as well as small and delicate items [1, 195]. Realistic exposure parameters for a wider range of work can be found in the literature; a larger survey showed that an average (but not maximal) weight for carrying, lifting, lowering and pushing objects ranges around 20–25 kg [11] across industries.

The current practice has not generated particularly reliable prosthetic arms: the published error rates are high. Researchers currently view conventional laboratory derived myoelectric control success rates in excess of 90% [196] or 96% [197] as good. Industrial manufacturing that is oriented toward workmanship and production [198, 199] defines acceptable failure rates around the “six sigma” to “nine sigma” range. And simple calculations will show just how relevant these figures are even for ADL in a home setting: unloading as few as 12 cups a day from a dish washer at home will amount to ∼ 360 grips per month. A grip success rate of only ∼ 99,7% will see one crashed cup a month, or a total of 12 crashed cups a year. Not even that may be sufficient for realistic industrial or even ADL application from the viewpoint of amputees, coworkers, employers or families. For industrial exposure, as in washing dishes for a restaurant, handling 1200 pieces of dishes per day may be a low figure; there, dropping one dish per month requires a grip success rate of 99,997%. Implementing industry grade failure rates for prosthetic arm component development and testing will be a first step into the right direction [200]. Once prosthetic arm systems exceed a “six sigma” standard under all work conditions (failed grips not in excess of 3.4/1,000,000, success rate exceeding 99,9996%), amputees may feel more interested in wearing one. Sensible advertising to critical customers may benefit from added quality ratings [201], particularly if they base on intense, strict and independent testing.

Private interests of arm amputees may cause their prosthetic arms to also require significant reliability and stability. In one arm amputee related private internet support forum^{Footnote 8}, the last consecutive 29 posts mentioned strenuous physical activities and related prosthetic issues (8 proud posts), motivation and discrimination aspects (8 posts), general queries (8 posts) and welcome notices for new members (5). There was no single reference to “bionic” prostheses. This points to the fact that privately initiated strenuous sweaty and hard activities are relevant within that community. For climbing, bike riding and other sports with a clear need for bi-manual work, frequent sudden failure is not an acceptable mode of product decay [202]. It goes with the territory that a modular prosthetic arm that conforms to sensibly low industrial failure rates also will be good for sports.

Even to just succeed in an expectedly low-intensity line of work or ADL of everyday life, a prosthetic arm that is built for PDW may be the one to use. In everyday reality, gradual escalation of any laboratory conformant and controlled environment type ADL situation may easily lead to any type of intense situation with a then failing prosthesis, whether staged or real [7, 203]. Due to escalating circumstances deviating from a dry stump skin and controlled sedentary position, myoelectric prostheses thus tend to perform worse than body-powered arms even during what one may call “normal life”.

Building effective solutions

Shoulder brace

A regular figure-nine harness compressed the brachial plexus significantly and thus was found to be ill-designed for heavy long term use [101]. We thus devised a shoulder anchor. With both flexible non-distensible as well as rigid materials, the pressure is distributed across a less compressible and larger shoulder area, away from the brachial plexus. In combination with reduced compression of body tissues, this design reduced control cable excursion from previously 12–15 cm to around 5 cm. With that, the distance from the cable being fully relaxed to the terminal device being fully actuated was reduced to less than half. The choice of shape and material also stopped the brace from rotating its pivot point to the direction of the cable pull. That qualitatively increased the range of comfortably achievable postures, also including overhead work. Features characterizing our improvements of our customized shoulder anchor over a figure-nine harness were identified and confirmed robotically [204]. A similar design had been developed previously, with high acceptance by the users [205]. Significant posture improvements, particularly for demanding and repetitive work, are of known high relevance [206].

Cable sheath – sudden failure versus graceful degradation

Sudden cable failure as any other sudden device failure dramatically generates and perpetuates user dissatisfaction [116, 207]. Better planning for cable failure, therefore, became a priority. Both far more robust design and graceful degradation were made part of a mission-critical property of the prosthetic arm.

Replacing orthopedic cable clamps with correct rigging [112] entirely removed one source of frequent cable breaks. Conventional prosthetic cable mounts were found to suffer unilateral housing damage very fast and early, which then lead steel cables to break. User driven cable housing revision with a Bowden sheath fixation on a flexible belt extended the service-free life time span of the steel cable, from 4 to 10 days to over nine months, under higher actuation forces.

Also, the cable sheath revision opened up a far greater grip strength range: with reduced overall sheath resistance, more subtle control became possible. Cable shredding in prosthetic arms had previously not been solved [150, 208], despite space exploration relevance [209]. Our current cable mounts are made from relatively soft plastic, allowing for graceful degradation and a visual check of cable sheath status. Further mount designs improvements may see a replacement of conventional bicycle housing with stacked cylindrical shells [210]. Further functional improvements may entail loop routing [211].

Quick lock wrist

We experienced several commercial wrist products failing over work related tasks as outlined here. The problem of a dilating spring fixing a connector bolt was that of an overly graceful degradation: the amount of wiggle this wrist exhibited after a few weeks was irritating, but not sufficient to warrant full replacement. Wearing a device that is in its late stages of failure but not broken enough to pay for replacement, here due to excessive wiggles, may also be a rather irritating problem.

Technical wrist connector design also defines its failure characteristic. Our design extends the operative range towards pulling work-specific relevant weights without risking wrist connector wiggle, dilation or damage [11] while it is also constructed to withstand considerably higher weights. With that, it allows for heavy lifting as well as quick rotational angle or terminal device change.

Further research and development

Cosmetic prosthetic arms

Within the realm of appearance appraisal, hands have a peculiar place [212]. So socially, the common treatment of an arm amputee wearing an obvious prosthesis does not seem different from the one that does not wear one [126]. Only successfully hiding the handicap stands a chance to effectively upgrade the amputee’s outcast status, if only from “discredited” to “discreditable” [213]. Currently, arm amputees are always exposed. A prosthesis that effectively hides the handicap both statically and dynamically does not exist currently.

Technically, the ultimate challenge for a prosthetic arm design based on a clear user need remains covering up the handicap effectively. Neither industry or research have achieved technology necessary for successfully hiding an arm amputation with a prosthesis. This may be an important next step in an attempt of prosthetic manufacturers’ to bring down staggering rejection rates. From the user perspective at the moment, the fact that no prosthesis conceals the disability usually ends up obviating a need for wearing a conventional prosthetic arm particularly if its gains are, weighted for hassle, effort and discomfort, marginal at best. Unforgiving appearance testing is required to facilitate research and development to steer towards actual “cosmetic” prostheses [214].

Functional prosthetic arms

Functional prostheses have their established role in hazardous bi-manual work, PDW or blue collar occupations as well as sports. As UBEA (without prosthetic arm) even outperform non-disabled competitors in typical ADL type bi-manual tasks [121, 122], testing and research may have to learn more about bi-manual task completion for that group, and if only to get a useful baseline.

Body-powered technology is sufficiently evolved that it can be seen as the key to unlocking the market for functional prosthetic arms. It can be built to offer reliable performance with graceful grip degradation, full integration of controls with body posture and minimal medical side-effects at relatively low cost. Current problems with fragile commercial components are easy to overcome conceptually, and we showed that practical solutions work under real conditions. To achieve this on a larger scale, mission-critical performance rates will have to be targeted. Targeted reliability for professional prostheses should lie in the range of fewer than 3 errors for a million single grips under all usage conditions.

Only with hard real world testing under sweaty conditions for weeks or months (to monitor skin and overuse) per test series will prosthetic manufacturers and researchers learn which control and gripper systems work well. Mild and cautious ADL are not suitable as target for testing, development and trouble-shooting functional prosthetic arms.

For any grippers, very affordable, easy to mount grip surface covers that are soft and resilient are the current challenge.

We also found that optimal usage entailed a relatively frequent switch of terminal devices, most notably between the VC and VO control type. For PDW under such conditions, the next frontier is thus in perfecting the design of body-powered heavy duty devices that contain a switchable VO/VC control [151, 158].

Conclusions

Trying to build a prosthetic arm that works for work in forensic medicine taught us a number of things about current technology and its potential.

Many current prosthetic arm tests and rehabilitation efforts focus on ADL. That focus is not sufficient to achieve satisfying solutions, particularly for PDW.

For the purpose of developing prosthetic arms for heavy and intense applications, really demanding testing procedures are mandatory. Occupational challenges may then necessitate prosthetic adjustments that only appear once prosthetic devices are subjected to sufficiently hard tests. Control error rates of prosthetic devices need to achieve realistically low figures in the six to nine sigma range, as is standard across industry elsewhere.

Once heavy and intense work, robust control under sweat generating conditions and very low error rates are set as requirements, it will become a lot easier to identify viable technologies.

We found that initially, no currently available technology fulfilled these requirements. But body-powered controls could be brought to useful function with extensive user driven innovation and design, whereas myoelectric technology could not.

Once a prosthetic arm manages to cover demanding occupational tasks with low failure rates, ADL may not be an issue at all any longer. This was exemplified in the CYBATHLON 2016’s Arm Prosthesis Race, where the pilot with a “light” version of a body-powered prehensor won on a set of ADL-derived tasks against all myoelectric competitors.

Endnotes

Notes

1.
WS, dominant sided right below elbow amputation 2008, board certified specialist in forensic medicine
2.
detailed notes across the years on www.swisswuff.ch/tech
3.
From Wikipedia: “Industrial and manual workers often wear durable canvas or cotton clothing that may be soiled during their work. Navy and light blue colors conceal potential sweat, dirt or grease on the worker’s clothing, helping him or her to appear cleaner.”
4.
Swiss Insurance Law UVG article 11 contains that supportive measures [incl. prosthetic arms] must be simple and efficient [as to their intended purpose].
5.
From [47]: “Health professionals offered little real help. Farmers in this study reported that health professionals assigned to assist them in their recovery were stymied because they lacked basic knowledge and understanding of farming.”
6.
http://www.virtopsy.com
7.
According to KHMI (Kreisschreiben über die Abgabe von Hilfsmitteln durch die Invalidenversicherung), paragraph 1036, Swiss laws provide that “instruction to use of the prosthesis is contained in the price at purchase” [215].
8.
Internet query performed in September 2016

Abbreviations

ADL:: Activities of daily living. These usually contain activities many people share and that are considered part of life rather than part of a job, sports or dedicated activity. The list of typical ADL thus contains washing face, putting toothpaste on a toothbrush and brushing teeth or attaching the end of a zipper and zipping a jacket. ADL are typically very light activities
CBPA:: Customized body-powered arm. We used this abbreviation to refer to the customized version of body-powered technology as laid out in the method section of our paper
COG:: Center of gravity. With the center of gravity of a prosthetic arm for below elbow amputation located more distally, higher elbow torques result. Typing over a certain amount of time entails repetitive strokes. These may add to cause strain on arm, shoulder, neck and muscle pain
deg C:: Degrees Celsius
g:: Grams
ILT:: Inherent technology limitation, such as limiting aspects of myoelectrode function (i.e., loss of function due to sweat, skin burn) that cannot be simply resolved by user modifications or user driven innovation
kg:: Kilograms
MR:: Manufacturer’s restriction. A manufacturer can restrict the functionality of a device for safety reasons. An example is that a manufacturer can require the user to only operate an electronic prosthetic hand while it is covered by a water proof, manufacturer issued glove
MSL:: Manual Skill Level. We used this subjective measure to rate the manual difficulty of single death scenes in this forensic medicine workplace evaluation
OB:: Otto Bock is a German prosthetic component manufacturer
PDW:: Physically demanding work with repetitive, strenuous, sweat driving or hazardous characteristics
TBI:: Touch Bionics iLimb. We used this abbreviation to refer to the myoelectric device used for comparison against the CBPA. Its details and setup are described in the method section
VC:: Voluntary closing mode of control for body-powered arms. Thereby, the terminal device rests in an open state and is closed, for the purpose of gripping or holding, by actuating the cable. It contains a spring mechanism that opens it again once the cable is relaxed again. During the actuation, the user feels the cable being tense and can react to variations in that feeling in real time. A typical device is the TRS Prehensor
VO:: Voluntary opening mode of control for body-powered arms. Thereby, the terminal device rests in a closed state, pulled close by rubbers or springs. There are terminal devices where the user can add (or take away) rubbers or springs in order to modify the grip force. The device only opens once the cable is actuated. This type of device is particularly useful for holding or carrying items. Typical devices are Becker hands or Hosmer hooks
SHAP:: Southampton Hand Assessment Procedure. A clinically validated hand function test
TRS:: TRS is a company in Boulder, CO, USA that manufactures and sells high performance body powered prosthetic technology
UBEA:: Unilateral below elbow amputee
USD:: US-Dollars
Not contained in this list of abbreviations:: abbreviations of authors’ names

References

1
Peterson NG, Mumford MD, Borman WC, Jeanneret PR, Fleishman EA, Levin KY, Campion MA, Mayfield MS, Morgeson FP, Pearlman K, et al. Understanding work using the occupational information network (o* net): Implications for practice and research. Pers Psychol. 2001; 54(2):451–92.
- Article
- Google Scholar
2
Davidson J. A survey of the satisfaction of upper limb amputees with their prostheses, their lifestyles, and their abilities. J Hand Ther. 2002; 15(1):62–70.
- PubMed
- Article
- Google Scholar
3
Millstein S, Bain D, Hunter G. A review of employment patterns of industrial amputees – factors influencing rehabilitation. Prosthetics Orthot Int. 1985; 9(2):69–78.
- CAS
- Google Scholar
4
Eveleth R. Augmenting Humanity: When State-of-the-Art is Second Best; NOVA Next, NOVA website. 2014. http://www.pbs.org/wgbh/nova/next/tech/durable-prostheses/. Accessed 2 July 2017.
5
Berning K, Cohick S, Johnson R, Miller LAC. Comparison of body-powered voluntary opening and voluntary closing prehensor for activities of daily life. J Rehabil Res Dev. 2014; 51(2):253.
- PubMed
- Article
- Google Scholar
6
Schweitzer W, Thali M, Breitbeck R, Ampanozi G. Virtopsy. Health Manag. 2014; 14(2):37.
- Google Scholar
7
Riener R. The cybathlon promotes the development of assistive technology for people with physical disabilities. J Neuroengineering Rehabil. 2016; 13(1):49.
- Article
- Google Scholar
8
Schweizer Radio und Fernsehen SRF. SRF Menschmaschine: ganztägige Liveberichterstattung und Thementag “Wissenschaftsevent Cybathlon”, 8. Oktober 2016. 2016. https://www.srf.ch/kultur/wissen/srf-menschmaschine-die-themenwoche. Accessed 16 July 2017.
9
Sharkey BJ, Davis PO. Hard Work: Defining Physical Work Performance Requirements. Hard Work: Defining Physical Work Performance Requirements. Champaign: Human Kinetics; 2008.
- Google Scholar
10
Atkins DJ, Heard DC, Donovan WH. Epidemiologic overview of individuals with upper-limb loss and their reported research priorities. J Prosthetics Orthot. 1996; 8(1):2–11.
- Article
- Google Scholar
11
Ciriello VM, Snook SH. Survey of manual handling tasks. Int J Ind Ergon. 1999; 23(3):149–56.
- Article
- Google Scholar
12
Australia SW. Hazardous Manual Tasks: Code of Practice. Australia: Australian Government-Safe Work; 2011, pp. 1–54.
- Google Scholar
13
Burrus J, Jackson T, Xi N, Steinberg J. Identifying the most important 21st century workforce competencies: An analysis of the occupational information network (O*NET). ETS Res Rep Ser. 2013; 2013(2):i–55. https://doi.org/10.1002/j.2333-8504.2013.tb02328.x.
- Google Scholar
14
MacCrory F, Westerman G, Alhammadi Y, Brynjolfsson E. Racing with and against the machine: changes in occupational skill composition in an era of rapid technological advance. In: ICIS 2014 Proceedings: Thirty Fifth International Conference on Information Systems. Atlanta: Association for Information Systems;2014.
- Google Scholar
15
Hyatt OM, Lemke B, Kjellstrom T. Regional maps of occupational heat exposure: past, present, and potential future. Glob Health Action. 2010; 3(1):5715.
- Article
- Google Scholar
16
Hettfleisch J, Hettfleisch L. Extremitätenspätfolgen nach Gliedmaßenamputation. Orthopädische und Unfallchirurgische Praxis. 2014; 3(11):554–7.
- Google Scholar
17
Greitemann B, Güth V, Baumgartner R. Asymmetrie der Haltung und der Rumpfmuskulatur nach einseitiger Armamputation – eine klinische, elektromyographische, haltungsanalytische und rasterphotogrammetrische Untersuchung. Zeitschrift für Orthopädie und ihre Grenzgebiete. 1996; 134(06):498–510.
- CAS
- PubMed
- Article
- Google Scholar
18
Jones L, Davidson J. Save that arm: a study of problems in the remaining arm of unilateral upper limb amputees. Prosthetics Orthot Int. 1999; 23(1):55–8.
- CAS
- Google Scholar
19
Gambrell CR. Overuse syndrome and the unilateral upper limb amputee: consequences and prevention. J Prosthetics Orthot. 2008; 20(3):126–32.
- Article
- Google Scholar
20
Østlie K, Franklin RJ, Skjeldal OH, Skrondal A, Magnus P. Musculoskeletal pain and overuse syndromes in adult acquired major upper-limb amputees. Arch Phys Med Rehabil. 2011; 92(12):1967–73.
- PubMed
- Article
- Google Scholar
21
Postema SG, van der Sluis CK, Waldenlöv K, Hermansson LMN. Body structures and physical complaints in upper limb reduction deficiency: a 24-year follow-up study. PloS ONE. 2012; 7(11):49727.
- Article
- CAS
- Google Scholar
22
Burger H, Vidmar G. A survey of overuse problems in patients with acquired or congenital upper limb deficiency. Prosthetics Orthot Int. 2016; 40(4):497–502.
- Article
- Google Scholar
23
Heckathorne CW, Waldera K. The prosthetics needs of farmers and ranchers with upper-limb amputations. In: Proceedings of the 2011 Myoelectric Controls / Powered Prosthetics Symposium. Fredericton: University of New Brunswick;2011.
- Google Scholar
24
Østlie K, Franklin RJ, Skjeldal OH, Skrondal A, Magnus P. Assessing physical function in adult acquired major upper-limb amputees by combining the disabilities of the arm, shoulder and hand (dash) outcome questionnaire and clinical examination. Arch Phys Med Rehabil. 2011; 92(10):1636–45.
- PubMed
- Article
- Google Scholar
25
Jang Y, Hwang MT, Li W. A work-oriented occupational therapy programme for individuals with physical disabilities. Occup Ther Int. 1997; 4(4):304–16.
- Article
- Google Scholar
26
Holsbeeke L, Ketelaar M, Schoemaker MM, Gorter JW. Capacity, capability, and performance: different constructs or three of a kind?Arch Phys Med Rehabil. 2009; 90(5):849–55.
- PubMed
- Article
- Google Scholar
27
Lum PS, Black I, Holley RJ, Barth J, Dromerick AW. Internal models of upper limb prosthesis users when grasping and lifting a fragile object with their prosthetic limb. Exp Brain Res. 2014; 232(12):3785–95.
- PubMed
- Article
- Google Scholar
28
Antfolk C, D’Alonzo M, Rosen B, Lundborg G, Sebelius F, Cipriani C. Sensory feedback in upper limb prosthetics. Expert Rev Med Devices. 2013; 10(1):45–54.
- CAS
- PubMed
- Article
- Google Scholar
29
Sullivan D, Von Wachter T. Job displacement and mortality: An analysis using administrative data. Q J Econ. 2009; 124(3):1265–306.
- Article
- Google Scholar
30
Charles KK, Stephens Jr M. Job displacement, disability, and divorce. Technical report, National Bureau of Economic Research. 2001.
31
Bakalim G. Causes of death in a series of 4738 finnish war amputees. Artif Limbs. 1969; 13(1):27–36.
- CAS
- PubMed
- Google Scholar
32
Agnew P. Functional effectiveness of a myo-electric prosthesis compared with a functional split-hook prosthesis: a single subject experiment. Prosthetics Orthot Int. 1981; 5(2):92–6.
- CAS
- Google Scholar
33
Resnik L, Borgia M. Reliability, validity, and responsiveness of the quickdash in patients with upper limb amputation. Arch Phys Med Rehabil. 2015; 96(9):1676–83.
- PubMed
- Article
- Google Scholar
34
Scotland T, Galway H. A long-term review of children with congenital and acquired upper limb deficiency. Bone Jt J. 1983; 65(3):346–9.
- CAS
- Google Scholar
35
Berke GM, Nielsen CC. Establishing parameters affecting the use of myoelectric prostheses in children: A preliminary investigation. J Prosthetics Orthot. 1991; 3(4):162–7.
- Article
- Google Scholar
36
Biddiss E, Chau T. The roles of predisposing characteristics, established need, and enabling resources on upper extremity prosthesis use and abandonment. Disabil Rehabil Assist Technol. 2007; 2(2):71–84.
- PubMed
- Article
- Google Scholar
37
Oliver RL. Satisfaction: A Behavioral Perspective on the Consumer [second Edition]. New York: Routledge; 2015.
- Google Scholar
38
Fornell C, Westbrook RA. The vicious circle of consumer complaints. J Mark. 1984:68–78.
39
Schweitzer W. swisswuff.ch/tech - “Why do people stop using their prosthetic arms? [vicious cycle]”. 2010. http://www.swisswuff.ch/tech/?p=344. Accessed 16 July 2017.
40
Radocy R. Prosthetic hand. Google Patents. US, Patent D294,174. 1988.
41
Post E. Real Programmers Don’t Use Pascal. Datamation. 1983; 29(7):263–5.
- Google Scholar
42
Millstein S, Heger H, Hunter G. Prosthetic use in adult upper limb amputees: a comparison of the body powered and electrically powered prostheses. Prosthetics Orthot Int. 1986; 10(1):27–34.
- CAS
- Google Scholar
43
Gaine W, Smart C, Bransby-Zachary M. Upper limb traumatic amputees: Review of prosthetic use. J Hand Surg. 1997; 22(1):73–6.
- CAS
- Article
- Google Scholar
44
Stürup J, Thyregod H, Jensen J, Retpen J, Boberg G, Rasmussen E, Jensen S. Traumatic amputation of the upper limb: the use of body-powered prostheses and employment consequences. Prosthetics Orthot Int. 1988; 12(1):50–2.
- Google Scholar
45
Kejlaa G. Consumer concerns and the functional value of prostheses to upper limb amputees. Prosthetics Orthot Int. 1993; 17(3):157–63.
- CAS
- Google Scholar
46
Serlin D. The Other Arms Race In: Davis LJ, editor. The Disability Studies Reader. New York: Routledge;2006. p. 49–65.
- Google Scholar
47
Reed D. Understanding and meeting the needs of farmers with amputations. Orthop Nurs. 2004; 23(6):397–405.
- PubMed
- Google Scholar
48
Brake D, Bates G. Fluid losses and hydration status of industrial workers under thermal stress working extended shifts. Occup Environ Med. 2003; 60(2):90–6.
- CAS
- PubMed
- PubMed Central
- Article
- Google Scholar
49
Faeh D, Marques-Vidal P, Chiolero A, Bopp M. Obesity in switzerland: do estimates depend on how body mass index has been assessed?Swiss Med Wkly. 2008; 138(13-14):204–10.
- PubMed
- Google Scholar
50
Lee DH. Seventy-five years of searching for a heat index. Environ Res. 1980; 22(2):331–56.
- CAS
- PubMed
- Article
- Google Scholar
51
Borg DN, Costello JT, Bach AJ, Stewart IB. Perceived exertion is as effective as the perceptual strain index in predicting physiological strain when wearing personal protective clothing. Physiol Behav. 2017; 169:216–23.
- CAS
- PubMed
- Article
- Google Scholar
52
Hart SG, Staveland LE. Development of nasa-tlx (task load index): Results of empirical and theoretical research. Adv Psychol. 1988; 52:139–83.
- Article
- Google Scholar
53
Laing RM, Sleivert GG. Clothing, textiles, and human performance. Text Prog. 2002; 32(2):1–122.
- Article
- Google Scholar
54
Carroll D. A quantitative test of upper extremity function. J Chronic Dis. 1965; 18(5):479–91.
- CAS
- PubMed
- Article
- Google Scholar
55
Light CM, Chappell PH, Kyberd PJ. Establishing a standardized clinical assessment tool of pathologic and prosthetic hand function: normative data, reliability, and validity. Arch Phys Med Rehabil. 2002; 83(6):776–83.
- PubMed
- Article
- Google Scholar
56
Hussaini A, Kyberd P. Refined clothespin relocation test and assessment of motion. Prosthetics Orthot Int. 2016:1–9. https://doi.org/10.1177/0309364616660250.
57
ISO/TC 168. ISO 10328:2000(en) – Prosthetics – Structural testing of lower-limb prostheses – Requirements and test methods. Geneva: Standard, International Organization for Standardization; 2016.
- Google Scholar
58
Detry R, Kraft D, Kroemer O, Bodenhagen L, Peters J, Krüger N, Piater J. Learning grasp affordance densities. J Behav Robot. 2011; 2(1):1.
- Article
- Google Scholar
59
Hengstebeck A, Weisner K, Klöckner M, Deuse J, Kuhlenkötter B, Roßmann J. Formal modelling of manual work processes for the application of industrial service robotics. Procedia CIRP. 2016; 41:364–9.
- Article
- Google Scholar
60
Beaudry MC, Long J, Miller HM, Neiman FD, Stone GW. A vessel typology for early chesapeake ceramics: the potomac typological system. Hist Archaeol. 1983; 17(1):18–43.
- Article
- Google Scholar
61
Garneau CJ, Parkinson MB. Optimization of product dimensions for discrete sizing applied to a tool handle. Int J Ind Ergon. 2012; 42(1):56–64.
- Article
- Google Scholar
62
Lawrence S. Artifacts of the modern world In: Balme J, Paterson A, editors. Archaeology in Practice: A student guide to archaeological analyses. Oxfort: Blackwell Publishing;2006. p. 362–88.
- Google Scholar
63
Molotch H. Inside Stuff: How Professionals Do It In: Molotch H, editor. Where Stuff Comes From: How Toasters, Toilets, Cars, Computers and Many Other Things Come To Be As They Are. London and New York: Routledge;2004. p. 6–15.
- Google Scholar
64
SHAP Business Enterprise. SHAP Southampton Hand Assessment Procedure – Assessor’s SHAP Protocol. 2009. http://www.shap.ecs.soton.ac.uk/files/protocol.pdf. Accessed 16 July 2017.
65
Crawford JO, Wanibe E, Nayak L. The interaction between lid diameter, height and shape on wrist torque exertion in younger and older adults. Ergonomics. 2002; 45(13):922–33.
- PubMed
- Article
- Google Scholar
66
Rowson J, Yoxall A. Hold, grasp, clutch or grab: Consumer grip choices during food container opening. Appl Ergon. 2011; 42(5):627–33.
- CAS
- PubMed
- Article
- Google Scholar
67
Calli B, Walsman A, Singh A, Srinivasa S, Abbeel P, Dollar AM. Benchmarking in manipulation research: Using the yale-cmu-berkeley object and model set. IEEE Robot Autom Mag. 2015; 22(3):36–52.
- Article
- Google Scholar
68
Ciocarlie M, Goldfeder C, Allen P. Dimensionality reduction for hand-independent dexterous robotic grasping. In: Proceedings of IEEE/RSJ International Conference on Intelligent Robots and Systems (IROS). San Diego: IEEE/RSJ/SICE;2007. p. 3270–5.
- Google Scholar
69
Allen PK, Ciocarlie MT, Goldfeder C, Dang H. Low-dimensional data-driven grasping. In: Proceedings of 2009 Robotics: Science and Systems Conference. Seattle: University of Washington;2009.
- Google Scholar
70
Otto Bock. Prosthetics Global Catalog – Upper Limb. Otto Bock Healthcare GmbH, Max-Näder-Str. 15, Duderstadt, Germany. 2013. https://professionals.ottobockus.com/media/pdf/2013_Prosthetics_Upper_Limb_Global_Catalog.pdf. Accessed 16 July 2017.
71
Otto Bock. 10V9 / 10V10 /10V25 – Rastenloses Handgelenk. Printed in Germany, 647G452, Auflage 02.09/1 - MD. 2009.
72
Lyon CC, Kulkarni J, Zimersonc E, Van Ross E, Beck MH. Skin disorders in amputees. J Am Acad Dermatol. 2000; 42(3):501–7.
- CAS
- PubMed
- Article
- Google Scholar
73
Siddiqi A, Weck Od, de Weck O. Spare parts requirements for space missions with reconfigurability and commonality. J Spacecr Rocket. 2007; 44(1):147–55.
- Article
- Google Scholar
74
Veatch BD, Scott JD. Prehensor device and improvements of same. Google Patents. US Patent 7,341,295. 2008.
75
Mhurchadha N, Eilís S. Developing consensus on what constitutes’ success’ following upper limb loss rehabilitation. 2010. PhD thesis, Dublin City University.
76
Seps M, Dermitzakis K, Hernandez-Arieta A. Study on lower back electrotactile stimulation characteristics for prosthetic sensory feedback. In: Proceedings of the 2011 IEEE/RSJ International Conference on Intelligent Robots and Systems (IROS). Piscataway: IEEE;2011. p. 3454–459. Sep 25-30 2011, San Francisco, CA, USA.
- Google Scholar
77
Dermitzakis K, Arieta AH, Pfeifer R. Gesture recognition in upper-limb prosthetics: A viability study using dynamic time warping and gyroscopes. In: Proceedings of the 33 ^rd Annual International Conference of the IEEE Engineering in Medicine and Biology Society, EMBC. Piscataway: IEEE;2011. p. 4530–533. Aug 30 – Sep 03 2011, Boston, MA, USA.
- Google Scholar
78
Castellini C, Passig G, Zarka E. Using ultrasound images of the forearm to predict finger positions. IEEE Trans Neural Syst Rehabil Eng. 2012; 20(6):788–97.
- PubMed
- Article
- Google Scholar
79
Jensen SE, Butt Z, Bill A, Baker T, Abecassis MM, Heinemann AW, Cella D, Dumanian GA. Quality of life considerations in upper limb transplantation: review and future directions. J Hand Surg. 2012; 37(10):2126–35.
- Article
- Google Scholar
80
Marini F, Tagliabue CF, Sposito AV, Hernandez-Arieta A, Brugger P, Estévez N, Maravita A. Crossmodal representation of a functional robotic hand arises after extensive training in healthy participants. Neuropsychologia. 2014; 53(0):178–86.
- PubMed
- Article
- Google Scholar
81
Atzori M, Gijsberts A, Caputo B, Müller H. Natural control capabilities of robotic hands by hand amputated subjects. In: Proceedings of the Engineering in Medicine and Biology Society (EMBC), 2014 36th Annual International Conference of the IEEE. Piscataway: IEEE;2014. p. 4362–5.
- Google Scholar
82
Waldera KE, Heckathorne CW, Parker M, Fatone S. Assessing the prosthetic needs of farmers and ranchers with amputations. Disabil Rehabil Assist Technol. 2013; 8(3):204–12.
- PubMed
- Article
- Google Scholar
83
Kardous CA, Shaw PB. So How Accurate Are These Smartphone Sound Measurement Apps?https://blogs.cdc.gov/niosh-science-blog/2014/04/09/sound-apps/. Accessed 16 July 2017.
84
Ray G, Saxena S, Mukhopadhyay P. Myoelectric control of an artificial hand for sequential movement in a tropical climate. Med Biol Eng Comput. 1979; 17(6):724–8.
- CAS
- PubMed
- Article
- Google Scholar
85
Schultz AE, Kuiken TA. Neural interfaces for control of upper limb prostheses: the state of the art and future possibilities. PM&R. 2011; 3(1):55–67.
- Article
- Google Scholar
86
Schweitzer W. swisswuff.ch/tech - “Car wash – what happens when one uses an iLimb Ultra Revolution *just* to assist holding the water tube [glove damage within minutes]”. 2014. http://www.swisswuff.ch/tech/?p=2965. Accessed 16 July 2017.
87
Biddiss E, Chau T. Upper-limb prosthetics: critical factors in device abandonment. Am J Phys Med Rehabil. 2007; 86(12):977–87.
- PubMed
- Article
- Google Scholar
88
Schweitzer W. swisswuff.ch/tech - “iLimb glove self destructs (in-storage product suicide) [WTF]”. 2016. http://www.swisswuff.ch/tech/?p=5651. Accessed 16 July 2017.
89
Touch Bionics. iLimb (TM) Ultra Revolution User Manual (issue 3). Livingston: Touch Bionics; 2014.
- Google Scholar
90
Howard J, Hoit J, Enoka R, Hasan Z. Relative activation of two human elbow flexors under isometric conditions: a cautionary note concerning flexor equivalence. Exp Brain Res. 1986; 62(1):199–202.
- CAS
- PubMed
- Article
- Google Scholar
91
Jiang N, Muceli S, Graimann B, Farina D. Effect of arm position on the prediction of kinematics from emg in amputees. Med Biol Eng Comput. 2013; 51(1-2):143–51.
- PubMed
- Article
- Google Scholar
92
Head J. The effect of socket movement and electrode contact on myoelectric prosthesis control during daily living activities. 2014. PhD thesis, University of Salford, Manchester, UK.
93
Ma RR, Rojas N, Dollar AM. Spherical hands: Towards underactuated, in-hand manipulation invariant to object size and grasp location. J Mech Robot. 2016; 8(6):061021. https://mechanismsrobotics.asmedigitalcollection.asme.org/article.aspx?articleID=2556269.
- Article
- Google Scholar
94
Schweitzer W. swisswuff.ch/tech - “Stump after wearing myoelectric “bionic” prosthesis for 10 hours [graphic /voightkampff]”. 2014. http://www.swisswuff.ch/tech/?p=2979. Accessed 16 July 2017.
95
Jaguemont J, Boulon L, Dubé Y. A comprehensive review of lithium-ion batteries used in hybrid and electric vehicles at cold temperatures. Appl Energy. 2016; 164:99–114.
- CAS
- Article
- Google Scholar
96
Guski R, Felscher-Suhr U, Schuemer R. The concept of noise annoyance: how international experts see it. J Sound Vib. 1999; 223(4):513–27.
- Article
- Google Scholar
97
Broadbent DE. Perception and Communication. Netherlands: Elsevier Science; 2013.
- Google Scholar
98
Patriciu A, Yoshida K, Struijk JJ, DeMonte TP, Joy ML, Stodkilde-Jorgensen H. Current density imaging and electrically induced skin burns under surface electrodes. IEEE Trans Biomed Eng. 2005; 52(12):2024–31.
- PubMed
- Article
- Google Scholar
99
Besio W, Sharma V, Spaulding J. The effects of concentric ring electrode electrical stimulation on rat skin. Ann Biomed Eng. 2010; 38(3):1111–8.
- CAS
- PubMed
- PubMed Central
- Article
- Google Scholar
100
Stecker MM, Patterson T, Netherton BL. Mechanisms of electrode induced injury. part 1: theory. Am J Electroneurodiagnostic Technol. 2006; 46(4):315–42.
- PubMed
- Google Scholar
101
Fryer CM. 6B - Upper-Limb Prosthetics: Harnessing and Controls for Body-Powered Devices In: Bowker JH, editor. Atlas of limb prosthetics: surgical, prosthetic, and rehabilitation principles. USA: Mosby Inc.;1992.
- Google Scholar
102
Morgan G, Wilbourn AJ. Cervical radiculopathy and coexisting distal entrapment neuropathies double-crush syndromes?Neurology. 1998; 50(1):78–83.
- CAS
- PubMed
- Article
- Google Scholar
103
Mäkelä JP, Ramstad R, Mattila V, Pihlajamäki H. Brachial plexus lesions after backpack carriage in young adults. Clin Orthop. 2006; 452:205–9.
- PubMed
- Article
- Google Scholar
104
Agrawal V, Peine WJ, Yao B. Modeling of transmission characteristics across a cable-conduit system. IEEE Trans Robot. 2010; 26(5):914–24.
- Article
- Google Scholar
105
Schweitzer W. Aufhängung für einen Bowdenzug mit einer Führung und mit einem nicht dehnbaren biegsamen Element. Swiss Patent. CH703982. 2016.
106
Meili R. Prothesenkupplung. Swiss Patent. CH710533. 2016.
107
Schweitzer W. swisswuff.ch/tech - “Shoulder harness III - prolonged usage problem description”. 2011. http://www.swisswuff.ch/tech/?p=386. Accessed 16 July 2017.
108
Schweitzer W. swisswuff.ch/tech - “Hosmer Model 6 Work Hook [tweak / improvement / backlock feature]”. 2016. http://www.swisswuff.ch/tech/?p=6102. Accessed 16 July 2017.
109
Becker DB. Artificial hand. Google Patents. US Patent 2,301,009. 1942.
110
Becker DB. Artificial hand having a body constructed from separate molded plastic parts for easier replacement of damaged parts. Google Patents. US Patent 3,413,658. 1968.
111
Markenscoff X, Ni L, Papadimitriou CH. The geometry of grasping. Int J Robot Res. 1990; 9(1):61–74.
- Article
- Google Scholar
112
Feyrer K. Wire Ropes. Germany: Springer; 2007.
- Google Scholar
113
Dakpa R, Heger H. Prosthetic management and training of adult upper limb amputees. Curr Orthop. 1997; 11(3):193–202.
- Article
- Google Scholar
114
Rantanen T, Guralnik JM, Foley D, Masaki K, Leveille S, Curb JD, White L. Midlife hand grip strength as a predictor of old age disability. Jama. 1999; 281(6):558–60.
- CAS
- PubMed
- Article
- Google Scholar
115
Biddiss EA, Chau TT. Upper limb prosthesis use and abandonment: a survey of the last 25 years. Prosthetics Orthot Int. 2007; 31(3):236–57.
- Article
- Google Scholar
116
Zeelenberg M, Pieters R. Beyond valence in customer dissatisfaction: A review and new findings on behavioral responses to regret and disappointment in failed services. J Bus Res. 2004; 57(4):445–55.
- Article
- Google Scholar
117
Wevers H, Durance J. Dynamic testing of below-knee prosthesis: assembly and components. Prosthetics Orthot Int. 1987; 11(3):117–23.
- CAS
- Google Scholar
118
Kuniholm J. Open arms. IEEE Spectr. 2009; 46(3):36–41.
- Article
- Google Scholar
119
White S. Severed hands as symbols of humanity in legend and popular narratives. Master’s thesis, Utah State University, Logan, UT, USA. 2014.
120
Baumgartner R, Botta P. Amputation und Prothesenversorgung der Oberen Extremität: Indikationsstellung, Operative Technik, Prothesen- und Hilfsmittelversorgung, Funktionstraining, Rehabilitation, Begutachtung. Germany: Enke; 1997.
- Google Scholar
121
Bagley AM, Molitor F, Wagner LV, Tomhave W, James MA. The unilateral below elbow test: A function test for children with unilateral congenital below elbow deficiency. Dev Med Child Neurol. 2006; 48(7):569–75.
- PubMed
- Article
- Google Scholar
122
James MA, Bagley AM, Brasington K, Lutz C, McConnell S, Molitor F. Impact of prostheses on function and quality of life for children with unilateral congenital below-the-elbow deficiency. J Bone Joint Surg. 2006; 88(11):2356–65.
- PubMed
- Google Scholar
123
de Jong IG, Reinders-Messelink HA, Janssen WG, Poelma MJ, van Wijk I, van der Sluis CK. Mixed feelings of children and adolescents with unilateral congenital below elbow deficiency: An online focus group study. PloS ONE. 2012; 7(6):37099.
- Article
- CAS
- Google Scholar
124
Frank G. Beyond stigma: Visibility and self-empowerment of persons with congenital limb deficiencies. J Soc Issues. 1988; 44(1):95–115.
- Article
- Google Scholar
125
Haslam N, Kashima Y, Loughnan S, Shi J, Suitner C. Subhuman, inhuman, and superhuman: Contrasting humans with nonhumans in three cultures. Soc Cogn. 2008; 26(2):248–58.
- Article
- Google Scholar
126
Kastl JM, Felkendorff K. Behinderung, Soziologie und Gesellschaftliche Erfahrung: Im Gespräch Mit Günther Cloerkes. Germany: Springer; 2014.
- Google Scholar
127
Lyman SM, Scott MB. Territoriality: A neglected sociological dimension. Soc Probl. 1967; 15(2):236–49.
- Article
- Google Scholar
128
Saradjian A, Thompson AR, Datta D. The experience of men using an upper limb prosthesis following amputation: positive coping and minimizing feeling different. Disabil Rehabil. 2008; 30(11):871–83.
- PubMed
- Article
- Google Scholar
129
Gollwitzer PM, Wicklund RA. Self-symbolizing and the neglect of others’ perspectives. J Pers Soc Psychol. 1985; 48(3):702.
- Article
- Google Scholar
130
Braun OL, Wicklund RA. Psychological antecedents of conspicuous consumption. J Econ Psychol. 1989; 10(2):161–87.
- Article
- Google Scholar
131
Dittmar H. Consumer Culture, Identity and Well-Being: The Search for the ’Good Life’ and the ’Body Perfect’. European Monographs in Social Psychology. UK: Taylor & Francis; 2007.
- Google Scholar
132
Li H, Bhowmick SS, Sun A. Affrank: Affinity-driven ranking of products in online social rating networks. J Assoc Inf Sci Technol. 2011; 62(7):1345–59.
- Article
- Google Scholar
133
Meyer B. Stereotype Content Model In: Samochowiec J, Schmidt A, editors. Robotik und Behinderungen - Wie Maschinen Morgen Menschen Helfen. Rüschlikon, ZH, Switzerland: GDI Gottlieb Duttweiler Institute;2017. p. 74–7.
- Google Scholar
134
Bogue R. Exoskeletons and robotic prosthetics: a review of recent developments. Ind Robot Int J. 2009; 36(5):421–7.
- Article
- Google Scholar
135
Kobrinski A, Bolkovitin S, Voskoboinikova L, Ioffe D, Polyan E, Popov B, Slavutski Y, Sysin A, Yakobson Y. Problems of Bioelectric Control. In: Automatic and Remote Control. Proceedings of the First International Congress of the International Federation of Automatic Control, I.F.A.C. vol. 2. London: Butterworths;1961. p. 619.
- Google Scholar
136
Belter JT, Segil JL, SM B. Mechanical design and performance specifications of anthropomorphic prosthetic hands: a review. J Rehabil Res Dev. 2013; 50(5):599.
- PubMed
- Article
- Google Scholar
137
Duong T, Wagner B, Abraham T, Davidson M, Bains G, Daher N, Friedrich A. Comparative study of functional grasp and efficiency between a 3d-printed and commercial myoelectric transradial prosthesis using able-bodied subjects: A pilot study. J Prosthetics Orthot. 2017; 29(3):112–8.
- Article
- Google Scholar
138
Pylatiuk C, Schulz S, Döderlein L. Results of an internet survey of myoelectric prosthetic hand users. Prosthetics Orthot Int. 2007; 31(4):362–70.
- Article
- Google Scholar
139
Higashi S. Hold it! women in television adventure series. J Pop Film Telev. 1980; 8(3):26–37.
- Article
- Google Scholar
140
Scheme E, Fougner A, Stavdahl Ø, Chan A, Englehart K. Examining the adverse effects of limb position on pattern recognition based myoelectric control. In: 2010 Annual International Conference of the IEEE Engineering in Medicine and Biology. Piscataway: IEEE;2010. p. 6337–40.
- Google Scholar
141
Newell Jr PH, Sherwood AM, McDaniel GL. Toward acoustic standards for powered assist devices. Bull Prosthetics Res. 1972; 17:21.
- Google Scholar
142
Brown JD, et al. An empirical evaluation of force feedback in body-powered prostheses. IEEE Trans Neural Syst Rehabil Eng. 2016; 25.3(2017):215–26.
- Google Scholar
143
Northmore-Ball M, Heger H, Hunter GA. The below-elbow myo-electric prosthesis. a comparison of the otto bock myo-electric prosthesis with the hook and functional hand. Bone Jt J. 1980; 62(3):363–7.
- CAS
- Google Scholar
144
Biddiss E, Beaton D, Chau T. Consumer design priorities for upper limb prosthetics. Disabil Rehabil Assist Technol. 2007; 2(6):346–57.
- PubMed
- Article
- Google Scholar
145
Carey SL, Lura DJ, Highsmith MJ, et al.Differences in myoelectric and body-powered upper-limb prostheses: Systematic literature review. J Rehabil Res Dev. 2015; 52(3):247.
- PubMed
- Article
- Google Scholar
146
Wright TW, Hagen AD, Wood MB. Prosthetic usage in major upper extremity amputations. J Hand Surgy. 1995; 20(4):619–22.
- CAS
- Article
- Google Scholar
147
Alley RD. Advancement of upper extremity prosthetic interface and frame design. In: Myoelectric Symposium. Fredericton: University of New Brunswick;2002.
- Google Scholar
148
Alley RD. Adaptable socket system, method, and kit. Google Patents. US Patent 9,283,093. 2016.
149
Radocy B. Upper-extremity prosthetics: considerations and designs for sports and recreation. Clin Prosthet Orthot. 1987; 11(3):131–53.
- Google Scholar
150
Carlson LE, Veatch BD, Frey DD. Efficiency of prosthetic cable and housing. J Prosthetics Orthot. 1995; 7(3):96–9.
- Article
- Google Scholar
151
Veatch BD. Gripping device with switchable prehension modes. Google Patents. US Patent 9,474,631. 2016.
152
Smit G, Bongers RM, Van der Sluis CK, Plettenburg DH. Efficiency of voluntary opening hand and hook prosthetic devices: 24 years of development?J Rehabil Res Dev. 2012; 49(4):523.
- PubMed
- Article
- Google Scholar
153
Smit G, Plettenburg DH, van der Helm FCT. The lightweight Delft Cylinder Hand: first multi-articulating hand that meets the basic user requirements IEEE Transactions on Neural Systems and Rehabilitation Engineering 23.3. Piscataway: IEEE; 2015, pp. 431–40.
- Google Scholar
154
Haverkate L, Smit G, Plettenburg DH. Assessment of body-powered upper limb prostheses by able-bodied subjects, using the box and blocks test and the nine-hole peg test. Prosthetics Orthot Int. 2016; 40(1):109–16.
- Article
- Google Scholar
155
Huinink LH, Bouwsema H, Plettenburg DH, van der Sluis CK, Bongers RM. Learning to use a body-powered prosthesis: changes in functionality and kinematics. J NeuroEngineering Rehab. 2016; 13(1):90.
- Article
- Google Scholar
156
Hichert M, Abbink DA, Kyberd PJ, Plettenburg DH. High cable forces deteriorate pinch force control in voluntary-closing body-powered prostheses. PLoS ONE. 2017; 12(1):0169996.
- Article
- CAS
- Google Scholar
157
Belter JT, Reynolds BC, Dollar AM. Grasp and force based taxonomy of split-hook prosthetic terminal devices. In: Engineering in Medicine and Biology Society (EMBC), 2014 36th Annual International Conference of the IEEE. Piscataway: IEEE;2014. p. 6613–8.
- Google Scholar
158
Sensinger JW, Lipsey J, Thomas A, Turner K. Design and evaluation of voluntary opening and voluntary closing prosthetic terminal device. J Rehabil Res Dev. 2015; 52(1):63–76.
- PubMed
- Article
- Google Scholar
159
Roberts T, Hope A, Skelton A. Why on earth did I buy that? A study of regretted appliance purchases. Phil Trans R Soc A. 2017; 375(2095):20160373.
- PubMed
- PubMed Central
- Article
- Google Scholar
160
Kuorinka I, Lortie M, Gautreau M. Manual handling in warehouses: the illusion of correct working postures. Ergonomics. 1994; 37(4):655–61.
- CAS
- PubMed
- Article
- Google Scholar
161
Authier M, Lortie M, Gagnon M. Manual handling techniques: Comparing novices and experts. Int J Ind Ergon. 1996; 17(5):419–29.
- Article
- Google Scholar
162
Petersen N, Thieschäfer L, Ploutz-Snyder L, Damann V, Mester J. Reliability of a new test battery for fitness assessment of the european astronaut corps. Extreme Physiol Med. 2015; 4(1):12.
- Article
- Google Scholar
163
Mueller RP, Hoffman SJ, Thur P. A study of parallels between antarctica south pole traverse equipment and lunar/mars surface systems. In: Earth and Space 2010: Engineering, Science, Construction, and Operations in Challenging Environments. USA: NASA;2010. p. 908–40.
- Google Scholar
164
Goerger SR, Madni AM, Eslinger OJ. Engineered resilient systems: A DoD perspective. Procedia Comput Sci. 2014; 28:865–72.
- Article
- Google Scholar
165
Seashore RH. An experimental and theoretical analysis of fine motor skills. Am J Psychol. 1940; 53(1):86–98.
- Article
- Google Scholar
166
Bernardi M, Solomonow M, Nguyen G, Smith A, Baratta R. Motor unit recruitment strategy changes with skill acquisition. Eur J Appl Physiol Occup Physiol. 1996; 74(1):52–9.
- CAS
- PubMed
- Article
- Google Scholar
167
Hichert M, Vardy AN, Plettenburg D. Fatigue-free operation of most body-powered prostheses not feasible for majority of users with trans-radial deficiency. Prosthetics Orthot Int. 2017:0309364617708651.
168
Leyk D, Rohde U, Erley O, Gorges W, Wunderlich M, Rüther T, Essfeld D. Recovery of hand grip strength and hand steadiness after exhausting manual stretcher carriage. Eur J Appl Physiol. 2006; 96(5):593–9.
- CAS
- PubMed
- Article
- Google Scholar
169
Basler RS, Hunzeker CM, Garcia MA, Dexter W. Athletic skin injuries: combating pressure and friction. Phys Sportsmedicine. 2004; 32(5):33–40.
- PubMed
- Article
- Google Scholar
170
Gerhardt LC, Strässle V, Lenz A, Spencer N, Derler S. Influence of epidermal hydration on the friction of human skin against textiles. J R Soc Interface. 2008; 5(28):1317–28.
- PubMed
- PubMed Central
- Article
- Google Scholar
171
Patterson T, Stecker MM, Netherton BL. Mechanisms of electrode induced injury. part 2: Clinical experience. Am J Electroneurodiagnostic Technol. 2007; 47(2):93–113.
- PubMed
- Google Scholar
172
Phillips SL, Craelius W. Residual kinetic imaging: a versatile interface for prosthetic control. Robotica. 2005; 23(3):277–82.
- Article
- Google Scholar
173
Radmand A, Scheme E, Englehart K. High-density force myography: A possible alternative for upper-limb prosthetic control. J Rehabil Res Dev. 2016; 53(4):443–56.
- PubMed
- Article
- Google Scholar
174
Castellini C, Artemiadis P, Wininger M, et al.Proceedings of the first workshop on peripheral machine interfaces: Going beyond traditional surface electromyography. Front Neurorobotics. 2014; 8:22. https://doi.org/10.3389/fnbot.2014.00022.
- Article
- Google Scholar
175
Bernard B, Sauter S, Fine L, Petersen M, Hales T. Job task and psychosocial risk factors for work-related musculoskeletal disorders among newspaper employees. Scand J Work Environ Health. 1994:417–26.
176
Kyberd PJ. Assessment of functionality of multifunction prosthetic hands. J Prosthetics Orthot. 2017; 29(3):103–11.
- Article
- Google Scholar
177
Schweitzer W. swisswuff.ch/tech - “Functional failures of prosthetic hands at the Cybathlon 2016 [details]”. 2016. http://www.swisswuff.ch/tech/?p=7655. Accessed 16 July 2017.
178
Carey SL, Highsmith MJ, Maitland ME, Dubey RV. Compensatory movements of transradial prosthesis users during common tasks. Clin Biomech. 2008; 23(9):1128–35.
- Article
- Google Scholar
179
Bouwsema H, van der Sluis CK, Bongers RM. Guideline for Training with a Myoelectric Prosthesis. Netherlands: Center for Human Movement Sciences/Department of Rehabilitation Medicine. University Medical Center Groningen, University of Groningen; 2013.
- Google Scholar
180
Veatch B. Cable lock device for prosthetic and orthotic devices. Google Patents. US Patent App. 11/455,064. 2007.
181
Harrell WA. Perceived risk of occupational injury: Control over pace of work and blue-collar versus white-collar work. Percept Mot Skills. 1990; 70(3_suppl):1351–9.
- CAS
- PubMed
- Article
- Google Scholar
182
Voigt D, Karguth A, Gorb S. Shoe soles for the gripping robot: Searching for polymer-based materials maximising friction. Robot Auton Syst. 2012; 60(8):1046–55.
- Article
- Google Scholar
183
Smit G, Bongers RM, Van der Sluis CK, Plettenburg DH. Efficiency of voluntary opening hand and hook prosthetic devices, 24 years of development?JRRD J Rehabil Res Dev. 2012;49(4).
184
Becker DB. Artificial hand. Google Patents: US Patent 2,301,009. 1942.
185
Sigrist R. Motivation and goals of the cybathlon. In: Entrepreneurs Determine The Future of Sports. Eindhoven: Sport Experience;2017.
- Google Scholar
186
Freedman L. Timber!: The Story of the Lumberjack World Championships. USA: University of Wisconsin Press; 2011.
- Google Scholar
187
Atkins DJ. Adult Upper-Limb Prosthetic Training In: Atkins DJ, Meier III RH, editors. Comprehensive management of the upper-limb amputee. New York: Springer;1989. p. 39–59.
- Google Scholar
188
Vujaklija I, Roche AD, Hasenoehrl T, et al. Translating research on myoelectric control into clinics – are the performance assessment methods adequate?Front Neurorobotics. 2017; 11:7. https://doi.org/10.3389/fnbot.2017.00007.
- Article
- Google Scholar
189
Curtis V, Biran A. Dirt, disgust, and disease: Is hygiene in our genes?Perspect Biol Med. 2001; 44(1):17–31.
- CAS
- PubMed
- Article
- Google Scholar
190
Nielsen CC. A survey of amputees: Functional level and life satisfaction, information needs, and the prosthetist’s role. J Prosthetics Orthot. 1991; 3(3):125–9.
- Article
- Google Scholar
191
Kyberd PJ, Beard DJ, Davey JJ, Morrison JD. A Survey of Upper-Limb Prosthesis Users in Oxfordshire. J Prosthetics Orthot. 1998; 10(4):84–91.
- Article
- Google Scholar
192
Kyberd PJ, Hill W. Survey of upper limb prosthesis users in Sweden, the United Kingdom and Canada. Prosthetics Orthot Int. 2011; 35(2):234–41.
- Article
- Google Scholar
193
Deijs M, Bongers R, Ringeling-van Leusen N, van der Sluis C. Flexible and static wrist units in upper limb prosthesis users: functionality scores, user satisfaction and compensatory movements. J Neuroengineering Rehabil. 2016; 13(1):26.
- CAS
- Article
- Google Scholar
194
Hockey J. ’switch on’: Sensory work in the infantry. Work Employ Soc. 2009; 23(3):477–93.
- Article
- Google Scholar
195
Magnusson M, Pope M. A review of the biomechanics and epidemiology of working postures (it isn’t always vibration which is to blame!). J Sound Vib. 1998; 215(4):965–76.
- Article
- Google Scholar
196
Dupont AC, Morin EL. A myoelectric control evaluation and trainer system. IEEE Trans Rehabil Eng. 1994; 2(2):100–7.
- Article
- Google Scholar
197
Wurth SM, Hargrove LJ. A real-time comparison between direct control, sequential pattern recognition control and simultaneous pattern recognition control using a fitts’ law style assessment procedure. J Neuroengineering Rehabil. 2014; 11(1):91.
- Article
- Google Scholar
198
Veblen T. The Instinct of Workmanship. USA: B.W. Huebsch; 1918.
- Google Scholar
199
Ritzer G, Goodman DJ. Classical Sociological Theory. USA: McGraw-Hill; 2004.
- Google Scholar
200
Linderman K, Schroeder RG, Zaheer S, Choo AS. Six sigma: a goal-theoretic perspective. J Oper Manag. 2003; 21(2):193–203.
- Article
- Google Scholar
201
Archibald RB, Haulman CA, Moody Jr CE. Quality, price, advertising, and published quality ratings. J Consum Res. 1983; 9(4):347–56.
- Article
- Google Scholar
202
Easterling KE. Advanced Materials for Sports Equipment: How Advanced Materials Help Optimize Sporting Performance and Make Sport Safer. London: Chapman & Hall; 1993.
- Google Scholar
203
Webb P. Daily activity and body temperature. Eur J Appl Physiol Occup Physiol. 1993; 66(2):174–7.
- CAS
- PubMed
- Article
- Google Scholar
204
Ayub R, Villarreal D, Gregg RD, Gao F. Evaluation of transradial body-powered prostheses using a robotic simulator. Prosthetics Orthot Int. 2016:0309364616650077.
205
Collier M, LeBIanc M. Axilla bypass ring for shoulder harnesses for upper-limb prostheses. J Prosthetics Orthot. 1996; 8(4):130–1.
- Article
- Google Scholar
206
Melhorn JM. A prospective study for upper-extremity cumulative trauma disorders of workers in aircraft manufacturing. J Occup Environ Med. 1996; 38(12):1264–71.
- CAS
- PubMed
- Article
- Google Scholar
207
Baum A, Fleming R, Singer JE. Coping with victimization by technological disaster. J Soc Issues. 1983; 39(2):117–38.
- Article
- Google Scholar
208
Pursley RJ. Harness patterns for upper-extremity prostheses. Artif Limbs. 1955; 2(3):26.
- CAS
- PubMed
- Google Scholar
209
Schiele A, Letier P, Linde RVD, Helm FVD. Bowden cable actuator for force-feedback exoskeletons. In: 2006 IEEE/RSJ International Conference on Intelligent Robots and Systems (IROS). Beijing: IEEE/RSJ SICE;2006. p. 3599–604.
- Google Scholar
210
Noetzold N. Pull cable system. Google Patents. US Patent 6,250,175. 2001. https://www.google.com/patents/US6250175. Accessed 16 July 2017.
211
Jeong U, Cho KJ. Feedforward friction compensation of bowden-cable transmission via loop routing. In: Proceedings of the 2015 IEEE/RSJ International Conference on Intelligent Robots and Systems (IROS). Piscataway: IEEE;2015. p. 5948–953.
- Google Scholar
212
Berry B. The Power of Looks: Social Stratification of Physical Appearance. USA: Taylor & Francis; 2016.
- Google Scholar
213
Goffman E. Stigma: Notes on a Spoiled Identity. New York: Simon & Schuster; 1963.
- Google Scholar
214
Schweitzer W. Improving Prosthetic Arms through Better Testing [invited commentary], vol. 96. Northglenn: O&P Edge, Western Media LLC; 2014.
- Google Scholar
215
Bundeamt für Sozialversicherungen BSV. Kreisschreiben über die Abgabe von Hilfsmitteln durch die Invalidenversicherung, Stand 1. Bern: Bundeamt für Sozialversicherungen; 2017.
- Google Scholar
216
Schweitzer W. swisswuff.ch/tech - “Hard Bimanual Activities (HBM) [overview]”. 2015. http://www.swisswuff.ch/tech/?p=5330. Accessed 16 July 2017.

Download references

Acknowledgments

Wrist: WS provided design requirement and testing over 3 prototype versions while Stephan Müller (SHL Group, Taoyuan City, Taiwan) drafted the CAD in cooperation with the manufacturers, Peter Schneider and Roman Meili (MDP Meili Design Production, Stein am Rhein, Switzerland) [106]. Extensive free of charge technical support for development, manufacturing and fast development cycles by Roman Meili and Peter Schneider (MDP Meili Design Production, Stein am Rhein, Switzerland) as well as Stephan Müller (SHL Group, Taoyuan City, Taiwan).

Cable: Cable mount advice was provided upon request free of charge by Daniel Schoepke (Brugg Drahtseil AG, Birr AG, Switzerland) and Ruedi Hafner (Hafners Rad, Wallisellen, Switzerland). WS invented the cable support system [105] and provided the first two single-handedly assembled prototypes. Balgrist Tec’s Arnulf Bleuler (who carried out the first definitive or final cable setup implementation after WS prototypes) and later DE provided most of WS’ prosthetic arms’ assemblies, assisted by other employees of Balgrist Tec (Zurich, Switzerland), and for all applied testing, close cooperation with the prosthetic technicians was a key factor in this.

Shoulder brace: design initiated by WS after he had developed neurological problems due to brachial plexus compression due to F9H; shoulder brace developed, designed and carried out by DE.

Funding

The authors express their gratitude to Emma Louise Kessler, MD for her generous donation to the Zurich Institute of Forensic Medicine, University of Zurich, Switzerland. The first and second author of this study are employed at that Institute. The local governmental disability insurance (IV, Invalidenversicherung, Canton of Zurich, Switzerland) financed the shoulder brace and wrist units as well as prosthetic arms, whereas repair and development costs were carried by all contributors to varying degrees.

Availability of data and materials

Data sharing not applicable to this article as no data sets were generated or analyzed during the current study.

Author information

Affiliations

Zurich Institute of Forensic Medicine, University of Zurich, Winterthurerstrasse 190, Zürich, Switzerland
- Wolf Schweitzer
- & Michael J. Thali
Balgrist Tec, Forchstrasse 340, Zürich, Switzerland
- David Egger

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Contributions

WS drafted the poster, provided all of the text and images and citations. DE built all final versions of the prosthetic arms. MT provided employment for and supported WS. All read and agreed to the final manuscript.

Corresponding author

Correspondence to Wolf Schweitzer.

Ethics declarations

Ethics approval and consent to participate

The user featured in this retrospective publication of on the job prosthetic arm evaluation consented to the publication and happens to be the first author and corresponding author of this study. As this work details the results of direct prosthetic device evaluation and component development as a necessity of employed work, this does not conform to the structure of a trial but of hand(s) on real life rehabilitation. Any adverse or negative side effects of prosthetic use as well as time, cost and efforts for medical treatment or prosthetic part repairs are an integral part of life with using prosthetic arms for PDW, and this paper shows how some of the significant negative aspects were minimized through user driven efforts. Ethics approval for reporting health and prosthesis use based outcomes was applied for and granted. The name of the responsible ethics committee is the Cantontal Ethics Committee of the Canton of Zurich, Switzerland. The commitee’s reference number for this is BASEC-Nr. Req-2017-00088.

Consent for publication

The user featured in this study is the corresponding author and first author of this study. As he writes this line, he, again, consents to this publication.

Competing interests

The authors declare that there is no competing or commercial interest and no conflict of interest.

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Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.

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About this article

Received
01 March 2017
Accepted
11 December 2017
Published
03 January 2018
DOI
https://doi.org/10.1186/s12984-017-0340-0

Keywords

Prosthesis design
Artificial limbs
Artificial arm
Body-powered prosthetic arm
Myoelectric prosthetic arm
User-driven design

Case-study of a user-driven prosthetic arm design: bionic hand versus customized body-powered technology in a highly demanding work environment

Abstract

Background

Methods

Results

Conclusions

Background

What is the current requirement for prosthetic arm technology?

What is the current acceptance for prosthetic arm technology under these requirements?

Forensic medicine as a work environment

Death scenes / field work

Office, research and laboratory work

Mapping of forensic medicine tasks to academic tests of prosthetic arms

Methods

Description of problem domain

Body-powered technology

Myoelectric technology

Funding

Training aspects

Choice of user driven innovations

Prosthetic arm comparison, training and assessments

Characterization off-shelf myoelectric technology / TBI problems

Characterization off-shelf body-powered technology/ CBPA problems

Solutions for body-powered arm and user-driven modifications (CBPA)

Solution for myoelectric arm (TBI)

Technology advantages weighed against each other

Other use than work and further developments

Results

Quantitative aspects

Qualitative aspects

Discussion

Consideration of requirements of different interest groups

Narrowing technical options

Dermatological side-effects of prosthetic arms

Sudden failure rather than graceful degradation

Grip quality and grip strength

Considerations about testing and reliability

Popularized testing

Occupational task oriented testing – lowering error rates towards “Six Sigma”

Building effective solutions

Shoulder brace

Cable sheath – sudden failure versus graceful degradation

Quick lock wrist

Further research and development

Cosmetic prosthetic arms

Functional prosthetic arms

Conclusions

Endnotes

Notes

Abbreviations

References

Acknowledgments

Funding

Availability of data and materials

Author information

Affiliations

Zurich Institute of Forensic Medicine, University of Zurich, Winterthurerstrasse 190, Zürich, Switzerland

Balgrist Tec, Forchstrasse 340, Zürich, Switzerland

Authors

Search for Wolf Schweitzer in:

Search for Michael J. Thali in:

Search for David Egger in:

Contributions

Corresponding author

Ethics declarations

Ethics approval and consent to participate

Consent for publication

Competing interests

Publisher’s Note

Rights and permissions

About this article

Received

Accepted

Published

DOI

Keywords

Journal of NeuroEngineering and Rehabilitation

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